US20070051371A1 - Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient - Google Patents
Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient Download PDFInfo
- Publication number
- US20070051371A1 US20070051371A1 US11/554,378 US55437806A US2007051371A1 US 20070051371 A1 US20070051371 A1 US 20070051371A1 US 55437806 A US55437806 A US 55437806A US 2007051371 A1 US2007051371 A1 US 2007051371A1
- Authority
- US
- United States
- Prior art keywords
- patient
- pressure
- snoring
- sleep
- monitoring
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/097—Devices for facilitating collection of breath or for directing breath into or through measuring devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6813—Specially adapted to be attached to a specific body part
- A61B5/6814—Head
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B7/00—Instruments for auscultation
- A61B7/003—Detecting lung or respiration noise
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F5/00—Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices; Anti-rape devices
- A61F5/56—Devices for preventing snoring
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0051—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes with alarm devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0057—Pumps therefor
- A61M16/0066—Blowers or centrifugal pumps
- A61M16/0069—Blowers or centrifugal pumps the speed thereof being controlled by respiratory parameters, e.g. by inhalation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
- A61M16/022—Control means therefor
- A61M16/024—Control means therefor including calculation means, e.g. using a processor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/06—Respiratory or anaesthetic masks
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/0015—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors
- A61M2016/0018—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical
- A61M2016/0024—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical with an on-off output signal, e.g. from a switch
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
- A61M2016/0036—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the breathing tube and used in both inspiratory and expiratory phase
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/04—Heartbeat characteristics, e.g. ECG, blood pressure modulation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/08—Other bio-electrical signals
- A61M2230/10—Electroencephalographic signals
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/18—Rapid eye-movements [REM]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/20—Blood composition characteristics
- A61M2230/205—Blood composition characteristics partial oxygen pressure (P-O2)
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/40—Respiratory characteristics
- A61M2230/43—Composition of exhalation
- A61M2230/432—Composition of exhalation partial CO2 pressure (P-CO2)
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/60—Muscle strain, i.e. measured on the user
Definitions
- the present invention relates to the diagnosis and treatment of partial or complete upper airway occlusion, a condition where the upper airway collapses, particularly under the reduced pressure generated by inhalation. This is most likely to happen during unconsciousness, sleep or anaesthesia.
- a particular application of the present invention is to the diagnosis and/or treatment of snoring and sleep apnea.
- Sleep apnea is characterized by complete occlusion of the upper airway passage during sleep while snoring is characterized by partial occlusion.
- Obstructive sleep apnea sufferers repeatedly choke on their tongue and soft palate throughout an entire sleep period resulting in lowered arterial blood oxygen levels and poor quality of sleep. It should be realized that although the following specification discusses sleep apnea in detail, the present invention also applies to the diagnosis and treatment of other forms of upper airway disorders.
- CPAP continuous positive airway pressure
- the patient is connected to a positive pressure air supply by means of a nose mask or nasal prongs.
- the air supply breathed by the patient is at all times, at slightly greater than atmospheric pressure.
- gauge pressures will typically be within the range of 2 cm to 25 cm.
- the application of continuous positive airway pressure provides what can be described as a “pneumatic splint”, supporting and stabilizing the upper airway and thus eliminating the occurrence of upper airway occlusions. It is effective in eliminating both snoring and obstructive sleep apnea and in many cases, is effective in treating central and mixed apnea.
- the airway pressure required for effective CPAP therapy differs from patient to patient.
- the practice has been for the patient to undergo two sleep studies at an appropriate observation facility such as a hospital, clinic or laboratory.
- the first night is spent observing the patient in sleep and recording selected parameters such as oxygen saturation, chest wall and abdominal movement, air flow, expired CO 2 , ECG, EEG, EMG and eye movement.
- This information can be interpreted to diagnose the nature of the sleeping disorder and confirm the presence or absence of apnea and where present, the frequency and duration of apneic episodes and extent and duration of associated oxygen desaturation.
- Apneas can be identified as obstructive, central or mixed.
- the second night is spent with the patient undergoing nasal CPAP therapy.
- the CPAP setting is increased to prevent the apnea.
- the pressure setting at the end of the sleep period i.e., the maximum used, is deemed to be the appropriate setting for that patient.
- these various pressures will, in fact, vary from day to day depending upon the patient's physical condition, for example, nasal congestion, general tiredness, effects of drugs such as alcohol, as well as their sleeping posture.
- the appropriate pressure found in the laboratory is necessarily the maximum of all these minimum pressures for that particular night and is not necessarily the ideal pressure for all occasions nor for every night. It will generally be higher than necessary for most of the night.
- Low airway pressures are also desirable before and during the early stage of each sleep period as the increased comfort of an initially lower airway pressure allows the patient to more easily fall asleep.
- a patient undergoing CPAP opens his mouth with pressurized air being forced through the nose the pressured air exits out of the mouth producing an unpleasant sensation. This can occur when the patient puts on the mask connected to the pressured air supply before falling asleep and some patients will therefore leave the mask off for as long as possible and may in fact faIl asleep without wearing the mask and therefore without the benefits of the CPAP therapy.
- International Patent publication WO/86/05965 discloses an apparatus which includes acoustic respiration sensors, background sound sensors and movement sensors. Such apparatus are capable of detecting breathing sounds, comparing those sounds with body movements and background noises and by further comparing the results with a data base of information, to indicate whether the patient is undergoing a normal or abnormal breathing pattern. Such apparatus can sound an alarm on the occurrence of apnea.
- the sound transducer in its most general form, consists of a pressure transducer which, in addition to detecting snoring sounds, can detect other respiratory parameters such as the rate of breathing, inhaled air flow or inhaled air flow rate.
- the inherent simplicity of this form of measurement makes it safe and practicable for anybody to use in their own home with a minimum of prior instruction.
- diagnosis in a sleep clinic as outlined above is beneficial, it has some deficiencies.
- a patient is likely not to sleep in a fully relaxed state in an unfamiliar environment and a single night is insufficient to obtain a pressure setting that will be optimal in the long run.
- home therapy at the pressure setting arrived at in this way is likely to be less than 100% effective on some occasions and higher than necessary for a substantial portion of the time.
- the cost and inconvenience of a sleep study in a hospital setting are to be avoided if possible.
- a skilled physician can usually recognize the symptoms of sleep apnea from questioning and examining a patient. Where no other indications are present there is very little risk in attempting nasal CPAP therapy without further testing as the treatment is fail safe and non-invasive. However, a very useful intermediate step would be to analyze the pattern of respiratory sounds over one or more full nights of sleep. Interpretation of these patterns together with questioning and examination will, in many cases, provide sufficient confirmation of apnea to prescribe nasal CPAP therapy. If nasal CPAP eliminates the symptoms of day time sleepiness (as assessed by the patient) and of apneic snoring patterns (as assessed by analysis of recorded respiratory sounds while on nasal CPAP), the treatment can be continued. Further check ups can be conducted at intervals recommended by the physician.
- the intermediate step before attempting nasal CPAP therapy would be to analyse the patterns of the respiratory parameters that can be obtained from a single pressure transducer. These parameters include, in addition to acoustic rate of breathing, inhaled/exhaled air volume and inhaled/exhaled air flow rate, and provide comprehensive information for the physician to assess the patient's condition. This additional information, coming from the same pressure transducer, is available at marginal additional cost to the acoustic recording and with no additional complexity in home use by the patient.
- the measurement of other parameters would provide further information to assist diagnoses and the acoustic and/or other respiratory recordings described above can readily be used in conjunction with other monitors such as ECG and/or pulse oximetry. Suitable monitors are available to measure both these parameters in the home but with increased information comes much higher cost of equipment and increase complexity in using the equipment.
- the correlation between reduced oxygen saturation and apnea is sufficiently well established to infer oxygen desaturation from the confirmation of an apneic event.
- the present inventors have recognized the detection of the noise of snoring or more particularly snoring patterns as a reliable parameter for detecting apneas as well as the imminent onset of apneic episodes.
- Characteristic snoring patterns can be associated with various sleep conditions including apnea and in fact in most (perhaps 95%) of sleep apnea sufferers, distinctive snoring patterns closely precede apneic episodes as will be later discussed.
- Characteristic patterns of other respiratory parameters such as rate of breathing, inhaled/exhaled air volume and inhaled/exhaled air flow rate, obtainable from the same pressure transducer as snoring patterns, can also be used for detecting apneas as well as the imminent onset of apneic episodes. Any one parameter or combination of parameters may be used for detecting apneas or other breathing disorders, as well as the imminent onset of apneas or other breathing disorders.
- a snoring monitor can accordingly be used at least as a preliminary diagnostic tool with or without monitoring other physiological parameters to provide information on the frequency and severity of snoring, hypopnea and apnea in a patient. Its simplicity and inexpensive nature allows it to be used at home in the patient's usual environment without the expense of a night in a sleep clinic. In some cases, e.g., where unusual snoring patterns are encountered, the diagnosis of the data from the snoring monitor will not be conclusive and the traditional full diagnosis in a sleep clinic will be required.
- a diagnostic device comprising a nose piece substantially fluidly sealable to the nasal air passages of a patient, a sound transducer in sound communication with the interior of the nose piece so as to be, when in use, in sound communication with the respiratory system of the patient and to detect and produce a signal responsive to the sounds of patient snoring, and recording equipment associated with the sound transducer for recording information indicative of the signal.
- a nose piece substantially fluidly sealable to, or in sealed fluid communication with, the nasal air passages of a patient, a pressure transducer in pressure communication with the interior of the nose piece so as to be in pressure communication with the respiratory system of the patient and to detect and produce a signal or signals responsive to snoring and other respiratory parameters, such as rate of breathing, inhaled/exhaled air volume and inhaled/exhaled air flow rate, of the patient, and recording equipment associated with the pressure transducer for recording information indicative of one or more of the signals.
- the pressure transducer measures or detects a number of audio or low frequency waves generated within the mask during breathing including a high frequency audio wave produced by the air flow into the mask and by the rotating elements of the air source, a low frequency audio wave produced by the resonance of the airways or chest cavity during snoring, a very low frequency large amplitude wave corresponding to the pressure variations produced by the air flowing over a section of the nose piece, which may include a flow restrictor to amplify the pressure drop.
- the output signal from the pressure transducer passes through filtering and conditioning circuits to separate the different waves of interest, including the low frequency audio wave described above and the very low frequency pressure wave produced by the air flowing over the said section of the nose piece.
- the breathing rate or interruption of breathing, the air flow rate during inhalation/exhalation and the beginning/end points of the breathing cycle are derived from the very low frequency pressure wave after further sampling or processing.
- the air flow is integrated for the duration of the inspiration and/or expiration phase using the said beginning/end points. This integral of air flow corresponds to the inhaled/exhaled air volume for each breath.
- the processed signals are recorded as a time chart or a table interpreted by a physician.
- a snoring monitor provides an effective substitute for the traditional first night in the sleep clinic.
- the monitor in its more general form provides information on respiratory parameters such as rate of breathing, inhaled/exhaled air volume, and inhaled/exhaled air flow rate, as well as snoring.
- diagnosis indicates CPAP therapy to be appropriate the patient can go straight to the traditional second night at the sleep clinic so as to determine their appropriate CPAP setting for their condition, or they could commence use of an automatic CPAP device such as the unit described hereunder.
- an effective CPAP device can be controlled by a feedback system in which snoring patterns are monitored and CPAP pressure is raised at the detection of predefined snoring patterns so as to provide increased airway pressure before, and in fact generally prevent the occurrence of, apneic episodes.
- a feedback control comprising a sound monitoring device in sound communication with the respiratory system of a patient when using the apparatus, and a processor responsive to output from the sound monitoring device so as to control CPAP pressure according to patient requirements as determined by output from the sound monitoring device in order to prevent apneic episodes.
- an effective CPAP device can be controlled by a feedback system in which patterns of respiratory parameters are monitored and CPAP pressure is raised at the detection of pre-defined patterns so as to provide increased airway pressure, before and in fact generally prevent the occurrence of apneic episodes or other forms of breathing disorders.
- the air flow rate inhaled or exhaled by the patient is compared to a base line level for that patient and if the flow rate is lower than the base line, the CPAP pressure is raised.
- the time interval between the onset of each inspiration or expiration is compared to a base line level for that patient and if the interval is greater than the base line, the CPAP pressure is raised.
- the integrated inhaled or exhaled volume of air is averaged over a relatively large number of breaths to give a moving base line for the patient. Simultaneously, the integrated inhaled or exhaled volume of air is averaged over a short time interval. If the volume over the short time interval is less than the volume over the relatively large number of breaths by a specified amount, CPAP pressure is raised.
- the feedback control is co-operative with a variable speed air compressor of the CPAP apparatus, the processor regulating the speed of the compressor when in use by increasing speed in response to a said signal equivalent to a preprogrammed signal indicative of a predetermined snoring pattern.
- the said signal could also be indicative of a pre-determined pattern in other respiratory parameters.
- control system furthermore decreases speed of the air compressor in the absence of the signal after a period of time in accordance with the predefined procedure.
- a CPAP apparatus including a variable speed air compressor, a nose piece for sealed air communication with a patient's respiratory system, an air line from the compressor to the nose piece, an enclosed microphone connected to the air line so as to be in sound communication with the patient's respiratory system, and a feedback system controlling the speed of the air compressor in response to an output from the microphone so as to increase compressor speed in response to detected sound indicative of heavy snoring in accordance with a pre-defined procedure.
- the feedback system reduces the speed of the air compressor in response to an absence of the said sound in accordance with the predefined procedure.
- a CPAP apparatus including a variable speed air compressor, a nose piece for sealed air communication with a patient's respiratory system, an air line from the compressor to the nose piece, a pressure transducer connected to the air line so as to be in pressure communication with the patient's respiratory system, and a feedback system controlling the speed of the air compressor in response to an output or outputs from the pressure transducer so as to increase compressor speed in response to detected patterns of sound or respiratory parameters indicative of snoring or breathing disorders in accordance with a predefined procedure.
- the feedback system reduces the speed of the air compressor in response to an absence of the said patterns of sound or respiratory parameters in accordance with the predefined procedures.
- a further aspect of the invention which provides a variable speed air compressor and control system in the CPAP apparatus, the control system regulating the speed of the compressor when in use by increasing its speed in accordance with a predefined procedure whereby the commencement of operation of the compressor occurs at a preselected minimum speed with a gradually increasing compressor speed over a preselected period of time to a preselected maximum speed.
- This embodiment of the invention provides an advantage in that the patient is exposed to a comfortably low pressure before falling asleep and during initial stages of sleep while the necessary therapeutic pressure is reached by the time it is required.
- FIG. 1 a is a schematic sectional view of one embodiment of a snoring detection apparatus in accordance with the present invention
- FIG. 1 b is a schematic sectional view of another embodiment of a snoring detection apparatus in accordance with the present invention.
- FIG. 3 is a diagram of a further embodiment of the present invention.
- FIG. 4 is a circuit diagram of the device of FIG. 3 ;
- FIG. 6 is a circuit diagram of the device of FIG. 5 ;
- FIG. 8 shows the volume of air breathed by a patient in normal sleep contrasted with the declining volume breathed as the patient starts to hypoventilate
- FIG. 9 shows the different pressure waves generated by the extraneous high frequency noise associated with air flow from the blower and the pressure waves of interest indicative of snoring and breathing and the composite wave comprising the contribution of all sources of pressure wave;
- FIG. 11 shows in schematic form how any or all of these parameters can be used either alone or by reference to control data to provide a signal to a Motor Speed Controller
- FIG. 12 shows in schematic form how the computing system which analyzes the parameters of interest with reference to control patient data controls motor speed and air pressure delivered to the patient;
- FIG. 1 a illustrates a snoring detection device 10 comprising a microphone 11 , in sound communication with the container 12 of a nose mask.
- Air being inhaled by the patient, enters the nasal passageways 14 through the opening 13 in the nose mask 12 and is exhaled in the reverse direction.
- the microphone 11 is ideally located to take advantage of the natural stethoscope formed by the enclosed airway. Hence the snoring and breathing sounds are focused and concentrated by this arrangement.
- the microphone 11 may be located within, or attached externally of, a nasal prong device as illustrated in FIG. 1 b .
- the detection device 10 can be used in a diagnostic device or a feedback control.
- the detection device 10 being used in diagnostic equipment there is connected to the microphone 11 an electronic processor/recorder which records signals from the microphone 11 either on a time basis or after preprogrammed processing so as to record for example tables of indexes such as the number of apneic episodes, their duration, etc.
- the recorded data can then be reviewed by the physician for diagnosis.
- FIG. 2 a shows a graph representing sound amplitudes recorded from the snoring detection device 10 .
- the major calibration in the time scale direction represents two minutes.
- blower motor noise can be diminished or completely removed by setting a low gain on the recording device or passing the signal through an amplitude filter to effectively ignore all sounds below a particular minimum amplitude or by passing the signals through a low pass frequency filter to effectively ignore sounds above its cut-off frequency.
- An alternative method is to use a sound attenuator in the air line proximate the blower.
- FIG. 2 b The correlation between snoring patterns and arterial oxygen is shown in FIG. 2 b .
- the snoring patterns are an accurate parameter for detecting imminent apneic episodes, and more importantly periods of low oxygen supply to the brain and other organs.
- recorded information derived from the signal of the device 10 can be used for diagnostic purposes, such as initial diagnosis of sleep apnea, without the need for the patient to stay overnight at an observation facility.
- the sound patterns can be analyzed by a programmed microprocessor within the diagnostic unit so as to record tables of indexes such as number of apneic episodes, their duration and time of occurrence. This is of economic significance because the cost of one overnight observation is comparable to the purchase price of a CPAP device.
- the nose prongs and mask 12 are convenient forms of containers for the monitor device 10 however the container could take any other convenient form.
- diagnostic apparatus in accordance with the present invention is suited for use by a patient with minimal supervision and therefore may be used successfully at home, the recorded diagnostic information being conveniently presented for expert analysis.
- the CPAP unit comprises a motor 20 which drives a blower 21 .
- the speed of the motor 20 is controlled by an electronic speed control unit 23 .
- the speed control unit can be manipulated to vary the output pressure of the blower 21 .
- the CPAP device also includes a snoring detection means 22 wherein sounds are detected by a microphone 11 .
- the snoring detection means 22 is a pressure detection means and microphone 11 is a differential pressure sensor.
- the snoring detection means 22 is conveniently in the form of the previously described device 10 .
- the motor speed control means is electrically connected to the snoring detection device 22 and increases the speed of the electric motor 20 by an analogue means in response to the electrical signal generated by the snoring detection device. Accordingly, the output pressure of the CPAP unit increases in response to detection of snoring.
- a signal is generated.
- the speed control unit 23 increases the speed of the fan motor and the output pressure is increased.
- Snoring is itself undesirable not only as it is a disturbance to others but it is strongly believed to be connected with hypertension. If the resultant increase in CPAP pressure is sufficient to completely stabilize the airway, snoring will cease.
- the CPAP pressure is increased again. This process is repeated until the upper airway is stabilized and snoring ceases. Hence, the occurrence of obstructive apnea can be eliminated by application of a minimum appropriate pressure at the time of use.
- the preferred embodiment also includes a means to decrease the pressure if an extended period of snore free breathing occurs. For example, this can be done by automatically reducing the CPAP pressure at a gradual rate as long as snoring is not detected.
- the rate at which the CPAP pressure is decreased in the absence of snoring is preferably much less than the rate at which it is increased when snoring is detected.
- a patient may connect himself to the CPAP unit and go to sleep.
- the CPAP pressure is initially at a minimum operating value of, for example, approximately 3 cm H 2 O gauge pressure so as not to cause the previously mentioned operational problems of higher initial pressures.
- the detection apparatus 22 will then respond to a snore, or snore pattern, and via the processor 26 increase the motor speed such that CPAP pressure increases by 1 cm H 2 O for each snore detected.
- the CPAP pressure can be increased relatively rapidly, if the patient's condition so requires, to a working pressure of the order of 8-10 cm, which is a typical requirement.
- An upper pressure limiting device can be incorporated for safety.
- a parameter such as pressure output can be recorded in some convenient retrievable form for periodic study by the physician.
- the CPAP unit of the present invention will not increase the pressure until needed, that is, unless the airway becomes unstable and snoring recommences no increase is made to the airway pressure.
- the pressure is never substantially greater than that required to prevent apnea.
- the decreasing CPAP pressure mode will be completely overwhelmed by a greater increase, about 1 cm H 2 O per detected snore or snoring pattern.
- a patient normally makes at least one loud snort or snoring sound at the end of an occurrence of apnea and the present invention will respond to this unusually loud sound to increase the CPAP pressure.
- the airway pressure can still be adjusted upward in response to the abnormally loud breathing sounds generated at the end of the apneic period.
- the present invention thus provides a CPAP device which modifies the CPAP pressure according to variations in a patient's requirements throughout an entire sleep period. It will be clear to those skilled in the art that the present invention can cope with the variation in airway pressure requirements such as may occur during a single sleep period, it will also be able to cope with variations in CPAP pressure requirements due to a general improvement or deterioration in a patient's general condition as may take place over a longer period of time.
- FIG. 4 illustrates in block form the circuitry of the CPAP device of FIG. 3 .
- a snoring detection apparatus 22 is comprised of the microphone 11 attached to the nose mask 12 .
- the electrical signals of the microphone 11 are sent to a Filter/Amplifier/Processor 26 which generates a control signal indicative of the recognition of a snoring pattern equivalent to a predetermined pattern.
- the maximum output of the SMPS 15 and therefore the maximum pressure delivered to the mask 12 , is limited by a pressure time control 17 .
- a control circuit 33 comprising a delay control 25 , a timer 24 , a switch mode power supply (SMPS) 15 , and an upper pressure control 17 .
- SMPS switch mode power supply
- the timer 24 a square wave pulse train, is generated where the duty ratio can be varied by the delay control 25 .
- This pulse train in the form of a current, is applied to a capacitor 19 to obtain a ramp voltage.
- the output of the timer 24 and the input of the SMPS 15 is a voltage increasing with respect to time.
- the output of the SMPS 15 and therefore the motor voltage and speed, follow the input.
- the minimum blower speed is preset so as to give effective operation of the air blower 21 and a minimum airway pressure which is comfortable to the patient. Typically a minimum pressure of 3-5 cm H 2 O will have negligible effect on most patients.
- the desired maximum airway pressure being the intended therapeutic airway pressure, is set by adjusting the variable control 17 .
- the magnitude of this pressure will vary according to the requirements of the individual patient but will typically be in the range 10-20 cm H 2 O.
- the apparatus commences operation at the minimum motor speed and gradually increases the motor speed over a period of time selected before reaching the maximum preselected speed according to the previous adjustment of control 17 .
- the delay control 25 is set to zero minutes airway pressure comes up to the full level as set by adjustment 17 in a short period of time.
- FIG. 7 illustrates a pressure detection device comprising a pressure sensor, in pressure communication with the container of a nose mask. Air, being inhaled by the patient, enters the nasal passageways through the opening in the nose mask and is exhaled in the reverse direction.
- the pressure sensor is ideally located to detect both pressure waves generated by the patient snoring or by variations in the respiration rate or pattern of the patient. Hence the snoring sounds and breathing variations are captured and concentrated by this arrangement.
- the pressure sensor may be located within or attached externally to a nasal prong device.
- the detection device can be used in a diagnostic device or a feedback control.
- a computing system as shown in FIG. 12 which analyses and records signals from the pressure sensor in a data store. These signals can be stored on a real time basis or after further processing in the form of indexes such as the number of apneic episodes, the number of hypopneas, their duration, etc.
- the recorded data can then be reviewed by a physician for diagnosis.
- FIG. 9 shows the sources of pressure waves detected by the pressure sensor.
- the high frequency wind noise is generated by the air blower and is extraneous for the purposes of interpreting the condition of the patient.
- Pressure waves at a frequency of 30 to 50 Hz are indicative of snoring and could be detected by using a particular embodiment of the pressure sensor in the form of a microphone. Disturbances in breathing pattern are detected at a very low frequency relating to breathing rate of approximately 0.5 Hz.
- the output of the sensor is a composite of the pressure waves generated by all these sources.
- FIG. 10 Shows a schematic electronic circuit which first amplifies the output of the pressure sensor before passing it through a series of filters to separate the pressure waves at the frequencies of interest. The high frequency wind noise is eliminated and signals indicative of snoring and breathing are obtained. The breathing signal is further processed to give information on breathing rate, flow rate and volume per breath.
- FIG. 2 a shows a graph representing sound amplitudes obtained from the snoring signal filtered from the pressure detection device.
- the major calibration in the time scale direction represents two minutes.
- Part A of FIG. 2 a is indicative of normal breathing
- part B indicates soft to moderate snoring
- part C shows constant loud snoring
- part E shows periods of silence punctuated by snoring.
