WO2001024698A1 - Airway treatment apparatus - Google Patents
Airway treatment apparatus Download PDFInfo
- Publication number
- WO2001024698A1 WO2001024698A1 PCT/US2000/023705 US0023705W WO0124698A1 WO 2001024698 A1 WO2001024698 A1 WO 2001024698A1 US 0023705 W US0023705 W US 0023705W WO 0124698 A1 WO0124698 A1 WO 0124698A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- pressure
- patient
- air
- air pressure
- mouthpiece
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H9/00—Pneumatic or hydraulic massage
- A61H9/005—Pneumatic massage
- A61H9/0078—Pneumatic massage with intermittent or alternately inflated bladders or cuffs
-
- 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
- A61M16/0006—Accessories therefor, e.g. sensors, vibrators, negative pressure with means for creating vibrations in patients' airways
-
- 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
- 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
- A61B5/085—Measuring impedance of respiratory organs or lung elasticity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H2205/00—Devices for specific parts of the body
- A61H2205/08—Trunk
Definitions
- the present invention relates to an airway clearance system and in particular to a system that includes a chest compression device for high frequency chest wall oscillation and a subsystem which enhances airflow velocity through the air passages caused by the high frequency chest wall oscillations.
- HFCWO high frequency chest wall oscillation
- the device most widely used to produce HFCWO is the ABI VestTM Airway Clearance System by American Biosystems, the assignee of the present application.
- a description of the pneumatically driven system can be found in the Van Brunt et al. patent, U.S. Patent No. 5,769,797, which is assigned to American Biosystems.
- Another example of a pneumatic chest compression vest has been described by Warwick et al., U.S. Patent No. 4,838,263.
- Airway resistance is the ratio of airway pressure to airway airflow. It is an indicator of the degree of plugging of the lung passages by mucus, and therefore, periodic measurement of airway resistance provides a good indicator of the success or lack thereof of a treatment for lung clearance.
- Prior art vest systems do not have the ability to aid in removing mucus from the upper airway passages. With some disease states, the debilitated patient is unable to produce a cough to remove the mucus accumulated in the upper airway passages. Normally, the current vest systems accelerate the mucus upward and outward in the upper bronchial passages and trachea by increasing airflow velocity. Many individuals can then, by means of a volitional cough, force the mucus into the mouth and then expectorate. The effectiveness of the treatment is greatly reduced if a weakened individual is unable to do this. Also, since a cough is an effective natural method of moving the mucus out of the airway, it would be beneficial to have a system which produced a cough on each oscillation of the chest wall.
- the invention discloses a method and apparatus for clearing a patient's lungs of mucus.
- the method includes applying an oscillating compressive force to the patient's chest that includes a steady state force and an oscillating force component. Air pressure is supplied to the patient's mouth via a mouthpiece. The air pressure is delivered in a timed relationship to the oscillating compressive force to provide increased oscillatory airflow for better lung clearance.
- BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 shows a block diagram of a first embodiment of an airway treatment apparatus which provides enhanced airway flow and chest compression bias line cancellation.
- Figure 2 is a block diagram of a second embodiment of an airway treatment apparatus which includes simulated cough inducement.
- Figure 3 is a schematic block diagram of the cough waveform generator module of Figure 2.
- Figure 4a shows one oscillation of the chest wall force applicator pressure and airflow velocity during a simulated cough sequence.
- Figure 4b shows multiple oscillations of the chest wall force applicator pressure and airflow velocity during simulated cough sequences.
- Figure 5 is a block diagram of a third embodiment of an airway treatment apparatus which provides airway resistance measurement.
- Figure 6 is a schematic block diagram of the airway resistance module of Figure 5.
- Figure 7 is a schematic block diagram of the airway resistance null detector/indicator module of Figure 5.
- Figure 8a is a graph of pressure waves during chest compression treatment from a chest wall force applicator and at a mouthpiece when the pressure at the mouthpiece is less than pressure produced by the chest wall force applicator.
- Figure 8b is a graph of pressure waves during chest compression treatment from the chest wall force applicator and at the mouthpiece when the pressure at the mouthpiece is at null.
- Figure 8c is a graph of pressure waves during chest compression treatment from the chest wall force applicator and at the mouthpiece when pressure at the mouthpiece is greater than pressure produced by the chest wall force applicator.
- Figure 9 is a block diagram of a fourth embodiment of an airway treatment apparatus which includes all of the features of the first, second, and third embodiments.