- section D of the chart of FIG. 2 a it can be seen that the breathing sound intensity rises and falls. This is indicative of obstructive hypopnea, a condition in which the breath-by-breath intensity decreases progressively, and then increases. In this pattern the decreasing intensity of the snoring occurs when the upper airway is almost, but not entirely, sucked closed by strong inspiratory efforts. This pattern is a “pre-apneic” pattern.
- FIG. 2 b The correlation between snoring patterns and arterial oxygen is shown in FIG. 2 b .
- the snoring patterns are an accurate parameter for detecting imminent apneic episodes, and more importantly periods of low oxygen supply to the brain and other organs.
- FIG. 8 shows the volume of air inhaled (or exhaled) by the patient with each breath as determined by the volume integrator from the breathing signal filtered from the pressure sensor.
- Part A of FIG. 8 shows normal breathing, while Part B shows shallow breathing or hypoventilation.
- a decreasing pattern of air volume inspired by the patient can be indicative of the imminent onset of apnea or can be undesirable as the patient's arterial oxygen level falls below an acceptable level.
- FIG. 10 shows how the processing system can be set up to respond when the average volume of a predefined number of the most recent breaths falls below the volume of a predefined long term average volume for that patient.
- FIG. 11 shows how the computing system can accept and analyze any or all of the processed signals from the pressure sensor and using the signal, alone or by comparison with control data for that patient, control the speed of the blower to vary the pressure of the air delivered to the patient's nose mask.
- FIG. 13 shows an example of how the signal indicative of snoring alone is received by the computing system and the computing system increases pressure in accordance with predefined procedure.
- the recorded information derived from the signal of the pressure sensor can be used for diagnostic purposes, such as initial diagnosis of sleep apnea or hypopnea, without the need for the patient to stay overnight in an observation facility, the sound and breathing patterns can be analyzed by a programmed microprocessor or computing system as shown in FIG. 12 so as to record tables of indexes such as number of hypopneas and/or apneic episodes, their duration and time of occurrence. This is of economic significance because the cost of one overnight observation is comparable to the purchase price of a CPAP device.
- diagnostic apparatus in accordance with the present invention is suited for use by a patient with minimal supervision and therefore may be used successfully at home, the recorded diagnostic information being conveniently presented for expert analysis.
- the CPAP unit comprises a motor 20 which drives a blower 21 .
- the speed of the motor 20 is controlled by an electronic speed control unit 23 .
- the speed control unit can be manipulated to vary the output pressure of the blower 21 .
- the CPAP device also includes a pressure detection means 22 wherein pressure waves in the form of electrical signals are detected by a pressure sensor 11 .
- the pressure detection means 22 is conveniently in the form of the previously described device illustrated in FIG. 7 .
- Electrical signals are fed from said sensor 11 to an amplifier/filter/processor unit 26 which may be inside or outside the blower unit casing and generates an electrical signal when snoring sounds and/or deviations of breathing parameters from predetermined values occur.
- the motor speed control means is electrically connected to the pressure detection device 22 while being electrically isolated from the patient and increases the speed of the electric motor 20 by an analogue means in response to the electrical signal generated by the pressure detection device. Accordingly, the output pressure of the CPAP unit increases in response to detection of snoring and/or deviations of breathing parameters from predetermined values.
- the method of operation can be illustrated by considering the effect of a snore or sequence of snores detected by the pressure sensor as shown in FIG. 13 .
- a snore or sequence of snores is detected by the snoring detection means 22 a signal is generated.
- the speed control unit 23 increases the speed of the fan motor and the output pressure is increased.
- Snoring is itself undesirable not only as it is a disturbance to others but it is strongly believed to be connected with hypertension.
- the preferred embodiment also includes a means to decrease the pressure if an extended period of snore free breathing occurs. For example, this can be done by automatically reducing the CPAP pressure at a gradual rate as long as snoring is not detected.
- the rate at which the CPAP pressure is decreased in the absence of snoring is preferable much less than the rate at which it is increased when snoring is detected.
- a predetermined deviation of any or all of the breathing parameters, flow rate, volume or breathing rate from a predetermined common value can generate a signal in a similar way. Hence a fall in the volume of air inspired or expired per breath below a preset value can generate a signal which increases the speed of the fan motor and increases the output pressure. After the breathing volume has returned to the control setting for a predetermined period, the fan motor speed will be decreased slowly until a snore or unacceptable breathing pattern is again detected by the pressure sensor.
- a patient may connect himself to the CPAP unit and go to sleep. Only one connection is required apart from the normal CPAP circuit and this is simply the connection from the pressure sensor to the amplifier/filter/processor unit. No electrodes or other sensors have to be attached to the patient's body as the pressure sensor is conveniently located in the CPAP mask.
- the CPAP pressure is initially at a minimum comfortable operating value of, for example, approximately 3 cm H 2 O gauge pressure so the as not to cause the previously mentioned operational problems of higher initial pressures. Not until some time after going to sleep, and the patient's body relaxes, will the airway start to become unstable and the patient start to snore or exhibit abnormal breathing patterns.
- the detection apparatus 22 will a respond to the snore, or snore pattern or abnormal breathing pattern and via the processor 26 increase the motor speed such that CPAP pressure increases by 1 cm H 2 O for each snore or predetermined abnormality in breathing pattern detected.
- the CPAP pressure can be increased relatively rapidly, if the patient's condition so requires, to a working pressure of the order of 8-10 cm H 2 O, which is a typical requirement.
- An upper pressure limiting device can be incorporated for safety.
- a parameter such as pressure output can be recorded in some convenient retrievable form for periodic study by the physician.
- the CPAP unit of the present invention will not increase the pressure until needed, that is, unless the airway becomes unstable and snoring or abnormal breathing patterns recommence, no increase is made to the airway pressure.
- the pressure is never substantially greater than that required to prevent apnea or other undesirable respiratory conditions.
- the decreasing CPAP pressure mode will be completely overwhelmed by a greater increase, about 1 cm H 2 O per predetected snore or snoring pattern or predetermined abnormality in breathing pattern.
- the pressure is reincreased to ensure that apnea is prevented, it being remembered that the snoring or abnormal breathing pattern is a precursor to apneic episodes or other undesirable respiratory conditions such as shallow breathing or hypopnea.
- a patient normally makes at least one loud snort or snoring sound at the and of an occurrence of apnea and the present invention will respond to this unusually loud sound to increase the CPAP pressure.
- the airway pressure can still be adjusted upward in response to the abnormally loud breathing sounds generated at the end of the apneic period.
- the present invention thus provides a CPAP device which modifies the CPAP pressure according to variations in a patient's requirements throughout an entire sleep period. It will be clear to those skilled in the art that the present invention can cope with the variation in airway pressure requirements such as may occur during a single sleep period, it will also be able to cope with variations in CPAP pressure requirements due to a general improvement or deterioration in a patient's general condition as may take place over a longer period of time.
- FIG. 12 illustrates in block form the circuitry of the feedback system.
- a pressure detection apparatus is provided either integral with or attached to the CPAP mask worn by the patient.
- the electrical signals from the pressure transducer are amplified and filtered to provide pressure waves of the desired frequencies indicative of snoring and breathing.
- the pressure wave indicative of breathing is further processed to generate signals indicative of flow rate, volume and breathing rate. Any or all signals are fed to a computing system which analyses the signals for deviation from predetermined values or patterns.
- the computing system may itself calculate control values of patterns for each patient based on moving average values or such values or patterns will be pre-programmed into the computing system.
- the computer system Where signals deviate from predetermined values or patterns the computer system generates a signal which is sent to the feedback speed controller on the blower motor. Increasing blower speed increases the air pressure and level of CPAP treatment delivered to the patient. The speed and pressure are increased until signals detected from the patient are within the acceptable range of control values or patterns and the speed and pressure are maintained at that level.
- the maximum output' of the blower can be limited by limiting the signal from the computer to correspond to a predetermined motor speed.
- a convenient way to gauge whether a correct therapeutic or maximum, pressure has been selected is to use the diagnostic device shown in FIG. 7 of this invention while the patient is undergoing CPAP therapy. Should the recorded data show no signs of apneic periods then the setting may be assumed to be adequate at least for the patient when in a similar physical condition. Another long term benefit can be gained by recording the pressure level applied to the patient during sleep periods in which CPAP is applied using the feedback device of this invention. By making such recordings spaced over a period of time the skilled physician can diagnose any long term changes in the patient's condition.
Abstract
Patients may operate a CPAP system to deliver appropriate airway pressure at their home. A patient's apnea problem can be diagnosed at home without supervision with a CPAP device which delivers a continuously minimum appropriate pressure for substantially the entire period of therapy.
Description
- This application is a continuation-in-part of application Ser. No. 07/457,757, filed Dec. 21, 1989.
- The present invention relates to the diagnosis and treatment of partial or complete upper airway occlusion, a condition where the upper airway collapses, particularly under the reduced pressure generated by inhalation. This is most likely to happen during unconsciousness, sleep or anaesthesia.
- A particular application of the present invention is to the diagnosis and/or treatment of snoring and sleep apnea. Sleep apnea is characterized by complete occlusion of the upper airway passage during sleep while snoring is characterized by partial occlusion. Obstructive sleep apnea sufferers repeatedly choke on their tongue and soft palate throughout an entire sleep period resulting in lowered arterial blood oxygen levels and poor quality of sleep. It should be realized that although the following specification discusses sleep apnea in detail, the present invention also applies to the diagnosis and treatment of other forms of upper airway disorders.
- Reference to international patent publication WO 82/03548 will show that the application of continuous positive airway pressure (CPAP) has been used as a means of treating the occurrence of obstructive sleep apnea. The patient is connected to a positive pressure air supply by means of a nose mask or nasal prongs. The air supply breathed by the patient, is at all times, at slightly greater than atmospheric pressure. For example, gauge pressures will typically be within the range of 2 cm to 25 cm. It has been found that the application of continuous positive airway pressure provides what can be described as a “pneumatic splint”, supporting and stabilizing the upper airway and thus eliminating the occurrence of upper airway occlusions. It is effective in eliminating both snoring and obstructive sleep apnea and in many cases, is effective in treating central and mixed apnea.
- The airway pressure required for effective CPAP therapy differs from patient to patient. In order to discover the airway pressure which is most effective for a particular individual, the practice has been for the patient to undergo two sleep studies at an appropriate observation facility such as a hospital, clinic or laboratory. The first night is spent observing the patient in sleep and recording selected parameters such as oxygen saturation, chest wall and abdominal movement, air flow, expired CO2, ECG, EEG, EMG and eye movement. This information can be interpreted to diagnose the nature of the sleeping disorder and confirm the presence or absence of apnea and where present, the frequency and duration of apneic episodes and extent and duration of associated oxygen desaturation. Apneas can be identified as obstructive, central or mixed. The second night is spent with the patient undergoing nasal CPAP therapy. When apnea is observed the CPAP setting is increased to prevent the apnea. The pressure setting at the end of the sleep period, i.e., the maximum used, is deemed to be the appropriate setting for that patient. For a given patient in a given physical condition there will be found different minimum pressures for various stages of sleep in order to prevent occlusions. Furthermore, these various pressures will, in fact, vary from day to day depending upon the patient's physical condition, for example, nasal congestion, general tiredness, effects of drugs such as alcohol, as well as their sleeping posture. Thus the appropriate pressure found in the laboratory is necessarily the maximum of all these minimum pressures for that particular night and is not necessarily the ideal pressure for all occasions nor for every night. It will generally be higher than necessary for most of the night.
- Also patients must be able to operate a CPAP system to deliver appropriate airway pressure at their home where their general physical condition or state of health may be quite different to that in the sleep clinic, and will certainly vary from day to day. The patient's physical condition often improves due to CPAP therapy. It is often the case that after a period of therapy the necessary airway pressure can be reduced by some amount while still preventing the occurrence of obstructive sleep apnea. However, the prior art provides no facility to take advantage of this fact other than by regular diagnostic sleep periods in a sleep clinic or hospital.
- The long term effects of CPAP therapy are unknown so it is desirable to keep the airway pressure as low as practicable, particularly if a patient requires long term treatment. Lower airway pressures also result in a lower face mask pressure which is generally more comfortable for the patient. It has been found that CPAP induces patients to swallow and this inducement to swallow can be reduced by lowering the airway pressure. Thus it is desirable to use the lowest practicable airway pressure that is effective in preventing airway occlusion during CPAP therapy for the comfort and, possibly, the long term safety of the patient. Also, a lower airway pressure requires less energy consumption and a less complex and therefore less expensive apparatus which is generally quieter.
- Low airway pressures are also desirable before and during the early stage of each sleep period as the increased comfort of an initially lower airway pressure allows the patient to more easily fall asleep. When a patient undergoing CPAP opens his mouth with pressurized air being forced through the nose the pressured air exits out of the mouth producing an unpleasant sensation. This can occur when the patient puts on the mask connected to the pressured air supply before falling asleep and some patients will therefore leave the mask off for as long as possible and may in fact faIl asleep without wearing the mask and therefore without the benefits of the CPAP therapy.
- Presently available CPAP units do not address this problem and so there is a need to provide a CPAP device which will be more acceptable to the patient before and during initial sleep by operating at an initially low pressure but automatically increasing to an appropriate therapeutic pressure before apnea occurs.
- In addition to the problems associated with administering CPAP therapy there exists the inconvenience and cost of diagnosis which is currently undertaken by overnight observation at a sleep clinic or the like. Hence a simple means whereby a patient's apnea problem can be diagnosed at home without supervision is clearly desirable as well as a CPAP device which will deliver a continuously minimum appropriate pressure for substantially the entire period of therapy.
- Devices are available to detect apnea. For example, International Patent publication WO/86/05965 discloses an apparatus which includes acoustic respiration sensors, background sound sensors and movement sensors. Such apparatus are capable of detecting breathing sounds, comparing those sounds with body movements and background noises and by further comparing the results with a data base of information, to indicate whether the patient is undergoing a normal or abnormal breathing pattern. Such apparatus can sound an alarm on the occurrence of apnea.
- Another device which could be readily adapted to detect and record the occurrence of apneic episodes is disclosed in U.S. Pat. No. 4,537,190. That apparatus is responsive to the CO2 levels in exhaled air during respiration and is also responsive to the absence of respiration (i.e., apnea) in which case it can switch on a ventilator.
- These devices are deficient in that they do not take advantage of the indication of apnea obtained exclusively from a recording from a single sound transducer (microphone) preferably located in the CPAP nose mask or prongs that can be interpreted by a skilled physician. The sound transducer, in its most general form, consists of a pressure transducer which, in addition to detecting snoring sounds, can detect other respiratory parameters such as the rate of breathing, inhaled air flow or inhaled air flow rate. The inherent simplicity of this form of measurement makes it safe and practicable for anybody to use in their own home with a minimum of prior instruction.
- Although diagnosis in a sleep clinic as outlined above is beneficial, it has some deficiencies. A patient is likely not to sleep in a fully relaxed state in an unfamiliar environment and a single night is insufficient to obtain a pressure setting that will be optimal in the long run. Thus home therapy at the pressure setting arrived at in this way is likely to be less than 100% effective on some occasions and higher than necessary for a substantial portion of the time. The cost and inconvenience of a sleep study in a hospital setting are to be avoided if possible.
- A skilled physician can usually recognize the symptoms of sleep apnea from questioning and examining a patient. Where no other indications are present there is very little risk in attempting nasal CPAP therapy without further testing as the treatment is fail safe and non-invasive. However, a very useful intermediate step would be to analyze the pattern of respiratory sounds over one or more full nights of sleep. Interpretation of these patterns together with questioning and examination will, in many cases, provide sufficient confirmation of apnea to prescribe nasal CPAP therapy. If nasal CPAP eliminates the symptoms of day time sleepiness (as assessed by the patient) and of apneic snoring patterns (as assessed by analysis of recorded respiratory sounds while on nasal CPAP), the treatment can be continued. Further check ups can be conducted at intervals recommended by the physician.
- In the most general form of the device, the intermediate step before attempting nasal CPAP therapy would be to analyse the patterns of the respiratory parameters that can be obtained from a single pressure transducer. These parameters include, in addition to acoustic rate of breathing, inhaled/exhaled air volume and inhaled/exhaled air flow rate, and provide comprehensive information for the physician to assess the patient's condition. This additional information, coming from the same pressure transducer, is available at marginal additional cost to the acoustic recording and with no additional complexity in home use by the patient.
- The measurement of other parameters would provide further information to assist diagnoses and the acoustic and/or other respiratory recordings described above can readily be used in conjunction with other monitors such as ECG and/or pulse oximetry. Suitable monitors are available to measure both these parameters in the home but with increased information comes much higher cost of equipment and increase complexity in using the equipment. The correlation between reduced oxygen saturation and apnea is sufficiently well established to infer oxygen desaturation from the confirmation of an apneic event.
- Diagnoses which are not conclusive from examination and home monitoring will continue to be confirmed from full sleep studies in a Sleep Disorders Center.
- Thus the prior art monitors and methods are deficient at least in that the resulting therapy is not 100% effective at all times, it is delivered at higher pressure than necessary for substantial periods, the equipment is expensive and has required diagnosis in specialized clinics.
- The present inventors have recognized the detection of the noise of snoring or more particularly snoring patterns as a reliable parameter for detecting apneas as well as the imminent onset of apneic episodes. Characteristic snoring patterns can be associated with various sleep conditions including apnea and in fact in most (perhaps 95%) of sleep apnea sufferers, distinctive snoring patterns closely precede apneic episodes as will be later discussed. Characteristic patterns of other respiratory parameters such as rate of breathing, inhaled/exhaled air volume and inhaled/exhaled air flow rate, obtainable from the same pressure transducer as snoring patterns, can also be used for detecting apneas as well as the imminent onset of apneic episodes. Any one parameter or combination of parameters may be used for detecting apneas or other breathing disorders, as well as the imminent onset of apneas or other breathing disorders.
- A pressure transducer such as a microphone is a suitable detector of these characteristic snoring sounds, and in particular the sounds of snoring patterns. Furthermore, the quality of the sounds monitored can be enhanced by placing the microphone within an enclosure which is in sound communication with a patient's respiratory system. By enclosing the microphone, a physical noise barrier isolates the microphone from external sounds. If the enclosure is in sound communication with the patient's respiratory system the natural stethoscope effect of the patient's respiratory system is thereby exploited. A further benefit of such a device is that the microphone is not in direct contact with any part of the patient's body. Thus, relative movement between the microphone and the patient's body, which is a noise source as far as monitoring is concerned, can be avoided.
- Monitoring of a patient's snoring patterns alone can in many instances provide information indicative of his/her condition, whether he/she suffers mild, medium or extreme apneic episodes, how often the episodes occur and therefore whether CPAP therapy will be beneficial. A snoring monitor can accordingly be used at least as a preliminary diagnostic tool with or without monitoring other physiological parameters to provide information on the frequency and severity of snoring, hypopnea and apnea in a patient. Its simplicity and inexpensive nature allows it to be used at home in the patient's usual environment without the expense of a night in a sleep clinic. In some cases, e.g., where unusual snoring patterns are encountered, the diagnosis of the data from the snoring monitor will not be conclusive and the traditional full diagnosis in a sleep clinic will be required.
- Thus, in one form of this invention there is provided a diagnostic device comprising a nose piece substantially fluidly sealable to the nasal air passages of a patient, a sound transducer in sound communication with the interior of the nose piece so as to be, when in use, in sound communication with the respiratory system of the patient and to detect and produce a signal responsive to the sounds of patient snoring, and recording equipment associated with the sound transducer for recording information indicative of the signal.
- In another form of the diagnostic device, there is provided a nose piece substantially fluidly sealable to, or in sealed fluid communication with, the nasal air passages of a patient, a pressure transducer in pressure communication with the interior of the nose piece so as to be in pressure communication with the respiratory system of the patient and to detect and produce a signal or signals responsive to snoring and other respiratory parameters, such as rate of breathing, inhaled/exhaled air volume and inhaled/exhaled air flow rate, of the patient, and recording equipment associated with the pressure transducer for recording information indicative of one or more of the signals.
- In one preferred embodiment of the diagnostic device, the intensity of the signal is recorded with respect to time. In another embodiment of the diagnostic device the microphone output is fed through an amplifier or filter to differentiate normal breathing sounds from those indicative of snoring, and the intensities and time pattern of the differentiated sounds are recorded. Further, in a embodiment of the diagnostic device the frequency and duration of airway occlusions are calculated by preprogrammed processing of the detected signal, the processed signal is recorded as a time chart or a table interpreted by the physician.
- In another embodiment of the diagnostic device, the pressure transducer measures or detects a number of audio or low frequency waves generated within the mask during breathing including a high frequency audio wave produced by the air flow into the mask and by the rotating elements of the air source, a low frequency audio wave produced by the resonance of the airways or chest cavity during snoring, a very low frequency large amplitude wave corresponding to the pressure variations produced by the air flowing over a section of the nose piece, which may include a flow restrictor to amplify the pressure drop. After suitable amplification, the output signal from the pressure transducer passes through filtering and conditioning circuits to separate the different waves of interest, including the low frequency audio wave described above and the very low frequency pressure wave produced by the air flowing over the said section of the nose piece.
- The breathing rate or interruption of breathing, the air flow rate during inhalation/exhalation and the beginning/end points of the breathing cycle are derived from the very low frequency pressure wave after further sampling or processing. Using a suitable integration technique, the air flow is integrated for the duration of the inspiration and/or expiration phase using the said beginning/end points. This integral of air flow corresponds to the inhaled/exhaled air volume for each breath. The processed signals are recorded as a time chart or a table interpreted by a physician.
- Thus in a number of cases such a snoring monitor provides an effective substitute for the traditional first night in the sleep clinic. The monitor in its more general form provides information on respiratory parameters such as rate of breathing, inhaled/exhaled air volume, and inhaled/exhaled air flow rate, as well as snoring. Where diagnosis indicates CPAP therapy to be appropriate the patient can go straight to the traditional second night at the sleep clinic so as to determine their appropriate CPAP setting for their condition, or they could commence use of an automatic CPAP device such as the unit described hereunder.
- The monitoring of snoring patterns is useful not only for recording information regarding those patterns for diagnostic purposes but is also useful in that certain snoring patterns are a precursor to most apneic episodes in a large proportion of sleep apnea victims. Thus, an effective CPAP device can be controlled by a feedback system in which snoring patterns are monitored and CPAP pressure is raised at the detection of predefined snoring patterns so as to provide increased airway pressure before, and in fact generally prevent the occurrence of, apneic episodes.
- Thus, in another form of the invention there is provided in a CPAP apparatus a feedback control comprising a sound monitoring device in sound communication with the respiratory system of a patient when using the apparatus, and a processor responsive to output from the sound monitoring device so as to control CPAP pressure according to patient requirements as determined by output from the sound monitoring device in order to prevent apneic episodes.
- The monitoring of other respiratory parameters, as well as snoring, is also useful not only for recording those patterns for diagnostic purposes but is also useful in that certain patterns of these parameters are a precursor to most apneic episodes and other forms of breathing disorders that can be treated by nasal CPAP. Thus an effective CPAP device can be controlled by a feedback system in which patterns of respiratory parameters are monitored and CPAP pressure is raised at the detection of pre-defined patterns so as to provide increased airway pressure, before and in fact generally prevent the occurrence of apneic episodes or other forms of breathing disorders.
- For example, the air flow rate inhaled or exhaled by the patient is compared to a base line level for that patient and if the flow rate is lower than the base line, the CPAP pressure is raised. Alternatively, the time interval between the onset of each inspiration or expiration is compared to a base line level for that patient and if the interval is greater than the base line, the CPAP pressure is raised. Alternatively, the integrated inhaled or exhaled volume of air is averaged over a relatively large number of breaths to give a moving base line for the patient. Simultaneously, the integrated inhaled or exhaled volume of air is averaged over a short time interval. If the volume over the short time interval is less than the volume over the relatively large number of breaths by a specified amount, CPAP pressure is raised.
- Preferably, the feedback control is co-operative with a variable speed air compressor of the CPAP apparatus, the processor regulating the speed of the compressor when in use by increasing speed in response to a said signal equivalent to a preprogrammed signal indicative of a predetermined snoring pattern. The said signal could also be indicative of a pre-determined pattern in other respiratory parameters.
- Preferably, the control system furthermore decreases speed of the air compressor in the absence of the signal after a period of time in accordance with the predefined procedure.
- In another form of the feedback device of the invention there is provided a CPAP apparatus including a variable speed air compressor, a nose piece for sealed air communication with a patient's respiratory system, an air line from the compressor to the nose piece, an enclosed microphone connected to the air line so as to be in sound communication with the patient's respiratory system, and a feedback system controlling the speed of the air compressor in response to an output from the microphone so as to increase compressor speed in response to detected sound indicative of heavy snoring in accordance with a pre-defined procedure. Preferably, the feedback system reduces the speed of the air compressor in response to an absence of the said sound in accordance with the predefined procedure.
- In another form of the apparatus there is provided a CPAP apparatus including a variable speed air compressor, a nose piece for sealed air communication with a patient's respiratory system, an air line from the compressor to the nose piece, a pressure transducer connected to the air line so as to be in pressure communication with the patient's respiratory system, and a feedback system controlling the speed of the air compressor in response to an output or outputs from the pressure transducer so as to increase compressor speed in response to detected patterns of sound or respiratory parameters indicative of snoring or breathing disorders in accordance with a predefined procedure. Preferably the feedback system reduces the speed of the air compressor in response to an absence of the said patterns of sound or respiratory parameters in accordance with the predefined procedures.
- Disadvantages in the prior art are also ameliorated by a further aspect of the invention which provides a variable speed air compressor and control system in the CPAP apparatus, the control system regulating the speed of the compressor when in use by increasing its speed in accordance with a predefined procedure whereby the commencement of operation of the compressor occurs at a preselected minimum speed with a gradually increasing compressor speed over a preselected period of time to a preselected maximum speed.
- This embodiment of the invention provides an advantage in that the patient is exposed to a comfortably low pressure before falling asleep and during initial stages of sleep while the necessary therapeutic pressure is reached by the time it is required.
- The present invention will now be described in detail by way of reference to the attached drawings in which:
-
FIG. 1 a is a schematic sectional view of one embodiment of a snoring detection apparatus in accordance with the present invention; -
FIG. 1 b is a schematic sectional view of another embodiment of a snoring detection apparatus in accordance with the present invention; -
FIG. 2 a is a slow recording of sound levels obtained using the monitor of the present invention for a patient suffering from sleep apnea; -
FIG. 2 b shows the correlation of sound patterns and blood oxygen levels during a period of repetitive obstructive apnea; -
FIG. 3 is a diagram of a further embodiment of the present invention; -
FIG. 4 is a circuit diagram of the device ofFIG. 3 ; -
FIG. 5 is a diagram of an embodiment of another aspect of the invention; -
FIG. 6 is a circuit diagram of the device ofFIG. 5 ; -
FIG. 7 is a schematic sectional view of one embodiment of a more general apparatus for detecting snoring and/or other respiratory parameters in accordance with the present invention; -
FIG. 8 shows the volume of air breathed by a patient in normal sleep contrasted with the declining volume breathed as the patient starts to hypoventilate; -
FIG. 9 shows the different pressure waves generated by the extraneous high frequency noise associated with air flow from the blower and the pressure waves of interest indicative of snoring and breathing and the composite wave comprising the contribution of all sources of pressure wave; -
FIG. 10 shows how the composite wave from the pressure sensor is filtered to generate information on the parameters of interest; -
FIG. 11 shows in schematic form how any or all of these parameters can be used either alone or by reference to control data to provide a signal to a Motor Speed Controller; -
FIG. 12 shows in schematic form how the computing system which analyzes the parameters of interest with reference to control patient data controls motor speed and air pressure delivered to the patient; and, -
FIG. 13 shows an example of how the pressure wave generated by snoring progressively increases/ decreases the air pressure delivered to the patient as directed by the computing system. -
FIG. 1 a illustrates asnoring detection device 10 comprising a microphone 11, in sound communication with thecontainer 12 of a nose mask. Air, being inhaled by the patient, enters thenasal passageways 14 through theopening 13 in thenose mask 12 and is exhaled in the reverse direction. As the airway extends from the source of snoring sounds within the patient's body, through thenasal passages 14 and out of theopening 13 in the nasal mask, the microphone 11 is ideally located to take advantage of the natural stethoscope formed by the enclosed airway. Hence the snoring and breathing sounds are focused and concentrated by this arrangement. Alternatively, the microphone 11 may be located within, or attached externally of, a nasal prong device as illustrated inFIG. 1 b. Thedetection device 10 can be used in a diagnostic device or a feedback control. In the case of thedetection device 10 being used in diagnostic equipment there is connected to the microphone 11 an electronic processor/recorder which records signals from the microphone 11 either on a time basis or after preprogrammed processing so as to record for example tables of indexes such as the number of apneic episodes, their duration, etc. The recorded data can then be reviewed by the physician for diagnosis. -
FIG. 2 a shows a graph representing sound amplitudes recorded from thesnoring detection device 10. The major calibration in the time scale direction represents two minutes. - The effect of blower motor noise can be diminished or completely removed by setting a low gain on the recording device or passing the signal through an amplitude filter to effectively ignore all sounds below a particular minimum amplitude or by passing the signals through a low pass frequency filter to effectively ignore sounds above its cut-off frequency. An alternative method is to use a sound attenuator in the air line proximate the blower.
- Part A of
FIG. 2 a is indicative of normal breathing, part B indicates soft to moderate snoring, part C shows constant loud snoring and part E shows periods of silence punctuated by snoring. In section D of the chart ofFIG. 2 a, it can be seen that the breathing sound intensity rises and falls. This is indicative of obstructive hypopnea, a condition in which the breath-by-breath intensity decreases progressively, and then increases. In this pattern the decreasing intensity of the snoring occurs when the upper airway is almost, but not entirely, sucked closed by strong inspiratory efforts. This pattern is a “pre-apneic” pattern. - The following part E, is therefore quickly interpreted by a skilled physician as being indicative of sleep apnea, with periods of airway occlusion which terminate with one or more loud breathing sounds followed by further occlusions.
- The correlation between snoring patterns and arterial oxygen is shown in
FIG. 2 b. Clearly the snoring patterns are an accurate parameter for detecting imminent apneic episodes, and more importantly periods of low oxygen supply to the brain and other organs. - Thus recorded information derived from the signal of the
device 10 can be used for diagnostic purposes, such as initial diagnosis of sleep apnea, without the need for the patient to stay overnight at an observation facility. The sound patterns can be analyzed by a programmed microprocessor within the diagnostic unit so as to record tables of indexes such as number of apneic episodes, their duration and time of occurrence. This is of economic significance because the cost of one overnight observation is comparable to the purchase price of a CPAP device. - The nose prongs and
mask 12 are convenient forms of containers for themonitor device 10 however the container could take any other convenient form. - Furthermore, diagnostic apparatus in accordance with the present invention is suited for use by a patient with minimal supervision and therefore may be used successfully at home, the recorded diagnostic information being conveniently presented for expert analysis.
- In
FIG. 3 , a CPAP apparatus embodying the invention is illustrated. The CPAP unit comprises amotor 20 which drives ablower 21. The speed of themotor 20 is controlled by an electronicspeed control unit 23. As an increase in motor speed also increases the blower speed which in turn increases the output air pressure of theblower 21, the speed control unit can be manipulated to vary the output pressure of theblower 21. The CPAP device also includes a snoring detection means 22 wherein sounds are detected by a microphone 11. In its most general form, the snoring detection means 22 is a pressure detection means and microphone 11 is a differential pressure sensor. The snoring detection means 22 is conveniently in the form of the previously describeddevice 10. Electrical impulses are fed from said microphone 11 to an amplifier/filter/processor unit 26 which generates an electrical signal when snoring sounds occur. The motor speed control means is electrically connected to thesnoring detection device 22 and increases the speed of theelectric motor 20 by an analogue means in response to the electrical signal generated by the snoring detection device. Accordingly, the output pressure of the CPAP unit increases in response to detection of snoring. - When a snore or sequence of snores is detected by the snoring detection means 22 a signal is generated. The
speed control unit 23 increases the speed of the fan motor and the output pressure is increased. As snoring is caused by vibration of the soft palate, it is there-fore indicative of an unstable airway and, as previously described, is a warning signal of the imminence of upper airway occlusion in patients that suffer obstructive sleep apnea. Snoring is itself undesirable not only as it is a disturbance to others but it is strongly believed to be connected with hypertension. If the resultant increase in CPAP pressure is sufficient to completely stabilize the airway, snoring will cease. If a further snoring sound is detected, the CPAP pressure is increased again. This process is repeated until the upper airway is stabilized and snoring ceases. Hence, the occurrence of obstructive apnea can be eliminated by application of a minimum appropriate pressure at the time of use. - In order to ensure that the CPAP pressure is maintained at a level as low as practicable to prevent the onset of apnea, the preferred embodiment also includes a means to decrease the pressure if an extended period of snore free breathing occurs. For example, this can be done by automatically reducing the CPAP pressure at a gradual rate as long as snoring is not detected. The rate at which the CPAP pressure is decreased in the absence of snoring is preferably much less than the rate at which it is increased when snoring is detected. This can be achieved, for example, by the amplifier/filter/
processor unit 26, in the absence of an electronic signal from the microphone 11, continuously gradually reducing the blower speed over a period of time but increasing the blower speed in incremental steps each time a snore is detected by the microphone 11. - In use, a patient may connect himself to the CPAP unit and go to sleep. The CPAP pressure is initially at a minimum operating value of, for example, approximately 3 cm H2O gauge pressure so as not to cause the previously mentioned operational problems of higher initial pressures. Not until some time after going to sleep, and the patient's body relaxes, will the airway start to become unstable and the patient start to snore. The
detection apparatus 22 will then respond to a snore, or snore pattern, and via theprocessor 26 increase the motor speed such that CPAP pressure increases by 1 cm H2O for each snore detected. The CPAP pressure can be increased relatively rapidly, if the patient's condition so requires, to a working pressure of the order of 8-10 cm, which is a typical requirement. An upper pressure limiting device can be incorporated for safety. Also, for ease of monitoring the variation over time in patient conditions, a parameter such as pressure output can be recorded in some convenient retrievable form for periodic study by the physician. - If for example in the early stages of sleep some lesser CPAP pressure will suffice, the CPAP unit of the present invention will not increase the pressure until needed, that is, unless the airway becomes unstable and snoring recommences no increase is made to the airway pressure.
- By continuously decreasing the CPAP pressure at a rate of, for example, 1 cm H2O each 15 mins. in the absence of snoring the pressure is never substantially greater than that required to prevent apnea. However, when a snore or snoring pattern is detected, the decreasing CPAP pressure mode will be completely overwhelmed by a greater increase, about 1 cm H2O per detected snore or snoring pattern. Once a stable sleeping pattern is achieved, the preferred embodiment will then continually test to ensure that the CPAP pressure is as low as is practicable. Should the CPAP pressure be decreased to such an extent that the upper airway becomes unstable and snoring recommences, the pressure is reincreased to ensure that apnea is prevented, it being remembered that the snoring pattern is a precursor to apneic episodes.
- The flexibility of the invention can be illustrated by the following example.
- It is known that a patient's maximum propensity to suffer sleep apnea occurs during REM sleep. An airway that was otherwise stable at a given CPAP pressure may become unstable during REM sleep. Should this happen snoring will set in before apnea occurs. In such circumstances, the present invention will raise the CPAP pressure in response to the snoring, thus preventing the onset of apnea. The REM sleep passes, the patient's airway becomes more stable and the higher airway pressure is no longer required. In such circumstances, the CPAP pressure will be gradually reduced until the first sign of snoring reoccurs at which point the pressure will again be increased.
- A patient normally makes at least one loud snort or snoring sound at the end of an occurrence of apnea and the present invention will respond to this unusually loud sound to increase the CPAP pressure. Thus even if apnea should occur without the usual precursor of snoring, the airway pressure can still be adjusted upward in response to the abnormally loud breathing sounds generated at the end of the apneic period.
- The present invention thus provides a CPAP device which modifies the CPAP pressure according to variations in a patient's requirements throughout an entire sleep period. It will be clear to those skilled in the art that the present invention can cope with the variation in airway pressure requirements such as may occur during a single sleep period, it will also be able to cope with variations in CPAP pressure requirements due to a general improvement or deterioration in a patient's general condition as may take place over a longer period of time.
-
FIG. 4 illustrates in block form the circuitry of the CPAP device ofFIG. 3 . Asnoring detection apparatus 22 is comprised of the microphone 11 attached to thenose mask 12. The electrical signals of the microphone 11 are sent to a Filter/Amplifier/Processor 26 which generates a control signal indicative of the recognition of a snoring pattern equivalent to a predetermined pattern. - Such control signals are sent to a
feedback speed controller 23. Thespeed controller 23 comprises a ramp generator and voltage tofrequency converter 24 for control of a switch mode power supply (SMPS) 15, which provides the power to run themotor 20 turning theblower 21. - The maximum output of the
SMPS 15, and therefore the maximum pressure delivered to themask 12, is limited by apressure time control 17. - In another aspect of the invention, shown in
FIGS. 5 and 6 , there is provided acontrol circuit 33 comprising adelay control 25, atimer 24, a switch mode power supply (SMPS) 15, and anupper pressure control 17. In the timer 24 a square wave pulse train, is generated where the duty ratio can be varied by thedelay control 25. This pulse train, in the form of a current, is applied to a capacitor 19 to obtain a ramp voltage. Hence the output of thetimer 24 and the input of theSMPS 15 is a voltage increasing with respect to time. The output of theSMPS 15, and therefore the motor voltage and speed, follow the input. - The minimum blower speed is preset so as to give effective operation of the
air blower 21 and a minimum airway pressure which is comfortable to the patient. Typically a minimum pressure of 3-5 cm H2O will have negligible effect on most patients. - The desired maximum airway pressure, being the intended therapeutic airway pressure, is set by adjusting the
variable control 17. The magnitude of this pressure will vary according to the requirements of the individual patient but will typically be in the range 10-20 cm H2O. - When the
delay control 25 is not set to zero minutes, the apparatus commences operation at the minimum motor speed and gradually increases the motor speed over a period of time selected before reaching the maximum preselected speed according to the previous adjustment ofcontrol 17. When thedelay control 25 is set to zero minutes airway pressure comes up to the full level as set byadjustment 17 in a short period of time. - By this arrangement sleep is commenced with a low and comfortable air pressure but then automatically increased after a selectable period of time to the desired therapeutic pressures so as to provide an adequate pneumatic splint to the airway passages during the latter stages of sleep when apnea is likely.
- A convenient way to gauge whether a correct therapeutic, or maximum, pressure has been selected is to use the
diagnostic device 10 of this invention while the patient is undergoing CPAP therapy. Should the recorded data show no signs of apneic periods then the setting may be assumed to be adequate at least for the patient when in a similar physical condition. Another long term benefit can be gained by recording the pressure level applied to the patient during sleep periods in which CPAP is applied using the feedback device of this invention. By making such recordings spaced over a period of time the skilled physician can diagnose any long term changes in the patient's condition. -
FIG. 7 illustrates a pressure detection device comprising a pressure sensor, in pressure communication with the container of a nose mask. Air, being inhaled by the patient, enters the nasal passageways through the opening in the nose mask and is exhaled in the reverse direction. The pressure sensor is ideally located to detect both pressure waves generated by the patient snoring or by variations in the respiration rate or pattern of the patient. Hence the snoring sounds and breathing variations are captured and concentrated by this arrangement. Alternatively, the pressure sensor may be located within or attached externally to a nasal prong device. - The detection device can be used in a diagnostic device or a feedback control. In the case of the detection device being used in diagnostic equipment there is connected to the pressure sensor a computing system as shown in
FIG. 12 which analyses and records signals from the pressure sensor in a data store. These signals can be stored on a real time basis or after further processing in the form of indexes such as the number of apneic episodes, the number of hypopneas, their duration, etc. The recorded data can then be reviewed by a physician for diagnosis. -
FIG. 9 shows the sources of pressure waves detected by the pressure sensor. The high frequency wind noise is generated by the air blower and is extraneous for the purposes of interpreting the condition of the patient. Pressure waves at a frequency of 30 to 50 Hz are indicative of snoring and could be detected by using a particular embodiment of the pressure sensor in the form of a microphone. Disturbances in breathing pattern are detected at a very low frequency relating to breathing rate of approximately 0.5 Hz. The output of the sensor is a composite of the pressure waves generated by all these sources. -
FIG. 10 Shows a schematic electronic circuit which first amplifies the output of the pressure sensor before passing it through a series of filters to separate the pressure waves at the frequencies of interest. The high frequency wind noise is eliminated and signals indicative of snoring and breathing are obtained. The breathing signal is further processed to give information on breathing rate, flow rate and volume per breath. -
FIG. 2 a shows a graph representing sound amplitudes obtained from the snoring signal filtered from the pressure detection device. The major calibration in the time scale direction represents two minutes. - The effect of blower motor noise can be diminished or completely removed by setting a low gain on the recording device or passing the signal through an amplitude filter to effectively ignore all sounds below a particular minimum amplitude or by passing the signals through a low pass frequency filter to effectively ignore sounds above its cut-off frequency. An alternative method is to use a sound attenuator in the air line proximate the blower.
- Part A of
FIG. 2 a is indicative of normal breathing, part B indicates soft to moderate snoring, part C shows constant loud snoring and part E shows periods of silence punctuated by snoring. In section D of the chart ofFIG. 2 a, it can be seen that the breathing sound intensity rises and falls. This is indicative of obstructive hypopnea, a condition in which the breath-by-breath intensity decreases progressively, and then increases. In this pattern the decreasing intensity of the snoring occurs when the upper airway is almost, but not entirely, sucked closed by strong inspiratory efforts. This pattern is a “pre-apneic” pattern. - The following part E is therefore quickly interpreted by a skilled physician as being indicative of sleep apnea, with periods of airway occlusion which terminate with one or more loud breathing sounds followed by further occlusions.
- The correlation between snoring patterns and arterial oxygen is shown in
FIG. 2 b. Clearly the snoring patterns are an accurate parameter for detecting imminent apneic episodes, and more importantly periods of low oxygen supply to the brain and other organs. -
FIG. 8 shows the volume of air inhaled (or exhaled) by the patient with each breath as determined by the volume integrator from the breathing signal filtered from the pressure sensor. Part A ofFIG. 8 shows normal breathing, while Part B shows shallow breathing or hypoventilation. A decreasing pattern of air volume inspired by the patient can be indicative of the imminent onset of apnea or can be undesirable as the patient's arterial oxygen level falls below an acceptable level. -
FIG. 10 shows how the processing system can be set up to respond when the average volume of a predefined number of the most recent breaths falls below the volume of a predefined long term average volume for that patient. -
FIG. 11 shows how the computing system can accept and analyze any or all of the processed signals from the pressure sensor and using the signal, alone or by comparison with control data for that patient, control the speed of the blower to vary the pressure of the air delivered to the patient's nose mask. -
FIG. 13 shows an example of how the signal indicative of snoring alone is received by the computing system and the computing system increases pressure in accordance with predefined procedure. - Thus, the recorded information derived from the signal of the pressure sensor can be used for diagnostic purposes, such as initial diagnosis of sleep apnea or hypopnea, without the need for the patient to stay overnight in an observation facility, the sound and breathing patterns can be analyzed by a programmed microprocessor or computing system as shown in
FIG. 12 so as to record tables of indexes such as number of hypopneas and/or apneic episodes, their duration and time of occurrence. This is of economic significance because the cost of one overnight observation is comparable to the purchase price of a CPAP device. - Furthermore, diagnostic apparatus in accordance with the present invention is suited for use by a patient with minimal supervision and therefore may be used successfully at home, the recorded diagnostic information being conveniently presented for expert analysis.
- In
FIG. 3 , a CPAP apparatus embodying the invention is illustrated. The CPAP unit comprises amotor 20 which drives ablower 21. The speed of themotor 20 is controlled by an electronicspeed control unit 23. As an increase in motor speed also increases blower speed which in turn increases the output air pressure ofblower 21, the speed control unit can be manipulated to vary the output pressure of theblower 21. The CPAP device also includes a pressure detection means 22 wherein pressure waves in the form of electrical signals are detected by a pressure sensor 11. The pressure detection means 22 is conveniently in the form of the previously described device illustrated inFIG. 7 . Electrical signals are fed from said sensor 11 to an amplifier/filter/processor unit 26 which may be inside or outside the blower unit casing and generates an electrical signal when snoring sounds and/or deviations of breathing parameters from predetermined values occur. The motor speed control means is electrically connected to thepressure detection device 22 while being electrically isolated from the patient and increases the speed of theelectric motor 20 by an analogue means in response to the electrical signal generated by the pressure detection device. Accordingly, the output pressure of the CPAP unit increases in response to detection of snoring and/or deviations of breathing parameters from predetermined values. - The method of operation can be illustrated by considering the effect of a snore or sequence of snores detected by the pressure sensor as shown in
FIG. 13 . When a snore or sequence of snores is detected by the snoring detection means 22 a signal is generated. Thespeed control unit 23 increases the speed of the fan motor and the output pressure is increased. As snoring is caused by vibration of the soft palate, it is therefore indicative of an unstable airway and, as previously described, is a warning signal of the imminence of upper airway occlusion in patients that suffer obstructive sleep apnea. Snoring is itself undesirable not only as it is a disturbance to others but it is strongly believed to be connected with hypertension. If the resultant increase in CPAP pressure is sufficient to completely stabilize the airway, snoring will cease. If a further snoring sound is detected, the CPAP pressure is increased again. This process is repeated until the upper airway is stabilized and snoring ceases. Hence, the occurrence of obstructive apnea can be eliminated by application of a minimum appropriate pressure at the time of use. - In order to ensure that the CPAP pressure is maintained at a level as low as practicable to prevent the onset of apnea, the preferred embodiment also includes a means to decrease the pressure if an extended period of snore free breathing occurs. For example, this can be done by automatically reducing the CPAP pressure at a gradual rate as long as snoring is not detected. The rate at which the CPAP pressure is decreased in the absence of snoring is preferable much less than the rate at which it is increased when snoring is detected. This can be achieved, for example, by the amplifier/filler/
processor unit 26, the absence of an electronic signal from the pressure sensor 11, continuously gradually reducing the blower speed over a period of time but increasing the blower speed in incremental steps each time a snore is detected by the pressure sensor 11. - A predetermined deviation of any or all of the breathing parameters, flow rate, volume or breathing rate from a predetermined common value can generate a signal in a similar way. Hence a fall in the volume of air inspired or expired per breath below a preset value can generate a signal which increases the speed of the fan motor and increases the output pressure. After the breathing volume has returned to the control setting for a predetermined period, the fan motor speed will be decreased slowly until a snore or unacceptable breathing pattern is again detected by the pressure sensor.
- In use a patient may connect himself to the CPAP unit and go to sleep. Only one connection is required apart from the normal CPAP circuit and this is simply the connection from the pressure sensor to the amplifier/filter/processor unit. No electrodes or other sensors have to be attached to the patient's body as the pressure sensor is conveniently located in the CPAP mask. The CPAP pressure is initially at a minimum comfortable operating value of, for example, approximately 3 cm H2O gauge pressure so the as not to cause the previously mentioned operational problems of higher initial pressures. Not until some time after going to sleep, and the patient's body relaxes, will the airway start to become unstable and the patient start to snore or exhibit abnormal breathing patterns. The
detection apparatus 22 will a respond to the snore, or snore pattern or abnormal breathing pattern and via theprocessor 26 increase the motor speed such that CPAP pressure increases by 1 cm H2O for each snore or predetermined abnormality in breathing pattern detected. The CPAP pressure can be increased relatively rapidly, if the patient's condition so requires, to a working pressure of the order of 8-10 cm H2O, which is a typical requirement. An upper pressure limiting device can be incorporated for safety. Also, for ease of monitoring the variation over time in patient conditions, a parameter such as pressure output can be recorded in some convenient retrievable form for periodic study by the physician. - If for example in the early stages of sleep some lesser CPAP pressure will suffice, the CPAP unit of the present invention will not increase the pressure until needed, that is, unless the airway becomes unstable and snoring or abnormal breathing patterns recommence, no increase is made to the airway pressure.
- By continuously decreasing the CPAP pressure as a rule of, for example, 1 cm H2O each 15 mins in the absence of snoring or abnormal breathing patterns, the pressure is never substantially greater than that required to prevent apnea or other undesirable respiratory conditions. However, when a snore, or snoring patterns or abnormal breathing pattern, is detected the decreasing CPAP pressure mode will be completely overwhelmed by a greater increase, about 1 cm H2O per predetected snore or snoring pattern or predetermined abnormality in breathing pattern. Once a stable sleeping pattern is achieved, the preferred embodiment will a continually test to ensure that the CPAP pressure is as low as is practicable. Should the CPAP pressure be decreased to such an extent that the upper airway becomes unstable and snoring or unacceptable breathing patterns recommence, the pressure is reincreased to ensure that apnea is prevented, it being remembered that the snoring or abnormal breathing pattern is a precursor to apneic episodes or other undesirable respiratory conditions such as shallow breathing or hypopnea.
- The flexibility of the invention can be illustrated by the following example.