- FIG 1 is a block diagram showing a patient P undergoing treatment using the preferred embodiment of airway treatment apparatus 10.
- apparatus 10 has two major subsystems, chest wall force applicator 12a (which applies oscillating compressive force to the chest of patient P) and air pressure input mouthpiece system 12b (which supplies air pressure to the patient's mouth in a relationship to the compressive force).
- Chest wall force applicator 12a includes brushless motor 14, vest oscillation frequency potentiometer 16, motor controller 18, shaft 20, wheel 22, reciprocating arm 24, pin 26, diaphragm 28, air chamber 30, blower 32, vest pressure potentiometer 34, blower controller 36, tube 38a with constriction 38b, hoses 40, and inflatable vest 42. Oscillated air pressure is delivered to inflatable vest 42 to cause inflatable vest 42 to apply an oscillating force to the patient's chest.
- Brushless motor 14 is operated by motor controller 18 at a speed which is set by vest oscillation frequency potentiometer 16.
- Shaft 20 is connected to brushless motor 14 and wheel 22.
- Reciprocating arm 24 is coupled to wheel 22 by pin 26, which is offset from the center of wheel 22.
- Reciprocating arm 24 is also coupled to diaphragm 28, which is part of air chamber 30.
- Blower 32 is operated by blower controller 36 based upon a control setting of potentiometer 34.
- Tube 38a with constriction 38b couples blower 32 with air chamber 30.
- Hoses 40 in turn, couple air chamber 30 with inflatable vest 42.
- the force generated on the patient's chest by chest wall force applicator 12a has an oscillatory air pressure component and a steady state air pressure component.
- the steady state air pressure (or "bias line pressure") is greater than atmospheric pressure, and the oscillatory air pressure rides on the steady state air pressure.
- the oscillatory air pressure component is created by brushless motor 14.
- the speed of brushless motor 14 is selected by vest oscillation potentiometer 16 and held constant by motor controller 18.
- Shaft 20 of brushless motor 14 rotates wheel 22 which, in turn, moves reciprocating arm 24 in a linear fashion and causes diaphragm 28 to oscillate the air in air chamber 30 at a frequency selected by vest oscillation potentiometer 16.
- the pressure created by brushless motor 14 follows a sinusoidal waveform pattern.
- vest pressure potentiometer 34 selects the speed of blower 32 and the speed is held constant by blower controller 36.
- the steady state air pressure is transferred to air chamber 30 through tube 38a.
- Constriction 38b within tube 38a prevents backflow of pressure pulses into blower 32 which would affect the pressure pulsation in a nonlinear manner.
- constriction 38b is a large impedance to oscillatory airflow but a low impedance to steady state airflow.
- the steady state air pressure created by blower 32 is greater than atmospheric pressure so that a whole oscillatory cycle is effective at moving the patient's chest.
- blower 32 has a pressure maximum of 12cm of water, which is well within tolerance limits of anticipated users. This is a safety feature designed so that if any component failure tended to speed up blower 32, it would not be unsafe.
- Hoses 40 convey air pressure waves from air chamber 30 to inflatable vest 42.
- Inflatable vest 42 thus, is cyclically inflated and deflated to apply HFCWO to the patient's chest at a frequency set by vest oscillation frequency potentiometer 16 about a steady state or bias line pressure set by vest pressure potentiometer 34.
- the steady state air pressure determines the intensity of the chest compressions since the oscillatory air pressure rides on the steady state air pressure. Therefore, the change of pressure (delta pressure) increases with increasing steady state pressure and results in the oscillatory air pressure never being less than atmospheric pressure.
- the patient's airways are cleared of mucus.
- Chest wall force applicator 12a also includes components to link it to air pressure input mouthpiece system 12b. These include vest sampling tube 50, vest pressure transducer (VPT) 52, phase shift network 54, line 56, line 58, and Oscillatory Positive Expiratory Pressure (OPEP) oscillation intensity potentiometer 60.
- VPT vest pressure transducer
- OPEP Oscillatory Positive Expiratory Pressure
- Vest sampling tube 50 is connected to inflatable vest 42 at one end and vest pressure transducer 52 at the other end.
- Vest pressure transducer 52 is connected to phase shift network 54 via line 56.
- Line 58 then connects phase shift network 54 to OPEP potentiometer 60.
- vest sampling tube 50 conveys vest pressure to vest pressure transducer 52 which converts it to an electrical signal representative of sensed vest pressure.