- It is known that a patient's maximum propensity to suffer sleep apnea occurs during REM sleep. An airway that was otherwise stable at a given CPAP pressure may become unstable during REM sleep. Should this happen snoring and/or particular deviations in breathing patterns will set in before apnea occurs. In such circumstances, the present invention will raise the CPAP pressure in response to the snoring or deviation in breathing patterns, thus preventing the onset of apnea or other undesirable respiratory condition. After the REM sleep passes, the patient's airway becomes more stable and the higher airway pressure is no longer required. In such circumstances, the CPAP pressure will be gradually reduced until the first sign of snoring and/or unacceptable breathing patterns reoccurs at which point the pressure will again be increased.
- A patient normally makes at least one loud snort or snoring sound at the and of an occurrence of apnea and the present invention will respond to this unusually loud sound to increase the CPAP pressure. Thus even if apnea should occur without the usual precursor of snoring or abnormal breathing pattern, the airway pressure can still be adjusted upward in response to the abnormally loud breathing sounds generated at the end of the apneic period.
- The present invention thus provides a CPAP device which modifies the CPAP pressure according to variations in a patient's requirements throughout an entire sleep period. It will be clear to those skilled in the art that the present invention can cope with the variation in airway pressure requirements such as may occur during a single sleep period, it will also be able to cope with variations in CPAP pressure requirements due to a general improvement or deterioration in a patient's general condition as may take place over a longer period of time.
-
FIG. 12 illustrates in block form the circuitry of the feedback system. A pressure detection apparatus is provided either integral with or attached to the CPAP mask worn by the patient. The electrical signals from the pressure transducer are amplified and filtered to provide pressure waves of the desired frequencies indicative of snoring and breathing. The pressure wave indicative of breathing is further processed to generate signals indicative of flow rate, volume and breathing rate. Any or all signals are fed to a computing system which analyses the signals for deviation from predetermined values or patterns. The computing system may itself calculate control values of patterns for each patient based on moving average values or such values or patterns will be pre-programmed into the computing system. - Where signals deviate from predetermined values or patterns the computer system generates a signal which is sent to the feedback speed controller on the blower motor. Increasing blower speed increases the air pressure and level of CPAP treatment delivered to the patient. The speed and pressure are increased until signals detected from the patient are within the acceptable range of control values or patterns and the speed and pressure are maintained at that level.
- The maximum output' of the blower can be limited by limiting the signal from the computer to correspond to a predetermined motor speed.
- A convenient way to gauge whether a correct therapeutic or maximum, pressure has been selected is to use the diagnostic device shown in
FIG. 7 of this invention while the patient is undergoing CPAP therapy. Should the recorded data show no signs of apneic periods then the setting may be assumed to be adequate at least for the patient when in a similar physical condition. Another long term benefit can be gained by recording the pressure level applied to the patient during sleep periods in which CPAP is applied using the feedback device of this invention. By making such recordings spaced over a period of time the skilled physician can diagnose any long term changes in the patient's condition. - It is to be understood that while the invention has been described above in conjunction with preferred specific embodiments, the description and examples are intended to illustrate and not limit the scope of the invention, which is defined by the scope of the appended claims.
Claims (8)
1-24. (canceled)
25. An apparatus useful in the diagnosis of sleep-disordered breathing of a patient, said apparatus comprising means for monitoring a plurality of respiratory parameters of said patient while sleeping substantially unsupervised in a non-clinical setting, said monitoring providing a signal indicative of the parameters being monitored, said monitoring means being fitted to a nasal mask adapted to be worn by said patient to cover said patient's mouth.
26. A method useful in the diagnosis of sleep apnea of a patient, said method comprising the steps of:
a) providing a monitoring apparatus for monitoring at least one respiratory parameter of said patient while sleeping substantially unsupervised in a non-clinical setting, said monitoring apparatus being in communication with a nasal mask and said monitoring apparatus being configured for non-clinical use to provide a signal indicative of the parameter being monitored;
b) monitoring at least one respiratory parameter of said patient using said monitoring apparatus; and
c) providing said signal to a sleep disorders clinical professional in the diagnosis of said sleep apnea.
27. A method of monitoring one or more respiratory parameters of a patient while sleeping substantially unsupervised in a non-clinical setting, said one or more respiratory parameters being useful in the diagnosis of sleep apnea, said method comprising the steps of:
a) providing a nasal mask to substantially surround said patient's nasal passages;
b) providing said nasal mask with access to a source of breathable gas to said patient;
c) providing said nasal mask with a sensor capable of measuring one or more respiratory parameters and transmitting one or more signals indicative of values of said parameters; and
d) providing additional sensors used in conjunction with said sensor for monitoring a non-respiratory parameter.
28. A method in accordance with claim 27 wherein said non-respiratory parameter is pulse oximetry.
29. A method of diagnosing whether a patient has sleep apnea, comprising the steps of:
providing the patient with apnea monitoring apparatus configured for home use to monitor at least one parameter of breathing of said patient, said monitoring apparatus being in communication with a nasal mask configured to be worn over the nasal passages of the patient;
allowing the patient to sleep at home while being monitored by said sleep apnea monitoring apparatus;
generating data indicative of said breathing parameter during the patient's home sleep;
analyzing said breathing parameter data; and
diagnosing the presence of sleep apnea on the basis of said breathing parameter data.
30. A method of diagnosing a patient for the condition of sleep apnea comprising the steps of:
providing said patient with an apparatus configured for home monitoring of the frequency and severity of the patient's snoring, hypopnea and apnea, said apparatus being in communication with a nasal mask;
generating data at said patient's home indicative of the frequency and severity of said patient's snoring, hypopnea and apnea; and
diagnosing the presence of sleep apnea on the basis of said data.
31. A method for determining by home monitoring whether a patient requires diagnosis of sleep apnea in a sleep clinic comprising the steps of:
providing said patient with an apparatus configured for home monitoring of data indicative of the frequency and severity of said patient's snoring, hypopnea and apnea, said apparatus being in communication with a nasal mask; and
analyzing said data for the presence of snoring, hypopnea and apnea patterns during said home monitoring to determine whether the patient requires a clinic environment for further observation and testing.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/554,378 US20070051371A1 (en) | 1987-06-26 | 2006-10-30 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
Applications Claiming Priority (17)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AUPI2730 | 1987-06-26 | ||
AUPI273087 | 1987-06-26 | ||
AUPI423487 | 1987-09-08 | ||
AUPI4234 | 1987-09-08 | ||
WOPCT/AU88/00215 | 1988-06-27 | ||
PCT/AU1988/000215 WO1988010108A1 (en) | 1987-06-26 | 1988-06-27 | Device for monitoring breathing during sleep and control of cpap treatment |
US45775789A | 1989-12-21 | 1989-12-21 | |
US54810890A | 1990-07-05 | 1990-07-05 | |
US7892692A | 1992-05-27 | 1992-05-27 | |
US10055693A | 1993-07-30 | 1993-07-30 | |
US38574295A | 1995-02-08 | 1995-02-08 | |
US65474296A | 1996-05-29 | 1996-05-29 | |
US83846297A | 1997-04-07 | 1997-04-07 | |
US08/934,176 US6635021B1 (en) | 1987-06-26 | 1997-09-19 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US10/050,163 US7004908B2 (en) | 1987-06-26 | 2002-01-18 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US11/186,695 US7141021B2 (en) | 1987-06-26 | 2005-07-21 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US11/554,378 US20070051371A1 (en) | 1987-06-26 | 2006-10-30 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/186,695 Continuation US7141021B2 (en) | 1987-06-26 | 2005-07-21 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
Publications (1)
Publication Number | Publication Date |
---|---|
US20070051371A1 true US20070051371A1 (en) | 2007-03-08 |
Family
ID=27507303
Family Applications (6)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US07/806,157 Expired - Lifetime US5199424A (en) | 1987-06-26 | 1991-12-12 | Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled |
US07/892,692 Expired - Lifetime US5245995A (en) | 1987-06-26 | 1992-05-27 | Device and method for monitoring breathing during sleep, control of CPAP treatment, and preventing of apnea |
US10/050,163 Expired - Fee Related US7004908B2 (en) | 1987-06-26 | 2002-01-18 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US10/086,444 Expired - Fee Related US6770037B2 (en) | 1987-06-26 | 2002-03-04 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US11/186,695 Expired - Fee Related US7141021B2 (en) | 1987-06-26 | 2005-07-21 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US11/554,378 Abandoned US20070051371A1 (en) | 1987-06-26 | 2006-10-30 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
Family Applications Before (5)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US07/806,157 Expired - Lifetime US5199424A (en) | 1987-06-26 | 1991-12-12 | Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled |
US07/892,692 Expired - Lifetime US5245995A (en) | 1987-06-26 | 1992-05-27 | Device and method for monitoring breathing during sleep, control of CPAP treatment, and preventing of apnea |
US10/050,163 Expired - Fee Related US7004908B2 (en) | 1987-06-26 | 2002-01-18 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US10/086,444 Expired - Fee Related US6770037B2 (en) | 1987-06-26 | 2002-03-04 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
US11/186,695 Expired - Fee Related US7141021B2 (en) | 1987-06-26 | 2005-07-21 | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient |
Country Status (1)
Country | Link |
---|---|
US (6) | US5199424A (en) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20080053442A1 (en) * | 1994-06-03 | 2008-03-06 | Ric Investments, Llc | Method and Apparatus for Providing Positive Airway Pressure to a Patient |
US20080251079A1 (en) * | 2007-04-13 | 2008-10-16 | Invacare Corporation | Apparatus and method for providing positive airway pressure |
US20100065055A1 (en) * | 2003-06-23 | 2010-03-18 | Invacare Corporation | System and method for providing a breathing gas |
US20110209706A1 (en) * | 2008-10-16 | 2011-09-01 | Koninklijke Philips Electronics N.V. | Ventilator with limp mode |
US8261742B2 (en) | 2007-08-23 | 2012-09-11 | Invacare Corporation | Method and apparatus for adjusting desired pressure in positive airway pressure devices |
US8640701B2 (en) | 2000-09-28 | 2014-02-04 | Invacare Corporation | Carbon dioxide-based bi-level CPAP control |
US11844605B2 (en) | 2016-11-10 | 2023-12-19 | The Research Foundation For Suny | System, method and biomarkers for airway obstruction |
Families Citing this family (511)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5199424A (en) | 1987-06-26 | 1993-04-06 | Sullivan Colin E | Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled |
US5522382A (en) | 1987-06-26 | 1996-06-04 | Rescare Limited | Device and method for treating obstructed breathing having a delay/ramp feature |
US5259373A (en) * | 1989-05-19 | 1993-11-09 | Puritan-Bennett Corporation | Inspiratory airway pressure system controlled by the detection and analysis of patient airway sounds |
USRE35295E (en) * | 1989-09-22 | 1996-07-16 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5239995A (en) * | 1989-09-22 | 1993-08-31 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5632269A (en) * | 1989-09-22 | 1997-05-27 | Respironics Inc. | Breathing gas delivery method and apparatus |
US5458137A (en) * | 1991-06-14 | 1995-10-17 | Respironics, Inc. | Method and apparatus for controlling sleep disorder breathing |
US6085747A (en) * | 1991-06-14 | 2000-07-11 | Respironics, Inc. | Method and apparatus for controlling sleep disorder breathing |
FR2680467B1 (en) * | 1991-08-21 | 1997-04-04 | Intertechnique Sa | RESPIRATORY PROTECTION EQUIPMENT AGAINST POLLUTANTS. |
US6629527B1 (en) * | 1991-10-17 | 2003-10-07 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5477852A (en) * | 1991-10-29 | 1995-12-26 | Airways Ltd., Inc. | Nasal positive airway pressure apparatus and method |
US5687715A (en) * | 1991-10-29 | 1997-11-18 | Airways Ltd Inc | Nasal positive airway pressure apparatus and method |
US7013892B2 (en) * | 1991-11-01 | 2006-03-21 | Ric Investments, Llc | Sleep apnea treatment apparatus |
DE69231157T2 (en) * | 1991-11-14 | 2001-02-15 | Univ Technologies Int | AUTOMATIC SYSTEM FOR GENERATING CONTINUOUS POSITIVE AIRWAY PRESSURE |
EP1149603A3 (en) | 1991-12-20 | 2003-10-22 | Resmed Limited | Ventilator for continuous positive airway pressure breathing (CPAP) |
US5803066A (en) * | 1992-05-07 | 1998-09-08 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5335654A (en) * | 1992-05-07 | 1994-08-09 | New York University | Method and apparatus for continuous adjustment of positive airway pressure for treating obstructive sleep apnea |
US5490502A (en) * | 1992-05-07 | 1996-02-13 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5645054A (en) * | 1992-06-01 | 1997-07-08 | Sleepnet Corp. | Device and method for the treatment of sleep apnea syndrome |
WO1993024169A1 (en) * | 1992-06-01 | 1993-12-09 | Cotner Ronald L | Demand positive pressure airway system for apnea treatment |
US5343878A (en) * | 1992-06-08 | 1994-09-06 | Respironics Inc. | Pressure application method |
FR2692152B1 (en) * | 1992-06-15 | 1997-06-27 | Pierre Medical Sa | BREATHING AID, PARTICULARLY FOR TREATING SLEEP APNEA. |
US6223064B1 (en) | 1992-08-19 | 2001-04-24 | Lawrence A. Lynn | Microprocessor system for the simplified diagnosis of sleep apnea |
US6342039B1 (en) | 1992-08-19 | 2002-01-29 | Lawrence A. Lynn | Microprocessor system for the simplified diagnosis of sleep apnea |
US20050062609A9 (en) * | 1992-08-19 | 2005-03-24 | Lynn Lawrence A. | Pulse oximetry relational alarm system for early recognition of instability and catastrophic occurrences |
US7758503B2 (en) | 1997-01-27 | 2010-07-20 | Lynn Lawrence A | Microprocessor system for the analysis of physiologic and financial datasets |
WO1994004071A1 (en) * | 1992-08-19 | 1994-03-03 | Lynn Lawrence A | Apparatus for the diagnosis of sleep apnea |
US7081095B2 (en) * | 2001-05-17 | 2006-07-25 | Lynn Lawrence A | Centralized hospital monitoring system for automatically detecting upper airway instability and for preventing and aborting adverse drug reactions |
US5517983A (en) * | 1992-12-09 | 1996-05-21 | Puritan Bennett Corporation | Compliance meter for respiratory therapy |
US5438980A (en) * | 1993-01-12 | 1995-08-08 | Puritan-Bennett Corporation | Inhalation/exhalation respiratory phase detection circuit |
US5813399A (en) * | 1993-03-16 | 1998-09-29 | Puritan Bennett Corporation | System and method for closed loop airway pressure control during the inspiratory cycle of a breath in a patient ventilator using the exhalation valve as a microcomputer-controlled relief valve |
US5431158A (en) * | 1993-04-20 | 1995-07-11 | Tirotta; Christopher F. | Endoscopy breathing mask |
US5560354A (en) | 1993-06-18 | 1996-10-01 | Rescare Limited | Facial masks for assisted respiration or CPAP |
EP0722352B1 (en) | 1993-10-01 | 2000-05-03 | Minnesota Mining And Manufacturing Company | Speech transmission adaptor for use with a respirator mask |
JPH0725263U (en) * | 1993-10-22 | 1995-05-12 | 本田技研工業株式会社 | Evaporative fuel treatment system for internal combustion engine for vehicles |
EP2324765B1 (en) * | 1993-11-05 | 2015-10-07 | ResMed Limited | Control of CPAP treatment |
US6675797B1 (en) | 1993-11-05 | 2004-01-13 | Resmed Limited | Determination of patency of the airway |
DE69422900T2 (en) * | 1993-12-01 | 2000-06-08 | Resmed Ltd | Continuous positive airway pressure (CPAP) device |
US6237593B1 (en) * | 1993-12-03 | 2001-05-29 | Resmed Limited | Estimation of flow and detection of breathing CPAP treatment |
AUPM279393A0 (en) * | 1993-12-03 | 1994-01-06 | Rescare Limited | Estimation of flow and detection of breathing in cpap treatment |
US5456264A (en) * | 1994-03-31 | 1995-10-10 | Universite Laval | Accuracy of breath-by-breath analysis of flow volume loop in identifying flow-limited breathing cycles in patients |
US5671733A (en) * | 1994-04-21 | 1997-09-30 | Snap Laboratories, L.L.C. | Method of analyzing sleep disorders |
AU758904B2 (en) * | 1994-05-20 | 2003-04-03 | New York University | Method for diagnosing a patient having sleep apnea |
AU728177B2 (en) * | 1994-05-20 | 2001-01-04 | New York University | Method for optimizing continuous positive airway pressure for treatment of obstructive sleep apnea |
US5794615A (en) * | 1994-06-03 | 1998-08-18 | Respironics, Inc. | Method and apparatus for providing proportional positive airway pressure to treat congestive heart failure |
US5537994A (en) | 1994-06-03 | 1996-07-23 | Thornton; W. Keith | Combination face mask and dental device for improved breathing during sleep |
US5535738A (en) * | 1994-06-03 | 1996-07-16 | Respironics, Inc. | Method and apparatus for providing proportional positive airway pressure to treat sleep disordered breathing |
US6105575A (en) | 1994-06-03 | 2000-08-22 | Respironics, Inc. | Method and apparatus for providing positive airway pressure to a patient |
US5983892A (en) | 1994-06-03 | 1999-11-16 | Thornton; W. Keith | Device for improving breathing |
FI954092A (en) * | 1994-09-08 | 1996-03-09 | Weinmann G Geraete Med | Method of controlling a respirator in the treatment of sleep apnea |
FR2724322A1 (en) * | 1994-09-12 | 1996-03-15 | Pierre Medical Sa | PRESSURE CONTROLLED BREATHING AID |
US6866040B1 (en) * | 1994-09-12 | 2005-03-15 | Nellcor Puritan Bennett France Developpement | Pressure-controlled breathing aid |
ATE235280T1 (en) | 1994-10-14 | 2003-04-15 | Bird Products Corp | PORTABLE, MECHANICAL AND DRIVEN COMPRESSOR VENTILATOR |
US5503146A (en) * | 1994-10-26 | 1996-04-02 | Devilbiss Health Care, Inc. | Standby control for CPAP apparatus |
US5551419A (en) * | 1994-12-15 | 1996-09-03 | Devilbiss Health Care, Inc. | Control for CPAP apparatus |
US5782240A (en) * | 1994-12-22 | 1998-07-21 | Snap Laboratories, L.L.C. | Method of classifying respiratory sounds |
US5540219A (en) * | 1995-01-26 | 1996-07-30 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5537997A (en) * | 1995-01-26 | 1996-07-23 | Respironics, Inc. | Sleep apnea treatment apparatus and passive humidifier for use therewith |
US5947115A (en) * | 1995-01-26 | 1999-09-07 | Respironics, Inc. | Gas flow pressure filter |
US5758637A (en) | 1995-08-31 | 1998-06-02 | Aerogen, Inc. | Liquid dispensing apparatus and methods |
AUPN236595A0 (en) | 1995-04-11 | 1995-05-11 | Rescare Limited | Monitoring of apneic arousals |
WO1996040337A1 (en) * | 1995-06-07 | 1996-12-19 | Nellcor Puritan Bennett Incorporated | Pressure control for constant minute volume |
US5564415A (en) * | 1995-06-07 | 1996-10-15 | Lifecare International, Inc. | Humidifier for a ventilator |
AUPN344195A0 (en) * | 1995-06-08 | 1995-07-06 | Rescare Limited | Monitoring of oro-nasal respiration |
AUPN394895A0 (en) * | 1995-07-03 | 1995-07-27 | Rescare Limited | Auto-calibration of pressure transducer offset |
US6000396A (en) * | 1995-08-17 | 1999-12-14 | University Of Florida | Hybrid microprocessor controlled ventilator unit |
AUPN547895A0 (en) | 1995-09-15 | 1995-10-12 | Rescare Limited | Flow estimation and compenstion of flow-induced pressure swings cpap treatment |
JP3845736B2 (en) | 1995-09-18 | 2006-11-15 | レスメッド・リミテッド | Pressure control in CPAP treatment or assisted ventilation |
DE19538473A1 (en) * | 1995-10-16 | 1997-04-17 | Map Gmbh | Device and method for the quantitative analysis of sleep disorders |
AUPN616795A0 (en) | 1995-10-23 | 1995-11-16 | Rescare Limited | Ipap duration in bilevel cpap or assisted respiration treatment |
AUPN627395A0 (en) * | 1995-10-31 | 1995-11-23 | Compumedics Sleep Pty Ltd | Integrated diagnostic and therapeutic device for gas delivery to patient |
US5921942A (en) * | 1995-11-01 | 1999-07-13 | University Technologies International, Inc. | Adaptively controlled mandibular positioning device and method of using the device |
US5865173A (en) * | 1995-11-06 | 1999-02-02 | Sunrise Medical Hhg Inc. | Bilevel CPAP system with waveform control for both IPAP and EPAP |
WO1997018003A1 (en) * | 1995-11-15 | 1997-05-22 | Regents Of The University Of Minnesota | System for detecting target respiratory flow rates |
US5682878A (en) * | 1995-12-07 | 1997-11-04 | Respironics, Inc. | Start-up ramp system for CPAP system with multiple ramp shape selection |
EP0788805A3 (en) * | 1996-02-06 | 1998-05-13 | DeVilbiss Health Care, Inc. | Control for CPAP apparatus |
US5657752A (en) * | 1996-03-28 | 1997-08-19 | Airways Associates | Nasal positive airway pressure mask and method |
AUPN973596A0 (en) | 1996-05-08 | 1996-05-30 | Resmed Limited | Control of delivery pressure in cpap treatment or assisted respiration |
NO319498B1 (en) * | 1996-07-30 | 2005-08-22 | Weinmann G Geraete Med | Respiratory apparatus for the therapy of sleep apnea ± and methods of controlling it. |
AUPO163896A0 (en) | 1996-08-14 | 1996-09-05 | Resmed Limited | Determination of respiratory airflow |
AUPO247496A0 (en) | 1996-09-23 | 1996-10-17 | Resmed Limited | Assisted ventilation to match patient respiratory need |
AUPO301796A0 (en) | 1996-10-16 | 1996-11-07 | Resmed Limited | A vent valve apparatus |
US5682881A (en) * | 1996-10-21 | 1997-11-04 | Winthrop; Neil | Nasal CPAP/Cannula and securement apparatus |
US6019101A (en) | 1996-10-31 | 2000-02-01 | Sleepnet Corporation | Nasal air mask |
AUPO418696A0 (en) | 1996-12-12 | 1997-01-16 | Resmed Limited | A substance delivery apparatus |
WO1998025664A1 (en) * | 1996-12-12 | 1998-06-18 | The Johns Hopkins University School Of Medicine | Method and apparatus for providing ventilatory support to a patient |
US5896857A (en) * | 1996-12-20 | 1999-04-27 | Resmed Limited | Valve for use in a gas delivery system |
AUPO425696A0 (en) | 1996-12-18 | 1997-01-23 | Resmed Limited | A device for preventing or reducing the passage of air through the mouth |
US9468378B2 (en) * | 1997-01-27 | 2016-10-18 | Lawrence A. Lynn | Airway instability detection system and method |
US8932227B2 (en) * | 2000-07-28 | 2015-01-13 | Lawrence A. Lynn | System and method for CO2 and oximetry integration |
US9042952B2 (en) * | 1997-01-27 | 2015-05-26 | Lawrence A. Lynn | System and method for automatic detection of a plurality of SPO2 time series pattern types |
AUPQ104099A0 (en) | 1999-06-18 | 1999-07-08 | Resmed Limited | Forehead support for facial mask |
WO1998033433A1 (en) * | 1997-01-31 | 1998-08-06 | Respironics Georgia, Inc. | Method and apparatus for treating airway disorders |
US6561191B1 (en) | 1997-02-10 | 2003-05-13 | Resmed Limited | Mask and a vent assembly therefor |
AUPO511397A0 (en) | 1997-02-14 | 1997-04-11 | Resmed Limited | An apparatus for varying the flow area of a conduit |
KR100454157B1 (en) * | 1997-05-07 | 2004-10-26 | 컴퓨메딕스 슬립 피티와이. 리미티드 | Apparatus for controlling gas delivery to patient |
EP1009464A4 (en) | 1997-05-16 | 2006-08-02 | Peter Craig Farrell | Nasal ventilation as a treatment for stroke |
AUPO742297A0 (en) | 1997-06-18 | 1997-07-10 | Resmed Limited | An apparatus for supplying breathable gas |
US20070191697A1 (en) * | 2006-02-10 | 2007-08-16 | Lynn Lawrence A | System and method for SPO2 instability detection and quantification |
US20080287756A1 (en) * | 1997-07-14 | 2008-11-20 | Lynn Lawrence A | Pulse oximetry relational alarm system for early recognition of instability and catastrophic occurrences |
AUPP015097A0 (en) | 1997-11-03 | 1997-11-27 | Resmed Limited | A mounting body |
AUPP026997A0 (en) | 1997-11-07 | 1997-12-04 | Resmed Limited | Administration of cpap treatment pressure in presence of apnea |
AU2004203432B2 (en) * | 1998-03-12 | 2007-03-15 | Respironics, Inc. | Method and apparatus for providing positive airway pressure to a patient |
US6962904B1 (en) * | 1998-03-13 | 2005-11-08 | Connective Tissue Imagineering | Elastin peptide analogs and uses thereof |
USD421298S (en) * | 1998-04-23 | 2000-02-29 | Resmed Limited | Flow generator |
JP4080591B2 (en) * | 1998-04-24 | 2008-04-23 | 株式会社群馬コイケ | Respiratory oxygen supply device |
AUPP370198A0 (en) * | 1998-05-25 | 1998-06-18 | Resmed Limited | Control of the administration of continuous positive airway pressure treatment |
AUPP496198A0 (en) * | 1998-07-31 | 1998-08-20 | Resmed Limited | Switches with graphical display |
US7158610B2 (en) * | 2003-09-05 | 2007-01-02 | Varian Medical Systems Technologies, Inc. | Systems and methods for processing x-ray images |
US6937696B1 (en) * | 1998-10-23 | 2005-08-30 | Varian Medical Systems Technologies, Inc. | Method and system for predictive physiological gating |
AUPP693398A0 (en) * | 1998-11-05 | 1998-12-03 | Resmed Limited | Fault diagnosis in CPAP and NIPPV devices |
US6360741B2 (en) | 1998-11-25 | 2002-03-26 | Respironics, Inc. | Pressure support system with a low leak alarm and method of using same |
FI110065B (en) * | 1998-12-08 | 2002-11-29 | Instrumentarium Oyj | Device in a feedback control system |
AUPP789698A0 (en) | 1998-12-23 | 1999-01-21 | Resmed Limited | An apparatus for supplying breathable gas |
AUPP826999A0 (en) * | 1999-01-21 | 1999-02-11 | Resmed Limited | A mounting arrangement |
US7073501B2 (en) * | 1999-02-04 | 2006-07-11 | Univerity Technologies International Inc. | Ventilatory stabilization technology |
FR2789593B1 (en) * | 1999-05-21 | 2008-08-22 | Mallinckrodt Dev France | APPARATUS FOR SUPPLYING AIR PRESSURE TO A PATIENT WITH SLEEP DISORDERS AND METHODS OF CONTROLLING THE SAME |
FR2789592A1 (en) | 1999-02-12 | 2000-08-18 | Mallinckrodt Dev France | APPARATUS FOR PROVIDING AIR PRESSURE TO A PATIENT WITH SLEEP DISORDERS AND ITS CONTROL METHODS |
FR2789594A1 (en) | 1999-05-21 | 2000-08-18 | Nellcor Puritan Bennett France | APPARATUS FOR PROVIDING AIR PRESSURE TO A PATIENT WITH SLEEP DISORDERS AND ITS CONTROL METHODS |
US6467477B1 (en) | 1999-03-26 | 2002-10-22 | Respironics, Inc. | Breath-based control of a therapeutic treatment |
AUPP949999A0 (en) | 1999-03-29 | 1999-04-22 | Resmed Limited | Forehead support for facial mask II |
US7094206B2 (en) * | 1999-04-23 | 2006-08-22 | The Trustees Of Tufts College | System for measuring respiratory function |
AUPP996499A0 (en) | 1999-04-23 | 1999-05-20 | Australian Centre For Advanced Medical Technology Ltd | A treatment for hypertension caused by pre-eclampsia |
US6401713B1 (en) * | 1999-05-05 | 2002-06-11 | Respironics, Inc. | Apparatus and method of providing continuous positive airway pressure |
US6240919B1 (en) * | 1999-06-07 | 2001-06-05 | Macdonald John J. | Method for providing respiratory airway support pressure |
US7219669B1 (en) | 1999-06-08 | 2007-05-22 | Sleepnet Corporation | Nose mask |
US6631718B1 (en) | 1999-06-08 | 2003-10-14 | Sleepnet Corporation | Air mask with seal |
FR2794635B1 (en) | 1999-06-14 | 2001-08-03 | Taema | APPARATUS FOR DIAGNOSING OR TREATING SLEEP BREATHING DISORDERS AND METHOD OF OPERATION |
WO2000078379A1 (en) * | 1999-06-16 | 2000-12-28 | Resmed Ltd. | Apparatus with automatic respiration monitoring and display |
JP3820811B2 (en) * | 1999-08-02 | 2006-09-13 | 株式会社デンソー | Respiratory system disease monitoring device |
US6739335B1 (en) | 1999-09-08 | 2004-05-25 | New York University School Of Medicine | Method and apparatus for optimizing controlled positive airway pressure using the detection of cardiogenic oscillations |
US6235177B1 (en) | 1999-09-09 | 2001-05-22 | Aerogen, Inc. | Method for the construction of an aperture plate for dispensing liquid droplets |
AUPQ339099A0 (en) | 1999-10-13 | 1999-11-04 | Resmed Limited | A humidifier |
WO2001026721A1 (en) * | 1999-10-14 | 2001-04-19 | The Trustees Of Boston University | Variable peak pressure ventilation method and system |
US7204250B1 (en) * | 1999-12-16 | 2007-04-17 | Compumedics Limited | Bio-mask |
US6247926B1 (en) | 2000-01-17 | 2001-06-19 | W. Keith Thornton | Oral appliance having a bonding layer and methods for fitting and relining same |
SE0000205D0 (en) * | 2000-01-25 | 2000-01-25 | Siemens Elema Ab | ventilator |
DE10014427A1 (en) | 2000-03-24 | 2001-10-04 | Weinmann G Geraete Med | Method for controlling a ventilator and device for monitoring |
US6405729B1 (en) | 2000-04-05 | 2002-06-18 | W. Keith Thornton | Oral appliance for improving breathing and method of constructing same |
US6464924B1 (en) | 2000-04-05 | 2002-10-15 | W. Keith Thornton | Method of forming a custom mask using an impression mask |
US6571798B1 (en) | 2000-04-05 | 2003-06-03 | W. Keith Thornton | Device for improving breathing and method of constructing same |
US7971588B2 (en) | 2000-05-05 | 2011-07-05 | Novartis Ag | Methods and systems for operating an aerosol generator |
US8336545B2 (en) | 2000-05-05 | 2012-12-25 | Novartis Pharma Ag | Methods and systems for operating an aerosol generator |
US6581594B1 (en) | 2000-05-15 | 2003-06-24 | Resmed Limited | Respiratory mask having gas washout vent and gas washout vent for respiratory mask |
WO2001096984A2 (en) * | 2000-06-14 | 2001-12-20 | Sleep Solutions, Inc. | Secure test and test result delivery system |
DE10031079A1 (en) * | 2000-06-30 | 2002-02-07 | Map Gmbh | Measuring patient breathing and state, correlates present respiration signals with prior reference measurements, to adjust CPAP therapy pressure accordingly |
DE10035946C2 (en) * | 2000-07-21 | 2002-06-27 | Map Gmbh | Bracket for a breathing mask |
US6935335B1 (en) | 2000-08-17 | 2005-08-30 | Ilife Systems, Inc. | System and method for treating obstructive sleep apnea |
US6814073B2 (en) | 2000-08-29 | 2004-11-09 | Resmed Limited | Respiratory apparatus with improved flow-flattening detection |
US6622726B1 (en) * | 2000-10-17 | 2003-09-23 | Newport Medical Instruments, Inc. | Breathing apparatus and method |
DE20017940U1 (en) | 2000-10-19 | 2000-12-28 | Map Gmbh | Breathing mask for supplying a breathing gas to a mask user and a derivation device for deriving breathing gas |
US6454724B1 (en) | 2000-10-25 | 2002-09-24 | Safe Flight Instrument Corporation | Sleep apnea detection system and method |
AUPR193300A0 (en) * | 2000-12-07 | 2001-01-04 | Resmed Limited | Mask assembly |
EP2308536B1 (en) | 2000-12-12 | 2012-03-28 | ResMed Limited | Headgear |
JP4336496B2 (en) | 2000-12-29 | 2009-09-30 | レスメド・リミテッド | Characterizing the mask system |
US9053222B2 (en) * | 2002-05-17 | 2015-06-09 | Lawrence A. Lynn | Patient safety processor |
US6666209B2 (en) * | 2001-02-20 | 2003-12-23 | 3M Innovative Properties Company | Method and system of calibrating air flow in a respirator system |
FR2826282B1 (en) | 2001-06-22 | 2004-05-28 | Taema | RESPIRATORY APPARATUS WITH STABILIZED PRESSURE TURBINE, TURBINE AND METHOD THEREOF |
CN1313172C (en) * | 2001-07-19 | 2007-05-02 | 雷斯姆德公司 | Method and equipment for pressure support ventilation of patients |
US7753050B2 (en) * | 2001-09-07 | 2010-07-13 | Resmed Limited | Headgear connection assembly for a respiratory mask assembly |
DE60225895T2 (en) | 2001-09-07 | 2009-04-09 | ResMed Ltd., Bella Vista | mask assembly |
FR2829917B1 (en) * | 2001-09-24 | 2004-06-11 | Ela Medical Sa | ACTIVE MEDICAL DEVICE INCLUDING MEANS FOR DIAGNOSING THE RESPIRATORY PROFILE |
US7246619B2 (en) * | 2001-10-10 | 2007-07-24 | Ric Investments, Llc | Snore detecting method and apparatus |
US7938114B2 (en) * | 2001-10-12 | 2011-05-10 | Ric Investments Llc | Auto-titration bi-level pressure support system and method of using same |
US7168429B2 (en) * | 2001-10-12 | 2007-01-30 | Ric Investments, Llc | Auto-titration pressure support system and method of using same |
DE10201682A1 (en) | 2002-01-17 | 2003-07-31 | Map Medizin Technologie Gmbh | The breathing mask arrangement |
ATE473774T1 (en) | 2001-10-22 | 2010-07-15 | Map Medizin Technologie Gmbh | MEDICAL MASK |
DE10151984C5 (en) | 2001-10-22 | 2008-07-17 | Map Medizin-Technologie Gmbh | Application device for a breathing mask arrangement |
WO2003041780A2 (en) * | 2001-11-16 | 2003-05-22 | Fisher & Paykel Healthcare Limited | A nasal positive pressure device |
EP1938856B1 (en) | 2001-11-22 | 2019-07-17 | ResMed Pty Ltd | Respiratory mask and gas washout vent |
CA2472644C (en) | 2002-01-07 | 2013-11-05 | Aerogen, Inc. | Devices and methods for nebulizing fluids for inhalation |
US7677467B2 (en) | 2002-01-07 | 2010-03-16 | Novartis Pharma Ag | Methods and devices for aerosolizing medicament |
ES2603067T3 (en) | 2002-01-15 | 2017-02-23 | Novartis Ag | Methods and systems for operating an aerosol generator |
US20030199945A1 (en) * | 2002-02-11 | 2003-10-23 | James Ciulla | Device and method for treating disordered breathing |
US7500481B2 (en) * | 2002-03-08 | 2009-03-10 | Kaerys S.A. | Apparatus to assist a patient's breathing with a variable ramp period to rise to treatment pressure |
US7448383B2 (en) * | 2002-03-08 | 2008-11-11 | Kaerys, S.A. | Air assistance apparatus providing fast rise and fall of pressure within one patient's breath |
US7438073B2 (en) * | 2002-03-08 | 2008-10-21 | Kaerys S.A. | Air assistance apparatus for computing the airflow provided by only means of pressure sensors |
CA2469318C (en) | 2002-03-22 | 2010-06-01 | Invacare Corporation | Nasal mask |
US7743767B2 (en) | 2002-04-23 | 2010-06-29 | Resmed Limited | Ergonomic and adjustable respiratory mask assembly with frame |
US8997742B2 (en) * | 2002-04-23 | 2015-04-07 | Resmed Limited | Ergonomic and adjustable respiratory mask assembly with cushion |
AUPS192602A0 (en) * | 2002-04-23 | 2002-05-30 | Resmed Limited | Nasal mask |
US8042542B2 (en) * | 2002-04-23 | 2011-10-25 | Resmed Limited | Respiratory mask assembly with magnetic coupling to headgear assembly |
EP1501458B1 (en) | 2002-05-01 | 2007-08-08 | Keith W. Thornton | Device for improving a user's breathing |
EP1509259B1 (en) | 2002-05-20 | 2016-04-20 | Novartis AG | Apparatus for providing aerosol for medical treatment and methods |
US7841987B2 (en) * | 2004-03-30 | 2010-11-30 | Apneos Corporation | System and method for visualizing sleep-related information |
USD485905S1 (en) | 2002-08-09 | 2004-01-27 | Resmed Limited | Nasal mask |
EP1545673B1 (en) | 2002-09-06 | 2013-12-18 | ResMed Limited | Forehead pad for respiratory mask |
EP2913079B1 (en) | 2002-09-06 | 2017-10-25 | ResMed Limited | Cushion for respiratory mask assembly |
NZ573226A (en) * | 2002-09-06 | 2010-07-30 | Resmed Ltd | Elbow for respiratory mask assembly |
US7107992B2 (en) * | 2002-10-04 | 2006-09-19 | Pavad Medical, Inc. | System and method for preventing closure of passageways |
US7620444B2 (en) | 2002-10-05 | 2009-11-17 | General Electric Company | Systems and methods for improving usability of images for medical applications |
US6857428B2 (en) | 2002-10-24 | 2005-02-22 | W. Keith Thornton | Custom fitted mask and method of forming same |
NZ553302A (en) | 2002-11-06 | 2008-10-31 | Resmed Ltd | Mask assembly with frame that can be flexed about longitudinal axis |
US7661426B2 (en) * | 2002-11-19 | 2010-02-16 | Michael Lauk | Method for controlling the pressure supplied by a CPAP device, CPAP device and storage medium |
US7189204B2 (en) | 2002-12-04 | 2007-03-13 | Cardiac Pacemakers, Inc. | Sleep detection using an adjustable threshold |
EP1575650B1 (en) | 2002-12-06 | 2016-05-25 | Fisher & Paykel Healthcare Limited | Mouthpiece |
US8672852B2 (en) * | 2002-12-13 | 2014-03-18 | Intercure Ltd. | Apparatus and method for beneficial modification of biorhythmic activity |
CA2512843A1 (en) * | 2003-01-09 | 2004-07-29 | The Research Foundation Of State University Of New York | Method of treating functional somatic syndromes and diagnosing sleep disorders based on functional somatic syndrome symptoms |
US7025730B2 (en) * | 2003-01-10 | 2006-04-11 | Medtronic, Inc. | System and method for automatically monitoring and delivering therapy for sleep-related disordered breathing |
EP1603619B1 (en) | 2003-02-21 | 2019-04-10 | ResMed Limited | Nasal assembly |
US7835529B2 (en) * | 2003-03-19 | 2010-11-16 | Irobot Corporation | Sound canceling systems and methods |
US7520277B1 (en) * | 2003-04-01 | 2009-04-21 | Daniel Grady | CPAP enclosure for the treatment of sleep apnea |
US7503327B2 (en) | 2003-04-10 | 2009-03-17 | Resmed Limited | Mask with integral cushion and forehead piece |
US7499750B2 (en) | 2003-04-11 | 2009-03-03 | Cardiac Pacemakers, Inc. | Noise canceling cardiac electrodes |
ES2459216T3 (en) | 2003-05-02 | 2014-05-08 | Resmed Limited | Mask system |
ATE538832T1 (en) | 2003-05-05 | 2012-01-15 | Resmed Ltd | HEADPROOF FOR A FACE MASK |
US20040244807A1 (en) * | 2003-06-04 | 2004-12-09 | Jianguo Sun | Sleep-lab systems and methods |
US7588033B2 (en) | 2003-06-18 | 2009-09-15 | Breathe Technologies, Inc. | Methods, systems and devices for improving ventilation in a lung area |
US8020555B2 (en) * | 2003-06-18 | 2011-09-20 | New York University | System and method for improved treatment of sleeping disorders using therapeutic positive airway pressure |
DE10337138A1 (en) * | 2003-08-11 | 2005-03-17 | Freitag, Lutz, Dr. | Method and arrangement for the respiratory assistance of a patient as well as tracheal prosthesis and catheter |
AU2003903138A0 (en) * | 2003-06-20 | 2003-07-03 | Resmed Limited | Method and apparatus for improving the comfort of cpap |
AU2004249258B2 (en) * | 2003-06-20 | 2011-04-07 | Resmed Limited | Apparatus for improving the comfort of CPAP |
US7621270B2 (en) * | 2003-06-23 | 2009-11-24 | Invacare Corp. | System and method for providing a breathing gas |
US8616195B2 (en) | 2003-07-18 | 2013-12-31 | Novartis Ag | Nebuliser for the production of aerosolized medication |
WO2005007056A2 (en) * | 2003-07-22 | 2005-01-27 | Zinder, Oren | A respiratory aid system and method |
US7118536B2 (en) * | 2003-07-25 | 2006-10-10 | Ric Investments, Llc. | Apnea/hypopnea detection system and method |
US7033673B2 (en) * | 2003-07-25 | 2006-04-25 | Analytical Services & Materials, Inc. | Erosion-resistant silicone coatings for protection of fluid-handling parts |
ES2592262T3 (en) * | 2003-08-04 | 2016-11-29 | Carefusion 203, Inc. | Portable respirator system |
US7607437B2 (en) * | 2003-08-04 | 2009-10-27 | Cardinal Health 203, Inc. | Compressor control system and method for a portable ventilator |
US8118024B2 (en) | 2003-08-04 | 2012-02-21 | Carefusion 203, Inc. | Mechanical ventilation system utilizing bias valve |
JP2007501072A (en) * | 2003-08-04 | 2007-01-25 | パルモネティック システムズ インコーポレイテッド | Compressor control system for portable ventilators |
US7527053B2 (en) * | 2003-08-04 | 2009-05-05 | Cardinal Health 203, Inc. | Method and apparatus for attenuating compressor noise |
US8156937B2 (en) * | 2003-08-04 | 2012-04-17 | Carefusion 203, Inc. | Portable ventilator system |
US6988994B2 (en) * | 2003-08-14 | 2006-01-24 | New York University | Positive airway pressure system and method for treatment of sleeping disorder in patient |
WO2007040988A2 (en) * | 2003-08-14 | 2007-04-12 | New York University | System and method for diagnosis and treatment of a breathing pattern of a patient |
US7896812B2 (en) * | 2003-08-14 | 2011-03-01 | New York University | System and method for diagnosis and treatment of a breathing pattern of a patient |
US7575553B2 (en) * | 2003-09-18 | 2009-08-18 | Cardiac Pacemakers, Inc. | Methods and systems for assessing pulmonary disease |
US8192376B2 (en) | 2003-08-18 | 2012-06-05 | Cardiac Pacemakers, Inc. | Sleep state classification |
US7664546B2 (en) * | 2003-09-18 | 2010-02-16 | Cardiac Pacemakers, Inc. | Posture detection system and method |
US7967756B2 (en) * | 2003-09-18 | 2011-06-28 | Cardiac Pacemakers, Inc. | Respiratory therapy control based on cardiac cycle |
AU2004266693B2 (en) | 2003-08-18 | 2011-03-10 | Breathe Technologies, Inc | Method and device for non-invasive ventilation with nasal interface |
US8606356B2 (en) | 2003-09-18 | 2013-12-10 | Cardiac Pacemakers, Inc. | Autonomic arousal detection system and method |
EP1670547B1 (en) | 2003-08-18 | 2008-11-12 | Cardiac Pacemakers, Inc. | Patient monitoring system |
US8002553B2 (en) | 2003-08-18 | 2011-08-23 | Cardiac Pacemakers, Inc. | Sleep quality data collection and evaluation |
US7591265B2 (en) | 2003-09-18 | 2009-09-22 | Cardiac Pacemakers, Inc. | Coordinated use of respiratory and cardiac therapies for sleep disordered breathing |
US7610094B2 (en) * | 2003-09-18 | 2009-10-27 | Cardiac Pacemakers, Inc. | Synergistic use of medical devices for detecting medical disorders |
US7668591B2 (en) * | 2003-09-18 | 2010-02-23 | Cardiac Pacemakers, Inc. | Automatic activation of medical processes |
US7662101B2 (en) * | 2003-09-18 | 2010-02-16 | Cardiac Pacemakers, Inc. | Therapy control based on cardiopulmonary status |
US7887493B2 (en) | 2003-09-18 | 2011-02-15 | Cardiac Pacemakers, Inc. | Implantable device employing movement sensing for detecting sleep-related disorders |
US8251061B2 (en) * | 2003-09-18 | 2012-08-28 | Cardiac Pacemakers, Inc. | Methods and systems for control of gas therapy |
US7510531B2 (en) | 2003-09-18 | 2009-03-31 | Cardiac Pacemakers, Inc. | System and method for discrimination of central and obstructive disordered breathing events |
US7396333B2 (en) | 2003-08-18 | 2008-07-08 | Cardiac Pacemakers, Inc. | Prediction of disordered breathing |
US7720541B2 (en) | 2003-08-18 | 2010-05-18 | Cardiac Pacemakers, Inc. | Adaptive therapy for disordered breathing |
US7757690B2 (en) | 2003-09-18 | 2010-07-20 | Cardiac Pacemakers, Inc. | System and method for moderating a therapy delivered during sleep using physiologic data acquired during non-sleep |
US20050053267A1 (en) * | 2003-09-05 | 2005-03-10 | Varian Medical Systems Technologies, Inc. | Systems and methods for tracking moving targets and monitoring object positions |
US8571639B2 (en) | 2003-09-05 | 2013-10-29 | Varian Medical Systems, Inc. | Systems and methods for gating medical procedures |
WO2005030048A1 (en) * | 2003-09-23 | 2005-04-07 | The Research Foundation Of State University Of New York | Method for predicting apnea-hypopnea index from overnight pulse oximetry readings |
CA2544301A1 (en) * | 2003-11-05 | 2005-05-26 | Pavad Medical, Inc. | Altering the stiffness, size, and/or shape of tissues for breathing disorders and other conditions |
EP1701756B1 (en) | 2003-11-26 | 2018-10-03 | ResMed Limited | Macro-control of treatment for sleep disordered breathing |
JP4773368B2 (en) | 2003-12-29 | 2011-09-14 | レスメド・リミテッド | Mechanical ventilation in the presence of sleep-disordered breathing |