- the electrical output signal of vest pressure transducer 52 is sent to phase shift network 54 via line 56.
- Phase shift network 54 compensates for delays in oscillatory pressure from chest wall force applicator 12a being transmitted as an oscillation within the patient's lungs and to the patient's mouth.
- the signal from phase shift network 54 (having a waveform representative of vest pressure applied by chest wall force applicator 12a) is supplied by line 58 to OPEP potentiometer 60 and then to air pressure input mouthpiece system 12b.
- Air pressure input mouthpiece system 12b includes motor drive amplifier 72, line 74, summing junction 76, line 78, diaphragm 80, linear motor 82, air chamber 84, sampling tube 86, pressure transducer (PT) 88, line 90, low pass filter (LPF) 92, comparator error amplifier 94, line 96, line 98, Positive Expiratory Pressure (PEP) level potentiometer 100, line 102, blower controller motor driver 104, blower 106, tube 108a with constriction 108b, tube 110, and mouthpiece 112 (with mouth port 112a, air supply port 112b, and outlet port 114).
- PEP Positive Expiratory Pressure
- Wiper 60a of OPEP potentiometer 60 is connected to motor drive amplifier 72 via line 74, summing junction 76, and line 78.
- Motor drive amplifier 72 is connected to diaphragm 80 of linear motor 82.
- Diaphragm 80 is then connected with air chamber 84 which is coupled to sampling tube 86 followed by pressure transducer 88.
- Line 90 connects pressure transducer 88 to low pass filter 92 which is followed by a connection to summing junction 76 and to comparator error amplifier 94 via lines 96 and 98.
- Comparator error amplifier 94 is also connected to PEP level potentiometer 100 through line 102 and to blower controller motor driver 104.
- Blower controller motor driver 104 provides a drive signal to blower 106, which is coupled to air chamber 84 by tube 108a that contains constriction 108b.
- Tube 110 extends from air chamber 84 and connects to air supply port 112b of mouthpiece 112.
- Mouth port 112a of mouthpiece 112 is placed in communication with the patient's mouth (i.e. either in or over the mouth). Mouthpiece 112 may also cover the patient's nose.
- Outlet port 114 is located a short distance from mouthpiece 112 on tube 110.
- the processed pressure waveform from vest pressure transducer 52 and phase shift network 54 is input to OPEP potentiometer 60 as described above.
- OPEP potentiometer 60 adjusts an Oscillatory Positive Expiratory Pressure (OPEP) intensity level to control the amount of airflow enhancement at the patient's mouth that is input to motor drive amplifier 72.
- motor drive amplifier 72 Based upon a control signal from summing junction 76, motor drive amplifier 72 operates linear motor 82 causing diaphragm 80 of linear motor 82 to oscillate air within air chamber 84.
- the control signal is based upon the PEP feedback signal from low pass filter 92 (which represents the steady state pressure in chamber 84) and the signal waveform from phase shift network 54 through OPEP potentiometer 60.
- the oscillatory waveform created in air chamber 84 is selected with the desired phase, intensity, and wave shape to perform the needed task.
- Linear motor 82 is not restricted to a sinusoidal waveform and can move in any complex pattern. Other embodiments of the invention may use other components to produce the same waveforms as linear motor 82 such as a solenoid or a motor driven cam mechanism.
- Air pressure from air chamber 84 is measured by sampling tube 86 and pressure transducer 88 relative to atmospheric pressure.
- the electrical signal generated by pressure transducer 88 is filtered by low pass filter 92, which has such a low frequency cutoff that the output from low pass filter 92 is essentially the average pressure in air chamber 84 produced by filtering out the effects of linear motor 82 and then carried on line 96.
- This PEP feedback signal is carried to the minus (-) input of comparator error amplifier 94 by line 98.
- PEP level potentiometer 100 selects a Positive Expiratory Pressure (PEP) level which is fed into the plus (+) input of comparator error amplifier 94 via line 102.
- PEP Positive Expiratory Pressure
- the PEP level is adjusted by PEP level potentiometer 100 to match the mean pressure exerted on the patient's chest wall by chest wall force applicator 12a.
- the output of comparator error amplifier 94 activates blower controller motor driver 104 which maintains the speed of blower 106. Since blower 106 communicates with air chamber 84 through tube 108a, the steady state pressure bias is regulated within air chamber 84. Constriction 108b, within tube 108a, prevents back flow of pressure pulses to blower 106 which would effect the pressure pulsation as previously discussed.