EP2510968B1 (en) | 2003-12-31 | 2017-02-08 | ResMed Limited | Compact oronasal patient interface |
NZ548484A (en) | 2004-01-16 | 2011-01-28 | Resmed Ltd | Headgear connection assembly using a clip with at least one resiliantly flexible spring arm |
US8011366B2 (en) * | 2004-02-04 | 2011-09-06 | Devilbiss Healthcare Llc | Method for acclimating a CPAP therapy patient to prescribed pressure |
WO2005079726A1 (en) | 2004-02-23 | 2005-09-01 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
JP4699443B2 (en) * | 2004-02-25 | 2011-06-08 | レスメド・リミテッド | Heart monitoring and treatment using a device for performing pressurized therapy for sleep disordered breathing |
US8146592B2 (en) * | 2004-02-26 | 2012-04-03 | Ameriflo, Inc. | Method and apparatus for regulating fluid flow or conserving fluid flow |
US7617826B1 (en) | 2004-02-26 | 2009-11-17 | Ameriflo, Inc. | Conserver |
JP3913748B2 (en) * | 2004-03-25 | 2007-05-09 | 三洋電機株式会社 | Snoring detection method and detection apparatus |
EP1737524B1 (en) | 2004-04-02 | 2018-10-10 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
US9072852B2 (en) | 2004-04-02 | 2015-07-07 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
US7267121B2 (en) * | 2004-04-20 | 2007-09-11 | Aerogen, Inc. | Aerosol delivery apparatus and method for pressure-assisted breathing systems |
US7946291B2 (en) * | 2004-04-20 | 2011-05-24 | Novartis Ag | Ventilation systems and methods employing aerosol generators |
US7276031B2 (en) * | 2004-05-12 | 2007-10-02 | New York University | System and method for classifying patient's breathing using artificial neural network |
US20060258930A1 (en) * | 2004-05-18 | 2006-11-16 | Jianping Wu | Device for use in sleep stage determination using frontal electrodes |
US7575005B2 (en) * | 2004-05-18 | 2009-08-18 | Excel-Tech Ltd. | Mask assembly with integrated sensors |
US8244340B2 (en) * | 2006-12-22 | 2012-08-14 | Natus Medical Incorporated | Method, system and device for sleep stage determination using frontal electrodes |
US20070208269A1 (en) * | 2004-05-18 | 2007-09-06 | Mumford John R | Mask assembly, system and method for determining the occurrence of respiratory events using frontal electrode array |
JP4787243B2 (en) | 2004-06-03 | 2011-10-05 | レスメド・リミテッド | Cushion for patient intermediate attachment |
US20050268912A1 (en) * | 2004-06-04 | 2005-12-08 | Norman Robert G | System and method for automated titration of continuous positive airway pressure |
NZ587820A (en) | 2004-06-16 | 2012-03-30 | Resmed Ltd | Cushion with a gusset for a respiratory mask assembly |
EP1804649A4 (en) * | 2004-07-23 | 2009-01-28 | Intercure Ltd | Apparatus and method for breathing pattern determination using a non-contact microphone |
US7934501B2 (en) * | 2004-07-23 | 2011-05-03 | Resmed Limited | Swivel elbow for a patient interface |
US7882834B2 (en) * | 2004-08-06 | 2011-02-08 | Fisher & Paykel Healthcare Limited | Autotitrating method and apparatus |
US20060042627A1 (en) * | 2004-08-31 | 2006-03-02 | Macmillan Nicholas J | PAP titrate control method and apparatus |
US7469698B1 (en) * | 2004-09-14 | 2008-12-30 | Winthrop De Childers | Parameter optimization in sleep apnea treatment apparatus |
US8578937B2 (en) | 2004-09-21 | 2013-11-12 | Medtronic Xomed, Inc. | Smart mandibular repositioning system |
US7836888B2 (en) * | 2004-09-21 | 2010-11-23 | Pavad Medical, Incorporated | Airway implant and methods of making and using |
US7882842B2 (en) | 2004-09-21 | 2011-02-08 | Pavad Medical, Inc. | Airway implant sensors and methods of making and using the same |
EP2510966B1 (en) | 2004-09-28 | 2014-01-15 | ResMed Ltd. | Apparatus for resolving upper airway instability |
NZ578881A (en) * | 2004-11-04 | 2011-04-29 | Resmed Ltd | Estimating the airflow through a PAP device from a motor's speed and adjusting the motor's control current accordingly |
US7996072B2 (en) | 2004-12-21 | 2011-08-09 | Cardiac Pacemakers, Inc. | Positionally adaptable implantable cardiac device |
JP4987726B2 (en) * | 2004-12-30 | 2012-07-25 | レスメド・リミテッド | Respirator with a gas washout vent and a gas washout vent assembly for a respirator |
DE202006021258U1 (en) | 2005-01-12 | 2014-05-05 | Resmed Limited | Upholstery for patient interface |
DE102005003553A1 (en) * | 2005-01-26 | 2006-08-03 | Weinmann Geräte für Medizin GmbH + Co. KG | Controlling pressure in a pneumatic supply unit such as in breathing apparatus where the pressure is measured at a narrowed portion of the conduit |
US7680534B2 (en) | 2005-02-28 | 2010-03-16 | Cardiac Pacemakers, Inc. | Implantable cardiac device with dyspnea measurement |
US7680538B2 (en) * | 2005-03-31 | 2010-03-16 | Case Western Reserve University | Method of treating obstructive sleep apnea using electrical nerve stimulation |
US20090048500A1 (en) * | 2005-04-20 | 2009-02-19 | Respimetrix, Inc. | Method for using a non-invasive cardiac and respiratory monitoring system |
JP5064383B2 (en) | 2005-05-25 | 2012-10-31 | エアロジェン,インコーポレイテッド | Vibration system and method |
EP1893267B1 (en) * | 2005-06-14 | 2016-09-28 | ResMed Limited | Apparatus for controlling mask leak in cpap treatment |
US8528551B2 (en) | 2005-06-14 | 2013-09-10 | Resmed Limited | Acclimatization therapy for first time users |
US9227032B2 (en) | 2005-06-14 | 2016-01-05 | Resmed Limited | Method and apparatus for improving CPAP patient compliance |
US7827987B2 (en) * | 2005-06-17 | 2010-11-09 | Nellcor Puritan Bennett Llc | Ball joint for providing flexibility to a gas delivery pathway |
US7451762B2 (en) * | 2005-06-17 | 2008-11-18 | Salter Labs | Pressure sensing device with test circuit |
US7455063B2 (en) * | 2005-06-17 | 2008-11-25 | Nellcor Puritan Bennett Llc | Adjustable gas delivery mask having a flexible gasket |
US7900630B2 (en) * | 2005-06-17 | 2011-03-08 | Nellcor Puritan Bennett Llc | Gas delivery mask with flexible bellows |
US7849855B2 (en) * | 2005-06-17 | 2010-12-14 | Nellcor Puritan Bennett Llc | Gas exhaust system for a gas delivery mask |
US7909035B2 (en) * | 2005-07-11 | 2011-03-22 | Airway Technologies, Llc | Multi-chamber mask and method of forming the same |
US7958892B2 (en) | 2005-07-29 | 2011-06-14 | Resmed Limited | Air delivery system |
US20070045152A1 (en) * | 2005-08-01 | 2007-03-01 | Resmed Limited | Storage system for an apparatus that delivers breathable gas to a patient |
US20070055115A1 (en) * | 2005-09-08 | 2007-03-08 | Jonathan Kwok | Characterization of sleep disorders using composite patient data |
CN101454041B (en) | 2005-09-20 | 2012-12-12 | 呼吸科技公司 | Systems, methods and apparatus for respiratory support of a patient |
CA2623661A1 (en) * | 2005-09-30 | 2007-04-12 | New York University | System and method for diagnosis and treatment of a breathing pattern of a patient |
NZ591992A (en) | 2005-10-14 | 2012-11-30 | Resmed Ltd | Breathing mask with cushion attached to frame via lip of cushion engaging within recess between frame outer and inner walls, and guided in via angled protrusion of frame inner wall |
US20090126739A1 (en) | 2005-10-25 | 2009-05-21 | Resmed Limited | Interchangeable Mask Assembly |
US20070118180A1 (en) | 2005-11-18 | 2007-05-24 | Quan Ni | Cardiac resynchronization therapy for improved hemodynamics based on disordered breathing detection |
US8025052B2 (en) * | 2005-11-21 | 2011-09-27 | Ric Investments, Llc | System and method of monitoring respiratory events |
WO2007062400A2 (en) | 2005-11-23 | 2007-05-31 | Jianguo Sun | Method and apparatus for providing positive airway pressure to a patient |
US20070129644A1 (en) * | 2005-12-02 | 2007-06-07 | Glenn Richards | Sleep disorder screening program |
EP2630914B1 (en) * | 2006-01-06 | 2017-09-13 | ResMed Limited | Computer controlled CPAP system with snore detection |
US7706852B2 (en) * | 2006-01-30 | 2010-04-27 | Nellcor Puritan Bennett Llc | System and method for detection of unstable oxygen saturation |
US7668579B2 (en) | 2006-02-10 | 2010-02-23 | Lynn Lawrence A | System and method for the detection of physiologic response to stimulation |
WO2007098200A2 (en) * | 2006-02-16 | 2007-08-30 | Imthera Medical, Inc. | An rfid-based apparatus, system, and method for therapeutic treatment of obstructive sleep apnea |
US8640698B2 (en) * | 2006-02-17 | 2014-02-04 | Redmed Limited | Method and apparatus for monitoring the condition of a patient with diabetes |
US8640697B2 (en) | 2006-02-17 | 2014-02-04 | Resmed Limited | Combination enhanced therapy |
EP1991297B1 (en) | 2006-03-06 | 2019-12-04 | ResMed Pty Ltd | Determination of apnea/hypopnea during cpap treatment |
NZ607280A (en) * | 2006-03-06 | 2014-06-27 | Resmed Ltd | Method and apparatus for improved flow limitation detection of obstructive sleep apnea |
DE102007011924A1 (en) * | 2006-03-08 | 2007-12-27 | Weinmann Geräte für Medizin GmbH & Co. KG | Method and device for controlling a ventilator |
US8316858B2 (en) | 2006-04-06 | 2012-11-27 | Airway Technologies, Llc | System for coupling an oral appliance to a medical mask |
US20080035146A1 (en) * | 2006-05-05 | 2008-02-14 | Jerry Crabb | Methods, systems and computer products for filling lungs |
US8196580B2 (en) * | 2006-05-11 | 2012-06-12 | Yossi Gross | Implantable respiration therapy device |
CN101541365A (en) | 2006-05-18 | 2009-09-23 | 呼吸科技公司 | Tracheostoma tracheotomy method and device |
WO2007140512A1 (en) * | 2006-06-05 | 2007-12-13 | Resmed Ltd | Systems and/or methods for calibration-less devices or less expensive calibration devices for treating sleep-disordered breathing |
US7734350B2 (en) * | 2006-06-14 | 2010-06-08 | Zmed Technologies, Inc. | Respiration apparatus |
WO2007147046A2 (en) * | 2006-06-14 | 2007-12-21 | Zmed Technologies, Inc. | Respiration stimulation |
US7762006B2 (en) * | 2006-06-14 | 2010-07-27 | Siestamed, Technologies | Medical equipment drying device |
US9010327B2 (en) * | 2006-06-30 | 2015-04-21 | Breas Medical Ab | Energy relief control in a mechanical ventilator |
US8874251B2 (en) | 2006-07-06 | 2014-10-28 | Airway Technologies, Llc | System and method for forming a custom medical mask from a three-dimensional electronic model |
US8236216B2 (en) | 2006-07-06 | 2012-08-07 | Airway Technologies, Llc | System and method for forming a custom medical mask using an orientation device |
US7594508B2 (en) * | 2006-07-13 | 2009-09-29 | Ric Investments, Llc. | Ventilation system employing synchronized delivery of positive and negative pressure ventilation |
CN102631741B (en) * | 2006-07-14 | 2015-11-04 | 菲舍尔和佩克尔保健有限公司 | Respiratory assist system |
CN101516427B (en) | 2006-07-28 | 2012-08-08 | 雷斯梅德有限公司 | Delivery of respiratory therapy |
US9937312B2 (en) | 2006-07-28 | 2018-04-10 | Resmed Limited | Delivery of respiratory therapy with foam interface |
JP2009545384A (en) | 2006-08-03 | 2009-12-24 | ブリーズ テクノロジーズ, インコーポレイテッド | Method and apparatus for minimally invasive respiratory assistance |
WO2008024918A2 (en) * | 2006-08-23 | 2008-02-28 | Jakel Incorporated | Producing a constant air flow from a blower |
US9028423B2 (en) | 2006-08-30 | 2015-05-12 | Resmed Limited | Distinguishing closed and open respiratory airway apneas by complex admittance values |
US20080053450A1 (en) * | 2006-08-31 | 2008-03-06 | Nellcor Puritan Bennett Incorporated | Patient interface assembly for a breathing assistance system |
US20090320842A1 (en) * | 2006-09-07 | 2009-12-31 | Renee Frances Doherty | Mask and flow generator system |
EP2061537A4 (en) | 2006-09-08 | 2017-04-05 | ResMed Limited | Method and apparatus for treating apnea/hypopnea |
US20100113957A1 (en) * | 2006-09-11 | 2010-05-06 | Anthony Williams | System, method and apparatus for monitoring a medical condition |
US7992558B2 (en) * | 2006-09-11 | 2011-08-09 | Airway Technologies Llc | Stability medical mask |
US20080060647A1 (en) * | 2006-09-12 | 2008-03-13 | Invacare Corporation | System and method for delivering a breathing gas |
CA2602005A1 (en) * | 2006-09-18 | 2008-03-18 | Invacare Corporation | Breathing mask |
WO2008048950A2 (en) * | 2006-10-17 | 2008-04-24 | Resmed Limited | Device for ramped control of cpap treatment |
US20080109047A1 (en) * | 2006-10-26 | 2008-05-08 | Pless Benjamin D | Apnea treatment device |
WO2008058328A1 (en) | 2006-11-13 | 2008-05-22 | Resmed Ltd | Systems, methods, and/or apparatuses for non-invasive monitoring of respiratory parameters in sleep disordered breathing |
US8020276B2 (en) | 2006-11-30 | 2011-09-20 | Airway Technologies, Llc | System and method for custom-orienting a medical mask to an oral appliance |
US20080139105A1 (en) * | 2006-12-06 | 2008-06-12 | Mcquay International | Duct static pressure control |
JP5911189B2 (en) | 2006-12-15 | 2016-04-27 | レスメド・リミテッドResMed Limited | Respiratory therapy |
US8517023B2 (en) | 2007-01-30 | 2013-08-27 | Resmed Limited | Mask system with interchangeable headgear connectors |
JP4607913B2 (en) * | 2007-02-08 | 2011-01-05 | レスメド・リミテッド | Respirator having a gas exhaust vent and gas exhaust vent assembly for a respiratory mask |
US20080216831A1 (en) * | 2007-03-08 | 2008-09-11 | Mcginnis William J | Standalone cpap device and method of using |
EP1978460B1 (en) * | 2007-04-05 | 2014-01-22 | ResMed R&D Germany GmbH | Monitoring device and method |
US8276585B2 (en) * | 2007-04-10 | 2012-10-02 | Resmed Limited | Systems and methods for visualizing pressures and pressure responses to sleep-related triggering events |
NZ578334A (en) | 2007-04-19 | 2011-01-28 | Resmed Ltd | Mask frame connected to face cushion via intervening clip |
NZ701856A (en) | 2007-05-11 | 2016-06-24 | Resmed Ltd | Automated control for detection of flow limitation |
WO2008144589A1 (en) | 2007-05-18 | 2008-11-27 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and providing ventilation therapy |
US8794235B2 (en) * | 2007-06-08 | 2014-08-05 | Ric Investments, Llc | System and method for treating ventilatory instability |
US9707367B2 (en) | 2007-06-21 | 2017-07-18 | Resmed Limited | Auto-adjusting mask stabilizer |
EP2017586A1 (en) * | 2007-07-20 | 2009-01-21 | Map-Medizintechnologie GmbH | Monitor for CPAP/Ventilator apparatus |
WO2009012599A1 (en) * | 2007-07-26 | 2009-01-29 | Uti Limited Partnership | Transient intervention for modifying the breathing of a patient |
NZ570059A (en) | 2007-07-30 | 2010-08-27 | Resmed Ltd | Nostril prong elastic support for gas breathing mask |
US20090078255A1 (en) * | 2007-09-21 | 2009-03-26 | Bowman Bruce R | Methods for pressure regulation in positive pressure respiratory therapy |
CN101888868B (en) | 2007-09-26 | 2014-01-22 | 呼吸科技公司 | Methods and devices for treating sleep apnea |
CN101873875B (en) | 2007-09-26 | 2014-11-12 | 呼吸科技公司 | Methods and devices for providing inspiratory and expiratory flow relief during ventilation therapy |
WO2009048580A1 (en) * | 2007-10-09 | 2009-04-16 | Imthera Medical, Inc. | Apparatus, system, and method for selective stimulation |
CN101888870B (en) * | 2007-10-26 | 2013-11-27 | 优特埃合伙有限公司 | Ventilation stabilization system |
AU2008321617B2 (en) * | 2007-11-16 | 2014-07-17 | Fisher & Paykel Healthcare Limited | Nasal pillows with high volume bypass flow and method of using same |
US7997885B2 (en) * | 2007-12-03 | 2011-08-16 | Carefusion 303, Inc. | Roots-type blower reduced acoustic signature method and apparatus |
US20090165795A1 (en) * | 2007-12-31 | 2009-07-02 | Nellcor Puritan Bennett Llc | Method and apparatus for respiratory therapy |
WO2009105432A2 (en) | 2008-02-19 | 2009-08-27 | Portaero, Inc. | Devices and methods for delivery of a therapeutic agent through a pneumostoma |
US8275553B2 (en) | 2008-02-19 | 2012-09-25 | Nellcor Puritan Bennett Llc | System and method for evaluating physiological parameter data |
US8475389B2 (en) | 2008-02-19 | 2013-07-02 | Portaero, Inc. | Methods and devices for assessment of pneumostoma function |
US11331447B2 (en) | 2008-03-04 | 2022-05-17 | ResMed Pty Ltd | Mask system with snap-fit shroud |
NZ608162A (en) | 2008-03-04 | 2014-11-28 | Resmed Ltd | An interface including a foam cushioning element |
DE202009018972U1 (en) | 2008-03-04 | 2014-12-09 | Resmed Limited | mask system |
WO2009108994A1 (en) | 2008-03-04 | 2009-09-11 | Resmed Ltd | A foam respiratory mask |
US8365730B2 (en) | 2008-03-24 | 2013-02-05 | Covidien Lp | Method and system for classification of photo-plethysmographically detected respiratory effort |
US20090247837A1 (en) * | 2008-03-27 | 2009-10-01 | Nellcor Puritan Bennett Llc | System And Method For Diagnosing Sleep Apnea |
US8888711B2 (en) | 2008-04-08 | 2014-11-18 | Carefusion 203, Inc. | Flow sensor |
US8770193B2 (en) | 2008-04-18 | 2014-07-08 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and controlling ventilator functions |
US8776793B2 (en) | 2008-04-18 | 2014-07-15 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and controlling ventilator functions |
US8251876B2 (en) | 2008-04-22 | 2012-08-28 | Hill-Rom Services, Inc. | Breathing exercise apparatus |
EP2113274B1 (en) | 2008-04-30 | 2016-04-27 | ResMed R&D Germany GmbH | Apparatus for controlled delivery of a breathing gas to the respiratory tracts of a user |
US10258757B2 (en) | 2008-05-12 | 2019-04-16 | Fisher & Paykel Healthcare Limited | Patient interface and aspects thereof |
US10792451B2 (en) | 2008-05-12 | 2020-10-06 | Fisher & Paykel Healthcare Limited | Patient interface and aspects thereof |
NZ589634A (en) | 2008-06-04 | 2012-09-28 | Resmed Ltd | A mask to apply positive airway pressure (PAP) for the treatment of a sleep disorder that attaches to the face |
US8905031B2 (en) | 2008-06-04 | 2014-12-09 | Resmed Limited | Patient interface systems |
NZ742900A (en) | 2008-06-05 | 2020-02-28 | ResMed Pty Ltd | Treatment of respiratory conditions by automatic control of flow and/or temperature and/or humidity independently to nares via separate flow paths |
US11660413B2 (en) | 2008-07-18 | 2023-05-30 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
CA2734296C (en) | 2008-08-22 | 2018-12-18 | Breathe Technologies, Inc. | Methods and devices for providing mechanical ventilation with an open airway interface |
US8424527B1 (en) * | 2008-09-05 | 2013-04-23 | Cleveland Medical Devices Inc. | Unique device for determining airway obstructions |
US10667727B2 (en) * | 2008-09-05 | 2020-06-02 | Varian Medical Systems, Inc. | Systems and methods for determining a state of a patient |
US20100061596A1 (en) * | 2008-09-05 | 2010-03-11 | Varian Medical Systems Technologies, Inc. | Video-Based Breathing Monitoring Without Fiducial Tracking |
US8398555B2 (en) * | 2008-09-10 | 2013-03-19 | Covidien Lp | System and method for detecting ventilatory instability |
CN104771821B (en) | 2008-09-12 | 2018-10-16 | 瑞思迈有限公司 | The interface structure method and apparatus of foam-based |
US8302602B2 (en) | 2008-09-30 | 2012-11-06 | Nellcor Puritan Bennett Llc | Breathing assistance system with multiple pressure sensors |
JP5711661B2 (en) | 2008-10-01 | 2015-05-07 | ブリーズ・テクノロジーズ・インコーポレーテッド | Ventilator with biofeedback monitoring and controls to improve patient activity and health |
US9155493B2 (en) | 2008-10-03 | 2015-10-13 | Nellcor Puritan Bennett Ireland | Methods and apparatus for calibrating respiratory effort from photoplethysmograph signals |
BRPI0920548B8 (en) | 2008-10-09 | 2021-06-22 | Imthera Medical Inc | device to control the position of a patient's tongue |
EP2349428B1 (en) | 2008-10-10 | 2017-09-20 | Fisher & Paykel Healthcare Limited | Nasal pillows for a patient interface |
EP3184045B1 (en) | 2008-11-19 | 2023-12-06 | Inspire Medical Systems, Inc. | System treating sleep disordered breathing |
JP2010131264A (en) * | 2008-12-05 | 2010-06-17 | Nippon Koden Corp | Respired air information measurement sensor |
WO2010115166A1 (en) | 2009-04-02 | 2010-10-07 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive open ventilation with gas delivery nozzles in free space |
US9132250B2 (en) | 2009-09-03 | 2015-09-15 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
EP2213324B1 (en) | 2009-01-30 | 2016-07-27 | ResMed R&D Germany GmbH | Patient interface structure and method/tool for manufacturing same |
CN102333558B (en) | 2009-02-25 | 2015-08-19 | 皇家飞利浦电子股份有限公司 | Automatic pressure titration |
US8607796B2 (en) | 2009-02-27 | 2013-12-17 | Airway Technologies, Llc | Apparatus and method for coupling an oral appliance to a gas delivery device |
US9962512B2 (en) | 2009-04-02 | 2018-05-08 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with a free space nozzle feature |
AU2010240501A1 (en) * | 2009-04-23 | 2011-10-06 | Yeda Research And Development Co. Ltd. | Nasal flow device controller |
US8545231B2 (en) * | 2009-06-25 | 2013-10-01 | Charles Richard Lloyd | Obstructive sleep apnea demonstration model device |
WO2011029074A1 (en) | 2009-09-03 | 2011-03-10 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
US20110070818A1 (en) * | 2009-09-24 | 2011-03-24 | Lennox Industries Inc. | Air blower validator, an hvac system and a method of manufacturing an hvac system |
US20110112601A1 (en) | 2009-11-10 | 2011-05-12 | Imthera Medical, Inc. | System for stimulating a hypoglossal nerve for controlling the position of a patient's tongue |
EP2501422B1 (en) | 2009-11-16 | 2019-12-25 | ResMed Pty Ltd | Apparatus for adaptable pressure treatment of sleep disordered breathing |
EP2501423A4 (en) | 2009-11-18 | 2014-10-29 | Fisher & Paykel Healthcare Ltd | Nasal interface |
EP3912666A1 (en) | 2009-12-23 | 2021-11-24 | Fisher & Paykel Healthcare Limited | Patient interface and headgear |
US8985104B2 (en) * | 2010-05-19 | 2015-03-24 | Carefusion 207, Inc. | Fan assembly for a rebreathe system |
US10335060B1 (en) | 2010-06-19 | 2019-07-02 | Dp Technologies, Inc. | Method and apparatus to provide monitoring |
CN103096981B (en) | 2010-08-16 | 2015-07-22 | 呼吸科技公司 | Methods, systems and devices using lox to provide ventilatory support |
US20130190641A1 (en) * | 2010-09-22 | 2013-07-25 | Meytar (Dital) Engineering Limited | Modular acoustic spirometer |
US9763626B2 (en) | 2010-09-22 | 2017-09-19 | Breathe.Me Ltd. | Acoustic spirometer system |
US8939152B2 (en) | 2010-09-30 | 2015-01-27 | Breathe Technologies, Inc. | Methods, systems and devices for humidifying a respiratory tract |
WO2012047121A1 (en) | 2010-10-08 | 2012-04-12 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
US8844537B1 (en) | 2010-10-13 | 2014-09-30 | Michael T. Abramson | System and method for alleviating sleep apnea |
US8983572B2 (en) | 2010-10-29 | 2015-03-17 | Inspire Medical Systems, Inc. | System and method for patient selection in treating sleep disordered breathing |
US20130226020A1 (en) * | 2010-11-05 | 2013-08-29 | Resmed Limited | Acoustic detection mask systems and/or methods |
US9457186B2 (en) | 2010-11-15 | 2016-10-04 | Bluewind Medical Ltd. | Bilateral feedback |
US8991392B1 (en) | 2010-12-21 | 2015-03-31 | Fisher & Paykel Healthcare Limited | Pressure adjustment method for CPAP machine |
CN102266616B (en) * | 2010-12-31 | 2014-02-26 | 北京谊安医疗系统股份有限公司 | Method and device for monitoring blockage of breathing equipment |
US20120209084A1 (en) * | 2011-01-21 | 2012-08-16 | Masimo Corporation | Respiratory event alert system |
US10448893B2 (en) | 2011-01-25 | 2019-10-22 | ResMed Pty Ltd | Method and apparatus for detecting respiratory effort |
US9084859B2 (en) | 2011-03-14 | 2015-07-21 | Sleepnea Llc | Energy-harvesting respiratory method and device |
WO2012138459A1 (en) | 2011-04-05 | 2012-10-11 | Airway Technologies, Llc | Oral appliance for treating particular disorders associated with sleep |
US10603456B2 (en) | 2011-04-15 | 2020-03-31 | Fisher & Paykel Healthcare Limited | Interface comprising a nasal sealing portion |
EP4282456A3 (en) | 2011-04-15 | 2024-02-14 | Fisher & Paykel Healthcare Limited | Interface comprising a rolling nasal bridge portion |
US9789273B2 (en) | 2011-05-13 | 2017-10-17 | Koninklijke Philips N.V. | Sensor and valve integrated into a patient interface |
US9486602B2 (en) | 2011-06-22 | 2016-11-08 | Breathe Technologies, Inc. | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
US8839791B2 (en) | 2011-06-22 | 2014-09-23 | Breathe Technologies, Inc. | Ventilation mask with integrated piloted exhalation valve |
US9038634B2 (en) | 2011-06-22 | 2015-05-26 | Breathe Technologies, Inc. | Ventilation mask with integrated piloted exhalation valve |
US20150039045A1 (en) | 2011-08-11 | 2015-02-05 | Inspire Medical Systems, Inc. | Method and system for applying stimulation in treating sleep disordered breathing |
WO2013111137A2 (en) | 2012-01-26 | 2013-08-01 | Rainbow Medical Ltd. | Wireless neurqstimulatqrs |
US9114256B2 (en) | 2012-01-31 | 2015-08-25 | Torytrans, S.L | Electrostimulation method and system for the treatment of sleep apnea |
US9399109B2 (en) | 2012-03-02 | 2016-07-26 | Breathe Technologies, Inc. | Continuous positive airway pressure (CPAP) therapy using measurements of speed and pressure |
US10179218B2 (en) | 2012-03-02 | 2019-01-15 | Breathe Technologies, Inc. | Dual pressure sensor continuous positive airway pressure (CPAP) therapy |
US11191914B2 (en) | 2012-03-02 | 2021-12-07 | Breathe Techologies, Inc. | Dual pressure sensor continuous positive airway pressure (CPAP) therapy |
US9180271B2 (en) | 2012-03-05 | 2015-11-10 | Hill-Rom Services Pte. Ltd. | Respiratory therapy device having standard and oscillatory PEP with nebulizer |
US9459597B2 (en) | 2012-03-06 | 2016-10-04 | DPTechnologies, Inc. | Method and apparatus to provide an improved sleep experience by selecting an optimal next sleep state for a user |
US10791986B1 (en) | 2012-04-05 | 2020-10-06 | Dp Technologies, Inc. | Sleep sound detection system and use |
JP5942566B2 (en) * | 2012-04-19 | 2016-06-29 | 富士通株式会社 | Apnea determination program, apnea determination apparatus, and apnea determination method |
US9669172B2 (en) | 2012-07-05 | 2017-06-06 | Resmed Limited | Discreet respiratory therapy system |
CN107626023B (en) | 2012-08-08 | 2021-03-02 | 费雪派克医疗保健有限公司 | Interface assembly for use in providing respiratory therapy |
US10159446B2 (en) * | 2012-09-04 | 2018-12-25 | Gregg A. Dickerson | Medical gating using positive airway pressure devices |
EP4279106A3 (en) | 2012-09-04 | 2024-01-17 | Fisher & Paykel Healthcare Limited | Valsalva mask |
US9839756B2 (en) | 2012-11-27 | 2017-12-12 | Resmed Limited | Methods and apparatus for ionization therapy |
WO2014087337A1 (en) | 2012-12-06 | 2014-06-12 | Bluewind Medical Ltd. | Delivery of implantable neurostimulators |
US10780017B2 (en) | 2013-03-15 | 2020-09-22 | Somne Llc | Treating sleep apnea with negative pressure |
US10548760B2 (en) | 2013-03-15 | 2020-02-04 | Somne Llc | Correlating a condition of a subject with a degree of sleep apnea being experienced by the subject |
KR20150139865A (en) | 2013-03-15 | 2015-12-14 | 잔소르스 엘엘씨 | Health monitoring, surveillance and anomaly detection |
WO2015038666A1 (en) | 2013-09-10 | 2015-03-19 | Ahmad Samir S | Zero pressure start continuous positive airway pressure therapy |
US20160271429A1 (en) * | 2013-10-17 | 2016-09-22 | Shigematsu Works Co., Ltd. | Breathing apparatus |
US11257593B2 (en) | 2014-01-29 | 2022-02-22 | Umethod Health, Inc. | Interactive and analytical system that provides a dynamic tool for therapies to prevent and cure dementia-related diseases |
US10369310B2 (en) | 2014-03-05 | 2019-08-06 | ResMed Pty Ltd | Method and apparatus for treatment of respiratory disorders |
NZ765842A (en) * | 2014-06-10 | 2022-02-25 | ResMed Pty Ltd | Method and apparatus for treatment of respiratory disorders |
GB2587295B8 (en) | 2014-08-25 | 2021-09-29 | Fisher & Paykel Healthcare Ltd | Respiratory mask and related portions, components or sub-assemblies |
TWI564041B (en) * | 2014-08-28 | 2017-01-01 | Apex Medical Corp | A breathing gas supply system and a control method thereof, and a computer program product for executing the method |
US10828452B2 (en) | 2014-09-16 | 2020-11-10 | Fisher & Paykel Healthcare Limited | Intramold headgear |
US10112022B2 (en) | 2014-09-18 | 2018-10-30 | Devilbiss Healthcare Llc | Method for detecting an inspiratory flow limitation during sleep-disordered breathing |
US10646680B2 (en) | 2014-09-19 | 2020-05-12 | Fisher & Paykel Healthcare Limited | Headgear assemblies and interface assemblies with headgear |
US10004896B2 (en) | 2015-01-21 | 2018-06-26 | Bluewind Medical Ltd. | Anchors and implant devices |
US9764146B2 (en) | 2015-01-21 | 2017-09-19 | Bluewind Medical Ltd. | Extracorporeal implant controllers |
US9597521B2 (en) | 2015-01-21 | 2017-03-21 | Bluewind Medical Ltd. | Transmitting coils for neurostimulation |
US11883188B1 (en) | 2015-03-16 | 2024-01-30 | Dp Technologies, Inc. | Sleep surface sensor based sleep analysis system |
CN113908438A (en) | 2015-03-19 | 2022-01-11 | 启迪医疗仪器公司 | Stimulation for treating sleep disordered breathing |
US10905836B2 (en) | 2015-04-02 | 2021-02-02 | Hill-Rom Services Pte. Ltd. | Manifold for respiratory device |
US11147505B1 (en) * | 2015-06-01 | 2021-10-19 | Verily Life Sciences Llc | Methods, systems and devices for identifying an abnormal sleep condition |
US9782589B2 (en) | 2015-06-10 | 2017-10-10 | Bluewind Medical Ltd. | Implantable electrostimulator for improving blood flow |
US10589051B2 (en) | 2015-10-20 | 2020-03-17 | Steven Salter | CPAP compliance notification apparatus and method |
US10105540B2 (en) | 2015-11-09 | 2018-10-23 | Bluewind Medical Ltd. | Optimization of application of current |
US9713707B2 (en) | 2015-11-12 | 2017-07-25 | Bluewind Medical Ltd. | Inhibition of implant migration |
CN108290019B (en) | 2015-12-01 | 2021-06-18 | 皇家飞利浦有限公司 | Method and apparatus for treating ataxic breathing |
US11298074B2 (en) | 2015-12-08 | 2022-04-12 | Fisher & Paykel Healthcare Limited | Flow-based sleep stage determination |
CA3017566A1 (en) | 2016-03-16 | 2017-09-21 | Fisher & Paykel Healthcare Limited | Strap assembly, strap connector, headgear, headgear assembly, method of forming headgear, tubular connector, patient interface and method of joining straps |
SG10202009031VA (en) | 2016-03-16 | 2020-10-29 | Fisher & Paykel Healthcare Ltd | Intra-mould substrate |
AU2017234346B2 (en) | 2016-03-16 | 2022-06-30 | Fisher & Paykel Healthcare Limited | Directional lock for interface headgear arrangement |
USD882066S1 (en) | 2016-05-13 | 2020-04-21 | Fisher & Paykel Healthcare Limited | Frame for a breathing mask |
US10124178B2 (en) | 2016-11-23 | 2018-11-13 | Bluewind Medical Ltd. | Implant and delivery tool therefor |
USD824020S1 (en) | 2017-02-23 | 2018-07-24 | Fisher & Paykel Healthcare Limited | Cushion assembly for breathing mask assembly |
USD823454S1 (en) | 2017-02-23 | 2018-07-17 | Fisher & Paykel Healthcare Limited | Cushion assembly for breathing mask assembly |
USD823455S1 (en) | 2017-02-23 | 2018-07-17 | Fisher & Paykel Healthcare Limited | Cushion assembly for breathing mask assembly |
WO2018201197A1 (en) | 2017-05-05 | 2018-11-08 | Resmed Limited | Screening, diagnosis and monitoring of respiratory disorders |
US20180353764A1 (en) | 2017-06-13 | 2018-12-13 | Bluewind Medical Ltd. | Antenna configuration |
CN110831649B (en) * | 2017-06-30 | 2023-02-10 | 皇家飞利浦有限公司 | Systems and methods for concurrent airway stabilization and lung stretch receptor activation |
US10792449B2 (en) | 2017-10-03 | 2020-10-06 | Breathe Technologies, Inc. | Patient interface with integrated jet pump |
WO2019175814A1 (en) | 2018-03-16 | 2019-09-19 | Fisher & Paykel Healthcare Limited | Headgear with lock disengagement mechanism |
CN109276788A (en) * | 2018-08-24 | 2019-01-29 | 广州康智件科技有限公司 | A kind of respiratory rate acquisition method and its device for oxygen uptake monitoring |
US11471097B1 (en) | 2018-10-15 | 2022-10-18 | Dp Technologies, Inc. | Hardware sensor system for improved sleep detection |
JP7314263B2 (en) | 2018-10-23 | 2023-07-25 | レスメド・プロプライエタリー・リミテッド | System and method for setting up a CPAP system |
US11266837B2 (en) | 2019-03-06 | 2022-03-08 | Medtronic Xomed, Inc. | Position sensitive lingual muscle simulation system for obstructive sleep apnea |
EP4162499A1 (en) | 2020-06-05 | 2023-04-12 | ResMed Sensor Technologies Limited | Systems and methods for identifying a user interface |
CA3181675A1 (en) | 2020-06-08 | 2021-12-16 | Graeme LYON | Systems and methods for categorizing and/or characterizing a user interface |
EP4189697A1 (en) | 2020-07-30 | 2023-06-07 | ResMed, Inc. | Systems and methods for determining a health condition on a device local to a respiratory system user |
US20240024597A1 (en) | 2020-08-31 | 2024-01-25 | Resmed Sensor Technologies Limited | Systems and methods for pre-symptomatic disease detection |
JP2023544119A (en) | 2020-09-18 | 2023-10-20 | レズメド センサー テクノロジーズ リミテッド | Systems and methods for monitoring comorbidities |
EP4237793A1 (en) | 2020-10-30 | 2023-09-06 | ResMed Sensor Technologies Limited | Systems and methods for determining a length and/or a diameter of a conduit |
EP4264631A1 (en) | 2020-12-18 | 2023-10-25 | ResMed Sensor Technologies Limited | Cohort sleep performance evaluation |
US20240066249A1 (en) | 2020-12-23 | 2024-02-29 | Resmed Sensor Technologies Limited | Systems and methods for detecting occlusions in headgear conduits during respiratory therapy |
EP4267223A1 (en) | 2020-12-23 | 2023-11-01 | ResMed Sensor Technologies Limited | Systems and methods for detecting rainout in a respiratory therapy system |
EP4329848A1 (en) | 2021-04-29 | 2024-03-06 | ResMed Sensor Technologies Limited | Systems and methods for modifying pressure settings of a respiratory therapy system |
US11400299B1 (en) | 2021-09-14 | 2022-08-02 | Rainbow Medical Ltd. | Flexible antenna for stimulator |
WO2023187686A1 (en) | 2022-03-30 | 2023-10-05 | ResMed Pty Ltd | Systems and methods for determining a positional sleep disordered breathing status |
WO2023192481A1 (en) | 2022-03-31 | 2023-10-05 | Resmed Inc. | Methods and systems for an overall health score |
Citations (97)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US35295A (en) * | 1862-05-20 | Improvement in water-elevators | ||
US2904033A (en) * | 1957-03-04 | 1959-09-15 | Sylvan M Shane | Breathing indicator |
US3559638A (en) * | 1967-09-19 | 1971-02-02 | James A Potter | Respiration meter having several modes of operation |
US3595228A (en) * | 1968-11-27 | 1971-07-27 | Robert C Simon | Flow line break alarm device |
US3611801A (en) * | 1968-10-28 | 1971-10-12 | Nasa | Respiration monitor |
US3726270A (en) * | 1971-09-20 | 1973-04-10 | Syst Res Labor Inc | Pulmonary information transmission system |
US3802417A (en) * | 1968-12-21 | 1974-04-09 | V Lang | Device for combined monitoring and stimulation of respiration |
US3817246A (en) * | 1972-12-11 | 1974-06-18 | Puritan Bennett Corp | Flow responsive respiration apparatus |
US3834383A (en) * | 1972-12-11 | 1974-09-10 | Puritan Bennett Corp | Respiration apparatus with flow responsive control valve |
US3840006A (en) * | 1973-04-26 | 1974-10-08 | Department Of Health Education | Respirator |
US3863630A (en) * | 1971-11-10 | 1975-02-04 | Synthelabo | Respiratory apparatus |
US3882847A (en) * | 1973-12-11 | 1975-05-13 | Harvey Barry Jacobs | Low-Cost Pneumatic Apnea or Respiration Monitor |
US3903875A (en) * | 1974-01-24 | 1975-09-09 | Sandoz Ag | Automatically calibrated respiratory ventilation monitor |
US3914994A (en) * | 1971-12-15 | 1975-10-28 | Philip M Banner | Liquid flow indicating and flow control means |
US3932054A (en) * | 1974-07-17 | 1976-01-13 | Western Engineering & Mfg. Co. | Variable pitch axial fan |
US3961627A (en) * | 1973-09-07 | 1976-06-08 | Hoffmann-La Roche Inc. | Automatic regulation of respirators |
US3972327A (en) * | 1973-03-22 | 1976-08-03 | Hoffmann-La Roche Inc. | Respirator |
US3985467A (en) * | 1975-05-27 | 1976-10-12 | Milton Roy Company | Constant pressure pump |
US4006634A (en) * | 1975-09-17 | 1977-02-08 | National Semiconductor Corporation | Flow meter |
US4016876A (en) * | 1973-11-06 | 1977-04-12 | Westinghouse Electric Corporation | Breathing apparatus |
US4083245A (en) * | 1977-03-21 | 1978-04-11 | Research Development Corporation | Variable orifice gas flow sensing head |
US4206754A (en) * | 1976-06-02 | 1980-06-10 | Boc Limited | Lung ventilators |
US4312235A (en) * | 1980-09-02 | 1982-01-26 | United Technologies Corporation | Sensor and meter for measuring the mass flow of a fluid stream |
US4322594A (en) * | 1980-06-27 | 1982-03-30 | Respiratory Care, Inc. | Temperature control system with alarm and shut down for non-tracking condition of dual thermometers |
US4347468A (en) * | 1980-04-28 | 1982-08-31 | Lake Center Industries | Electronic variable speed automotive blower control system |
US4368740A (en) * | 1980-11-03 | 1983-01-18 | Binder Andy S | Physiologic analyzer |
US4381788A (en) * | 1981-02-27 | 1983-05-03 | Douglas David W | Method and apparatus for detecting apnea |
US4387722A (en) * | 1978-11-24 | 1983-06-14 | Kearns Kenneth L | Respiration monitor and x-ray triggering apparatus |
US4430468A (en) * | 1982-07-21 | 1984-02-07 | E. I. Du Pont De Nemours And Company | Surfactant-containing filled and plasticized thermoplastic compositions based on ethylene interpolymers |
US4433693A (en) * | 1979-09-27 | 1984-02-28 | Hochstein Peter A | Method and assembly for monitoring respiration and detecting apnea |
US4448058A (en) * | 1982-07-02 | 1984-05-15 | Sensormedics Corporation | Respiratory gas analysis instrument having improved volume calibration method and apparatus |
US4452252A (en) * | 1981-05-26 | 1984-06-05 | Respitrace Corporation | Non-invasive method for monitoring cardiopulmonary parameters |
US4499914A (en) * | 1983-04-14 | 1985-02-19 | Litton Systems, Inc. | Selector valve for an aircraft on board oxygen generation system with high pressure oxygen backup |
US4519399A (en) * | 1982-12-13 | 1985-05-28 | Rion Kabushiki Kaisha | Method for measuring the degree of nasality |
US4537190A (en) * | 1981-12-11 | 1985-08-27 | Synthelabo | Process and device for controlling artificial respiration |
US4570631A (en) * | 1982-12-03 | 1986-02-18 | Kircaldie, Randall And Mcnab (As Trustee) | Respirating gas supply method and apparatus therefor |
US4580575A (en) * | 1982-06-14 | 1986-04-08 | Aequitron Medical, Inc. | Apnea monitoring system |
US4595016A (en) * | 1985-01-30 | 1986-06-17 | Mine Safety Appliances Co. | APNEA monitor |
US4602644A (en) * | 1982-08-18 | 1986-07-29 | Plasmedics, Inc. | Physiological detector and monitor |
US4619270A (en) * | 1984-04-16 | 1986-10-28 | Margolis Frederick J | Infant respiratory arrest stimulator device |
US4648407A (en) * | 1985-07-08 | 1987-03-10 | Respitrace Corporation | Method for detecting and differentiating central and obstructive apneas in newborns |
US4648396A (en) * | 1985-05-03 | 1987-03-10 | Brigham And Women's Hospital | Respiration detector |
US4677975A (en) * | 1984-10-16 | 1987-07-07 | The University Of Auckland | Method of dispensing and/or a dispenser |
US4686975A (en) * | 1985-05-03 | 1987-08-18 | Applied Membrane Technology, Inc. | Electronic respirable gas delivery device |
US4686974A (en) * | 1985-10-18 | 1987-08-18 | Tottori University | Breath synchronized gas-insufflation device and method therefor |
US4686999A (en) * | 1985-04-10 | 1987-08-18 | Tri Fund Research Corporation | Multi-channel ventilation monitor and method |
US4738266A (en) * | 1983-05-09 | 1988-04-19 | Thatcher John B | Apnoea monitor |
US4747403A (en) * | 1986-01-27 | 1988-05-31 | Advanced Pulmonary Technologies, Inc. | Multi-frequency jet ventilation technique and apparatus |
US4777963A (en) * | 1987-06-18 | 1988-10-18 | Mckenna Kevin | Respiration monitor |
US4795314A (en) * | 1987-08-24 | 1989-01-03 | Cobe Laboratories, Inc. | Condition responsive pump control utilizing integrated, commanded, and sensed flowrate signals |
US4802485A (en) * | 1987-09-02 | 1989-02-07 | Sentel Technologies, Inc. | Sleep apnea monitor |
US4802492A (en) * | 1987-03-11 | 1989-02-07 | National Jewish Center For Immunology And Respiratory Medicine | Method for determining respiratory function |
US4803471A (en) * | 1986-10-24 | 1989-02-07 | Hudson Oxygen Therapy Sales Co. | Ventilator monitor and alarm apparatus |
US4819629A (en) * | 1986-10-28 | 1989-04-11 | Siemens Aktiengesellschaft | Method and apparatus for delivering aerosol to the airways and/or lungs of a patient |
US4823788A (en) * | 1988-04-18 | 1989-04-25 | Smith Richard F M | Demand oxygen controller and respiratory monitor |
US4825802A (en) * | 1986-07-24 | 1989-05-02 | Societe Anonyme Drager | Pheumatic alarm for respirator |
US4827922A (en) * | 1987-03-05 | 1989-05-09 | L'air Liquide | Process and device for supplying respiratory oxygen |
US4836258A (en) * | 1987-07-10 | 1989-06-06 | Ellis Reginald C L | Attachment apparatus for a tire mat |
US4837386A (en) * | 1987-06-24 | 1989-06-06 | Air Products And Chemicals, Inc. | Method of treating membranes with ultraviolet radiation |
US4838257A (en) * | 1987-07-17 | 1989-06-13 | Hatch Guy M | Ventilator |
US4838275A (en) * | 1985-11-29 | 1989-06-13 | Lee Arnold St J | Home medical surveillance system |
US4844085A (en) * | 1985-09-13 | 1989-07-04 | Luciano Gattinoni | Pulmonary pressure and volume measurement |
US4860766A (en) * | 1983-11-18 | 1989-08-29 | Respitrace Corp. | Noninvasive method for measuring and monitoring intrapleural pressure in newborns |
US4915103A (en) * | 1987-12-23 | 1990-04-10 | N. Visveshwara, M.D., Inc. | Ventilation synchronizer |
US4928684A (en) * | 1988-05-27 | 1990-05-29 | Salvia-Werk Gesellschaft Zur Herstellung Chemischer And Pharmazeutischer Erzeuginisse Mbh | Apparatus for assisting the spontaneous respiration of a patient |
US4938210A (en) * | 1989-04-25 | 1990-07-03 | Trudell Medical | Inhalation chamber in ventilator circuit |
US4938212A (en) * | 1987-10-16 | 1990-07-03 | Puritan-Bennett Corporation | Inspiration oxygen saver |
US4957107A (en) * | 1988-05-10 | 1990-09-18 | Sipin Anatole J | Gas delivery means |
US4982738A (en) * | 1988-11-30 | 1991-01-08 | Dr. Madaus Gmbh | Diagnostic apnea monitor system |
US4986269A (en) * | 1985-05-23 | 1991-01-22 | Etela-Hameen Keuhkovammayhdistys R.Y. | Respiration therapy apparatus |
US5024219A (en) * | 1987-01-12 | 1991-06-18 | Dietz Henry G | Apparatus for inhalation therapy using triggered dose oxygenator employing an optoelectronic inhalation sensor |
US5046491A (en) * | 1990-03-27 | 1991-09-10 | Derrick Steven J | Apparatus and method for respired gas collection and analysis |
US5048515A (en) * | 1988-11-15 | 1991-09-17 | Sanso David W | Respiratory gas supply apparatus and method |
US5099837A (en) * | 1990-09-28 | 1992-03-31 | Russel Sr Larry L | Inhalation-based control of medical gas |
US5105354A (en) * | 1989-01-23 | 1992-04-14 | Nippon Kayaku Kabushiki Kaisha | Method and apparatus for correlating respiration and heartbeat variability |
US5107830A (en) * | 1987-02-21 | 1992-04-28 | University Of Manitoba | Lung ventilator device |
US5107831A (en) * | 1989-06-19 | 1992-04-28 | Bear Medical Systems, Inc. | Ventilator control system using sensed inspiratory flow rate |
US5117819A (en) * | 1990-09-10 | 1992-06-02 | Healthdyne, Inc. | Nasal positive pressure device |
US5129390A (en) * | 1987-12-18 | 1992-07-14 | Institut Nationale De La Sante Et De La Recherche Medicale | Process for regulating an artificial ventilation device and such device |
US5134995A (en) * | 1989-05-19 | 1992-08-04 | Puritan-Bennett Corporation | Inspiratory airway pressure system with admittance determining apparatus and method |
US5195528A (en) * | 1990-02-16 | 1993-03-23 | Hok Instrument Ab | Acoustic respiration detector |
US5199424A (en) * | 1987-06-26 | 1993-04-06 | Sullivan Colin E | Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled |
US5203343A (en) * | 1991-06-14 | 1993-04-20 | Board Of Regents, The University Of Texas System | Method and apparatus for controlling sleep disorder breathing |
US5231983A (en) * | 1990-01-03 | 1993-08-03 | Minnesota Mining And Manufacturing | Method of and apparatus for the aerosol administration of medication |
US5239995A (en) * | 1989-09-22 | 1993-08-31 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5239994A (en) * | 1991-05-10 | 1993-08-31 | Bunnell Incorporated | Jet ventilator system |
US5303698A (en) * | 1991-08-27 | 1994-04-19 | The Boc Group, Inc. | Medical ventilator |