- the steady state pressure bias is maintained in the patient's mouth through communication with air chamber 84 via tube 110 and mouthpiece 112. Air pressure input mouthpiece system 12b accomplishes, in effect, a shift in the effective atmospheric pressure.
- An oscillatory airflow is produced that rides on a steady state pressure (which is greater than atmospheric pressure) in the mouth.
- the combined oscillatory pressure and steady state pressure has a waveform, intensity, and phase relationship to the chest compressions that enhances airflow through the air passages.
- the patient perceives no vest pressure, because the steady state pressure in the mouth and lungs is equal to and opposite the pressure from chest wall force applicator 12a, and thus, the forces counteract each other. This is very beneficial with some disease states where the external pressure on the chest from a chest wall force applicator 12a can cause considerable distress to the patient.
- a patient may already have difficulty breathing and would have even greater difficultly if the patient had to breathe against a force trying to compress the patient's lungs.
- Air pressure input mouthpiece system 12b also provides an effective means of enhancing oscillations caused by chest wall force applicator 12a without increasing the force applied on the patient's chest. Increased force on the patient's chest would be too uncomfortable. Therefore, air pressure input mouthpiece system 12b enhances the function of chest wall force applicator 12a by oscillating the pressure at the patient's mouth in synchronism with the airflow produced by the oscillations on the chest by chest wall force applicator 12a.
- OPEP potentiometer 60 regulates the extent to which air pressure input mouthpiece system 12b enhances airflow velocity created by chest wall force applicator 12a, it can alternatively be set to (a) increase the volume of the lungs slightly by increasing the pressure in air chamber 84 or (b) deflate the lungs by decreasing the pressure in air chamber 84. This is a beneficial function, because in some disease states the lungs need to be given greater volume. In other disease states where the lungs may be hyperinflated, it is desirable to reduce the lungs' volume.
- Outlet port 114 is located a short distance from mouthpiece 112. The distance is determined by the distance 100% humidified air from mouthpiece 112 travels in one cycle. This allows the humid air from the outflow half cycles to be returned to the patient's airways during the inflow half cycles, thus preventing the airways from drying out.
- the positive pressure produced by blower 106 maintains a net average of airflow from blower 106 through air chamber 84 and tube 110 and out outlet port 114. Therefore, any fluids and mucus are drained out through outlet port 114 and not passed into air chamber 84 where they could cause damage.
- this airflow stream provides a continuous supply of fresh air for normal respiration as the much larger tidal breathing volume oscillations move fresh air from the position of outlet port 114 in tube 110 into the patient's lungs.
- Figure 2 shows a second embodiment of apparatus 10, having a simulated cough inducer 12c, which includes cough waveform generator module 160 and light interrupter 164.
- the embodiment shown in Figure 2 is generally similar to the embodiment of Figure 1 , and similar reference characters are used to designate similar elements.
- Figure 3 shows a schematic block diagram of cough waveform generator module 160, which includes optical sensor processor 166, cough waveform generator 168, line 170, cough intensity potentiometer 172, line 174, and summing junction 176.
- Light interrupter 164 ( Figure 2) is attached to wheel 22 and sends signals to optical sensor processor 166. These components make up a diaphragm position sensor which is connected to cough waveform generator 168 via line 170. The output of cough waveform generator 168 is connected to Cough Intensity potentiometer 172. Line 174 connects Cough Intensity potentiometer 172 with one input of summing junction 176. Another input of summing junction 176 is connected to wiper 60a of OPEP potentiometer 60. Line 74 connects the output of summing junction 176 with an input of summing junction 76. The output of summing junction 76 is connected to motor drive amplifier 72 through line 78.
- the diaphragm position sensor formed by light interrupter 164 and optical sensor processor 166 produces a timing signal that triggers the start and finish of cough waveform generator 168.
- optical sensor processor 166 activates cough waveform generator 168.
- Optical sensor processor 166 stops cough waveform generator 168 when oscillatory lung pressure reaches zero (as indicated by the position of light interrupter 164).
- Cough Intensity potentiometer 172 determines the magnitude of the signal from cough waveform generator 168, and the signal is carried to summing junction 176 via line 174.
- OPEP potentiometer 60 sets the level of the OPEP waveform, and this signal is also supplied to summing junction 176.
- Summing junction 176 then combines the OPEP waveform signal with the cough waveform signal from cough waveform generator 168.