US5303700A (en) * | 1991-07-04 | 1994-04-19 | Dragerwerk Aktiengesellschaft | Method for detecting the respiratory phases of a patient during an assisted ventilating process |
US5313937A (en) * | 1989-09-22 | 1994-05-24 | Respironics Inc. | Leak compensation method and apparatus for a breathing system |
US5322057A (en) * | 1987-07-08 | 1994-06-21 | Vortran Medical Technology, Inc. | Intermittent signal actuated nebulizer synchronized to operate in the exhalation phase, and its method of use |
US5388571A (en) * | 1987-07-17 | 1995-02-14 | Roberts; Josephine A. | Positive-pressure ventilator system with controlled access for nebulizer component servicing |
US5400777A (en) * | 1990-10-31 | 1995-03-28 | Siemens Aktiengesellschaft | Ventilator |
US5509414A (en) * | 1994-09-27 | 1996-04-23 | Hok Instrument Ab | Apparatus and method for non-contacting detection of respiration |
US5535739A (en) * | 1992-05-07 | 1996-07-16 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5540219A (en) * | 1995-01-26 | 1996-07-30 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5549106A (en) * | 1989-05-19 | 1996-08-27 | Puritan-Bennett Corporation | Inspiratory airway pressure system using constant pressure and measuring flow signals to determine airway patency |
US5660171A (en) * | 1990-05-11 | 1997-08-26 | Puritan-Bennett Corporation | System and method for flow triggering of pressure supported ventilation by comparison of inhalation and exhalation flow rates |
Family Cites Families (41)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3559838A (en) * | 1968-08-15 | 1971-02-02 | Foster Wheeler Corp | Manway removal apparatus |
US3989037A (en) | 1970-06-23 | 1976-11-02 | Siemens Aktiengesellschaft | Flow measuring device |
US3926177A (en) | 1972-09-11 | 1975-12-16 | Cavitron Corp | Activity and respiration monitor |
US4239039A (en) * | 1979-02-28 | 1980-12-16 | Thompson Harris A | Dual control valve for positive pressure artificial respiration apparatus |
DE3021326A1 (en) | 1980-06-06 | 1981-12-17 | Drägerwerk AG, 2400 Lübeck | DEVICE FOR MEASURING AT LEAST TWO PNEUMATIC LUNG PARAMETERS AND MEASURING METHODS THEREFOR |
DE3023648A1 (en) | 1980-06-24 | 1982-01-21 | Jaeger, Erich, 8700 Würzburg | DEVICE FOR EXAMINING THE RESPIRATORY RESPIRATORY SENSITIVITY |
US4414982A (en) | 1980-11-26 | 1983-11-15 | Tritec Industries, Inc. | Apneic event detector and method |
DE3276924D1 (en) * | 1981-04-24 | 1987-09-17 | Somed Pty Ltd | Device for treating snoring sickness |
US4430995A (en) * | 1981-05-29 | 1984-02-14 | Hilton Joseph R | Power assisted air-purifying respirators |
US4481944A (en) | 1981-11-19 | 1984-11-13 | Bunnell Life Systems, Inc. | Apparatus and method for assisting respiration |
US4516424A (en) * | 1982-07-09 | 1985-05-14 | Hudson Oxygen Therapy Sales Company | Oxygen concentrator monitor and regulation assembly |
US4550726A (en) | 1982-07-15 | 1985-11-05 | Mcewen James A | Method and apparatus for detection of breathing gas interruptions |
EP0104004A1 (en) | 1982-09-06 | 1984-03-28 | Graham Cameron Grant | Fluid flowmeter and method of measuring flow rate |
IL71468A (en) * | 1984-04-08 | 1988-06-30 | Dan Atlas | Apnea monitoring method and apparatus |
DE3422066A1 (en) * | 1984-06-14 | 1985-12-19 | Drägerwerk AG, 2400 Lübeck | VENTILATION SYSTEM AND CONTROLLABLE VALVE UNIT TO |
FR2568397B1 (en) * | 1984-07-27 | 1987-08-14 | Mequignon Jean Claude | PROCESS FOR STOPPING THE HUMAN SNORING OF ITS EMISSIONS AND APPARATUS NECESSARY FOR THE IMPLEMENTATION OF THIS PROCESS |
US4971065A (en) | 1985-02-11 | 1990-11-20 | Pearce Stephen D | Transducer for detecting apnea |
EP0218690A4 (en) * | 1985-04-10 | 1987-07-22 | Emergent Technology Corp | Multi-channel ventilation monitor and method. |
US4870960A (en) | 1985-10-07 | 1989-10-03 | Litton Systems, Inc. | Backup breathing gas supply for an oxygen concentrator system |
SE451232C (en) * | 1985-10-25 | 1992-03-04 | Carl Eric Persson | DEVICE FOR THE PREVENTION OF SNORING FROM A SLEEPING PERSON |
US4688974A (en) * | 1985-12-20 | 1987-08-25 | Deere & Company | Cooperating bolster and fixture construction for quick-change fixturing |
US4848396A (en) * | 1986-01-10 | 1989-07-18 | Sisk David E | Cast hopper tee |
US5052400A (en) | 1986-02-20 | 1991-10-01 | Dietz Henry G | Method and apparatus for using an inhalation sensor for monitoring and for inhalation therapy |
US4782832A (en) * | 1987-07-30 | 1988-11-08 | Puritan-Bennett Corporation | Nasal puff with adjustable sealing means |
US4838258A (en) | 1987-10-26 | 1989-06-13 | Gibeck-Dryden Corporation | Gas sampling lumen for breathing system |
US5065756A (en) * | 1987-12-22 | 1991-11-19 | New York University | Method and apparatus for the treatment of obstructive sleep apnea |
FI82808C (en) | 1987-12-31 | 1991-04-25 | Etelae Haemeen Keuhkovammayhdi | Ultraljudfinfördelningsanordning |
US5170798A (en) | 1988-02-10 | 1992-12-15 | Sherwood Medical Company | Pulmonary function tester |
US4972842A (en) | 1988-06-09 | 1990-11-27 | Vital Signals, Inc. | Method and apparatus for precision monitoring of infants on assisted ventilation |
US4960118A (en) | 1989-05-01 | 1990-10-02 | Pennock Bernard E | Method and apparatus for measuring respiratory flow |
USRE35295E (en) * | 1989-09-22 | 1996-07-16 | Respironics, Inc. | Sleep apnea treatment apparatus |
EP0467853B1 (en) * | 1990-07-18 | 1996-01-10 | AVL Medical Instruments AG | Device and method for the measurement of blood pressure |
US5063938A (en) | 1990-11-01 | 1991-11-12 | Beck Donald C | Respiration-signalling device |
EP0491969B1 (en) | 1990-12-20 | 1995-08-23 | Siemens-Elema AB | Lung ventilator with a flow rate dependent trigger threshold |
EP0553372B1 (en) * | 1992-01-29 | 1996-11-13 | Hewlett-Packard GmbH | Method and system for monitoring vital signs |
US5549108A (en) * | 1992-09-25 | 1996-08-27 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5682898A (en) * | 1995-04-19 | 1997-11-04 | Colin Corporation | Respiration rate measuring apparatus |
US5730147A (en) * | 1996-01-11 | 1998-03-24 | Craig; Robert J. | Combined thermometer and fecal sampling apparatus |
US5853005A (en) * | 1996-05-02 | 1998-12-29 | The United States Of America As Represented By The Secretary Of The Army | Acoustic monitoring system |
DE69730298T2 (en) * | 1996-06-12 | 2005-01-13 | Seiko Epson Corp. | KOERPERTEMPERATURMESSVORRICHTUNG |
US6998980B2 (en) * | 2003-05-01 | 2006-02-14 | University Of Florida Research Foundation, Inc. | Microfield interface device for monitoring animal cage environments |
-
1991
- 1991-12-12 US US07/806,157 patent/US5199424A/en not_active Expired - Lifetime
-
1992
- 1992-05-27 US US07/892,692 patent/US5245995A/en not_active Expired - Lifetime
-
2002
- 2002-01-18 US US10/050,163 patent/US7004908B2/en not_active Expired - Fee Related
- 2002-03-04 US US10/086,444 patent/US6770037B2/en not_active Expired - Fee Related
-
2005
- 2005-07-21 US US11/186,695 patent/US7141021B2/en not_active Expired - Fee Related
-
2006
- 2006-10-30 US US11/554,378 patent/US20070051371A1/en not_active Abandoned
Patent Citations (99)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US35295A (en) * | 1862-05-20 | Improvement in water-elevators | ||
US2904033A (en) * | 1957-03-04 | 1959-09-15 | Sylvan M Shane | Breathing indicator |
US3559638A (en) * | 1967-09-19 | 1971-02-02 | James A Potter | Respiration meter having several modes of operation |
US3611801A (en) * | 1968-10-28 | 1971-10-12 | Nasa | Respiration monitor |
US3595228A (en) * | 1968-11-27 | 1971-07-27 | Robert C Simon | Flow line break alarm device |
US3802417A (en) * | 1968-12-21 | 1974-04-09 | V Lang | Device for combined monitoring and stimulation of respiration |
US3726270A (en) * | 1971-09-20 | 1973-04-10 | Syst Res Labor Inc | Pulmonary information transmission system |
US3863630A (en) * | 1971-11-10 | 1975-02-04 | Synthelabo | Respiratory apparatus |
US3914994A (en) * | 1971-12-15 | 1975-10-28 | Philip M Banner | Liquid flow indicating and flow control means |
US3817246A (en) * | 1972-12-11 | 1974-06-18 | Puritan Bennett Corp | Flow responsive respiration apparatus |
US3834383A (en) * | 1972-12-11 | 1974-09-10 | Puritan Bennett Corp | Respiration apparatus with flow responsive control valve |
US3972327A (en) * | 1973-03-22 | 1976-08-03 | Hoffmann-La Roche Inc. | Respirator |
US3840006A (en) * | 1973-04-26 | 1974-10-08 | Department Of Health Education | Respirator |
US3961627A (en) * | 1973-09-07 | 1976-06-08 | Hoffmann-La Roche Inc. | Automatic regulation of respirators |
US4016876A (en) * | 1973-11-06 | 1977-04-12 | Westinghouse Electric Corporation | Breathing apparatus |
US3882847A (en) * | 1973-12-11 | 1975-05-13 | Harvey Barry Jacobs | Low-Cost Pneumatic Apnea or Respiration Monitor |
US3903875A (en) * | 1974-01-24 | 1975-09-09 | Sandoz Ag | Automatically calibrated respiratory ventilation monitor |
US3932054A (en) * | 1974-07-17 | 1976-01-13 | Western Engineering & Mfg. Co. | Variable pitch axial fan |
US3985467A (en) * | 1975-05-27 | 1976-10-12 | Milton Roy Company | Constant pressure pump |
US4006634A (en) * | 1975-09-17 | 1977-02-08 | National Semiconductor Corporation | Flow meter |
US4206754A (en) * | 1976-06-02 | 1980-06-10 | Boc Limited | Lung ventilators |
US4083245A (en) * | 1977-03-21 | 1978-04-11 | Research Development Corporation | Variable orifice gas flow sensing head |
US4387722A (en) * | 1978-11-24 | 1983-06-14 | Kearns Kenneth L | Respiration monitor and x-ray triggering apparatus |
US4433693A (en) * | 1979-09-27 | 1984-02-28 | Hochstein Peter A | Method and assembly for monitoring respiration and detecting apnea |
US4347468A (en) * | 1980-04-28 | 1982-08-31 | Lake Center Industries | Electronic variable speed automotive blower control system |
US4322594A (en) * | 1980-06-27 | 1982-03-30 | Respiratory Care, Inc. | Temperature control system with alarm and shut down for non-tracking condition of dual thermometers |
US4312235A (en) * | 1980-09-02 | 1982-01-26 | United Technologies Corporation | Sensor and meter for measuring the mass flow of a fluid stream |
US4368740A (en) * | 1980-11-03 | 1983-01-18 | Binder Andy S | Physiologic analyzer |
US4381788A (en) * | 1981-02-27 | 1983-05-03 | Douglas David W | Method and apparatus for detecting apnea |
US4452252A (en) * | 1981-05-26 | 1984-06-05 | Respitrace Corporation | Non-invasive method for monitoring cardiopulmonary parameters |
US4537190A (en) * | 1981-12-11 | 1985-08-27 | Synthelabo | Process and device for controlling artificial respiration |
US4580575A (en) * | 1982-06-14 | 1986-04-08 | Aequitron Medical, Inc. | Apnea monitoring system |
US4448058A (en) * | 1982-07-02 | 1984-05-15 | Sensormedics Corporation | Respiratory gas analysis instrument having improved volume calibration method and apparatus |
US4430468A (en) * | 1982-07-21 | 1984-02-07 | E. I. Du Pont De Nemours And Company | Surfactant-containing filled and plasticized thermoplastic compositions based on ethylene interpolymers |
US4602644A (en) * | 1982-08-18 | 1986-07-29 | Plasmedics, Inc. | Physiological detector and monitor |
US4570631A (en) * | 1982-12-03 | 1986-02-18 | Kircaldie, Randall And Mcnab (As Trustee) | Respirating gas supply method and apparatus therefor |
US4519399A (en) * | 1982-12-13 | 1985-05-28 | Rion Kabushiki Kaisha | Method for measuring the degree of nasality |
US4499914A (en) * | 1983-04-14 | 1985-02-19 | Litton Systems, Inc. | Selector valve for an aircraft on board oxygen generation system with high pressure oxygen backup |
US4738266A (en) * | 1983-05-09 | 1988-04-19 | Thatcher John B | Apnoea monitor |
US4860766A (en) * | 1983-11-18 | 1989-08-29 | Respitrace Corp. | Noninvasive method for measuring and monitoring intrapleural pressure in newborns |
US4619270A (en) * | 1984-04-16 | 1986-10-28 | Margolis Frederick J | Infant respiratory arrest stimulator device |
US4677975A (en) * | 1984-10-16 | 1987-07-07 | The University Of Auckland | Method of dispensing and/or a dispenser |
US4595016A (en) * | 1985-01-30 | 1986-06-17 | Mine Safety Appliances Co. | APNEA monitor |
US4686999A (en) * | 1985-04-10 | 1987-08-18 | Tri Fund Research Corporation | Multi-channel ventilation monitor and method |
US4648396A (en) * | 1985-05-03 | 1987-03-10 | Brigham And Women's Hospital | Respiration detector |
US4686975A (en) * | 1985-05-03 | 1987-08-18 | Applied Membrane Technology, Inc. | Electronic respirable gas delivery device |
US4986269A (en) * | 1985-05-23 | 1991-01-22 | Etela-Hameen Keuhkovammayhdistys R.Y. | Respiration therapy apparatus |
US4648407A (en) * | 1985-07-08 | 1987-03-10 | Respitrace Corporation | Method for detecting and differentiating central and obstructive apneas in newborns |
US4844085A (en) * | 1985-09-13 | 1989-07-04 | Luciano Gattinoni | Pulmonary pressure and volume measurement |
US4686974A (en) * | 1985-10-18 | 1987-08-18 | Tottori University | Breath synchronized gas-insufflation device and method therefor |
US4838275A (en) * | 1985-11-29 | 1989-06-13 | Lee Arnold St J | Home medical surveillance system |
US4747403A (en) * | 1986-01-27 | 1988-05-31 | Advanced Pulmonary Technologies, Inc. | Multi-frequency jet ventilation technique and apparatus |
US4825802A (en) * | 1986-07-24 | 1989-05-02 | Societe Anonyme Drager | Pheumatic alarm for respirator |
US4803471A (en) * | 1986-10-24 | 1989-02-07 | Hudson Oxygen Therapy Sales Co. | Ventilator monitor and alarm apparatus |
US4819629A (en) * | 1986-10-28 | 1989-04-11 | Siemens Aktiengesellschaft | Method and apparatus for delivering aerosol to the airways and/or lungs of a patient |
US5024219A (en) * | 1987-01-12 | 1991-06-18 | Dietz Henry G | Apparatus for inhalation therapy using triggered dose oxygenator employing an optoelectronic inhalation sensor |
US5107830A (en) * | 1987-02-21 | 1992-04-28 | University Of Manitoba | Lung ventilator device |
US4827922A (en) * | 1987-03-05 | 1989-05-09 | L'air Liquide | Process and device for supplying respiratory oxygen |
US4802492A (en) * | 1987-03-11 | 1989-02-07 | National Jewish Center For Immunology And Respiratory Medicine | Method for determining respiratory function |
US4777963A (en) * | 1987-06-18 | 1988-10-18 | Mckenna Kevin | Respiration monitor |
US4837386A (en) * | 1987-06-24 | 1989-06-06 | Air Products And Chemicals, Inc. | Method of treating membranes with ultraviolet radiation |
US5245995A (en) * | 1987-06-26 | 1993-09-21 | Rescare Limited | Device and method for monitoring breathing during sleep, control of CPAP treatment, and preventing of apnea |
US5199424A (en) * | 1987-06-26 | 1993-04-06 | Sullivan Colin E | Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled |
US5322057A (en) * | 1987-07-08 | 1994-06-21 | Vortran Medical Technology, Inc. | Intermittent signal actuated nebulizer synchronized to operate in the exhalation phase, and its method of use |
US4836258A (en) * | 1987-07-10 | 1989-06-06 | Ellis Reginald C L | Attachment apparatus for a tire mat |
US5388571A (en) * | 1987-07-17 | 1995-02-14 | Roberts; Josephine A. | Positive-pressure ventilator system with controlled access for nebulizer component servicing |
US4838257A (en) * | 1987-07-17 | 1989-06-13 | Hatch Guy M | Ventilator |
US4795314A (en) * | 1987-08-24 | 1989-01-03 | Cobe Laboratories, Inc. | Condition responsive pump control utilizing integrated, commanded, and sensed flowrate signals |
US4802485A (en) * | 1987-09-02 | 1989-02-07 | Sentel Technologies, Inc. | Sleep apnea monitor |
US4938212A (en) * | 1987-10-16 | 1990-07-03 | Puritan-Bennett Corporation | Inspiration oxygen saver |
US5129390A (en) * | 1987-12-18 | 1992-07-14 | Institut Nationale De La Sante Et De La Recherche Medicale | Process for regulating an artificial ventilation device and such device |
US4915103A (en) * | 1987-12-23 | 1990-04-10 | N. Visveshwara, M.D., Inc. | Ventilation synchronizer |
US4823788A (en) * | 1988-04-18 | 1989-04-25 | Smith Richard F M | Demand oxygen controller and respiratory monitor |
US4957107A (en) * | 1988-05-10 | 1990-09-18 | Sipin Anatole J | Gas delivery means |
US4928684A (en) * | 1988-05-27 | 1990-05-29 | Salvia-Werk Gesellschaft Zur Herstellung Chemischer And Pharmazeutischer Erzeuginisse Mbh | Apparatus for assisting the spontaneous respiration of a patient |
US5048515A (en) * | 1988-11-15 | 1991-09-17 | Sanso David W | Respiratory gas supply apparatus and method |
US4982738A (en) * | 1988-11-30 | 1991-01-08 | Dr. Madaus Gmbh | Diagnostic apnea monitor system |
US5105354A (en) * | 1989-01-23 | 1992-04-14 | Nippon Kayaku Kabushiki Kaisha | Method and apparatus for correlating respiration and heartbeat variability |
US4938210A (en) * | 1989-04-25 | 1990-07-03 | Trudell Medical | Inhalation chamber in ventilator circuit |
US5134995A (en) * | 1989-05-19 | 1992-08-04 | Puritan-Bennett Corporation | Inspiratory airway pressure system with admittance determining apparatus and method |
US5549106A (en) * | 1989-05-19 | 1996-08-27 | Puritan-Bennett Corporation | Inspiratory airway pressure system using constant pressure and measuring flow signals to determine airway patency |
US5107831A (en) * | 1989-06-19 | 1992-04-28 | Bear Medical Systems, Inc. | Ventilator control system using sensed inspiratory flow rate |
US5239995A (en) * | 1989-09-22 | 1993-08-31 | Respironics, Inc. | Sleep apnea treatment apparatus |
US5433193A (en) * | 1989-09-22 | 1995-07-18 | Respironics Inc. | Breathing gas delivery method and apparatus |
US5313937A (en) * | 1989-09-22 | 1994-05-24 | Respironics Inc. | Leak compensation method and apparatus for a breathing system |
US5231983A (en) * | 1990-01-03 | 1993-08-03 | Minnesota Mining And Manufacturing | Method of and apparatus for the aerosol administration of medication |
US5195528A (en) * | 1990-02-16 | 1993-03-23 | Hok Instrument Ab | Acoustic respiration detector |
US5046491A (en) * | 1990-03-27 | 1991-09-10 | Derrick Steven J | Apparatus and method for respired gas collection and analysis |
US5660171A (en) * | 1990-05-11 | 1997-08-26 | Puritan-Bennett Corporation | System and method for flow triggering of pressure supported ventilation by comparison of inhalation and exhalation flow rates |
US5117819A (en) * | 1990-09-10 | 1992-06-02 | Healthdyne, Inc. | Nasal positive pressure device |
US5099837A (en) * | 1990-09-28 | 1992-03-31 | Russel Sr Larry L | Inhalation-based control of medical gas |
US5400777A (en) * | 1990-10-31 | 1995-03-28 | Siemens Aktiengesellschaft | Ventilator |
US5239994A (en) * | 1991-05-10 | 1993-08-31 | Bunnell Incorporated | Jet ventilator system |
US5203343A (en) * | 1991-06-14 | 1993-04-20 | Board Of Regents, The University Of Texas System | Method and apparatus for controlling sleep disorder breathing |
US5303700A (en) * | 1991-07-04 | 1994-04-19 | Dragerwerk Aktiengesellschaft | Method for detecting the respiratory phases of a patient during an assisted ventilating process |
US5303698A (en) * | 1991-08-27 | 1994-04-19 | The Boc Group, Inc. | Medical ventilator |
US5535739A (en) * | 1992-05-07 | 1996-07-16 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5509414A (en) * | 1994-09-27 | 1996-04-23 | Hok Instrument Ab | Apparatus and method for non-contacting detection of respiration |
US5540219A (en) * | 1995-01-26 | 1996-07-30 | Respironics, Inc. | Sleep apnea treatment apparatus |
Cited By (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20080053442A1 (en) * | 1994-06-03 | 2008-03-06 | Ric Investments, Llc | Method and Apparatus for Providing Positive Airway Pressure to a Patient |
US7810496B2 (en) * | 1994-06-03 | 2010-10-12 | Ric Investments, Llc | Method and apparatus for providing positive airway pressure to a patient |
US20110036352A1 (en) * | 1994-06-03 | 2011-02-17 | Ric Investments, Llc | Method and apparatus for providing positive airway pressure to a patient |
US8640701B2 (en) | 2000-09-28 | 2014-02-04 | Invacare Corporation | Carbon dioxide-based bi-level CPAP control |
US20100065055A1 (en) * | 2003-06-23 | 2010-03-18 | Invacare Corporation | System and method for providing a breathing gas |
US8066004B2 (en) | 2003-06-23 | 2011-11-29 | Invacare Corporation | System and method for providing a breathing gas |
US20080251079A1 (en) * | 2007-04-13 | 2008-10-16 | Invacare Corporation | Apparatus and method for providing positive airway pressure |
US8261742B2 (en) | 2007-08-23 | 2012-09-11 | Invacare Corporation | Method and apparatus for adjusting desired pressure in positive airway pressure devices |
US20110209706A1 (en) * | 2008-10-16 | 2011-09-01 | Koninklijke Philips Electronics N.V. | Ventilator with limp mode |
US8714152B2 (en) * | 2008-10-16 | 2014-05-06 | Koninklijke Philips N.V. | Ventilator with limp mode |
US11844605B2 (en) | 2016-11-10 | 2023-12-19 | The Research Foundation For Suny | System, method and biomarkers for airway obstruction |
Also Published As
Publication number | Publication date |
---|---|
US7004908B2 (en) | 2006-02-28 |
US7141021B2 (en) | 2006-11-28 |
US6770037B2 (en) | 2004-08-03 |
US20050283089A1 (en) | 2005-12-22 |
US20020100477A1 (en) | 2002-08-01 |
US5199424A (en) | 1993-04-06 |
US20020124848A1 (en) | 2002-09-12 |
US5245995A (en) | 1993-09-21 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6770037B2 (en) | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient | |
US6635021B1 (en) | Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient | |
WO1988010108A1 (en) | Device for monitoring breathing during sleep and control of cpap treatment | |
US8297281B2 (en) | Session-by-session adjustment of a device for treating sleep disordered breathing | |
KR101060923B1 (en) | Method and Apparatus for Maintaining and Monitoring Sleep Quality During Therapeutic Treatments | |
JP2010104814A (en) | Method and apparatus for maintaining and monitoring sleep quality during therapeutic treatment | |
US20100095959A1 (en) | Device for ramped control of cpap treatment | |
AU2012216551B2 (en) | Session-By-Session Adjustment of a Device for Treating Sleep Disordered Breathing | |
Netzel | Design of a new controller to treat the obstructive sleep apnea |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |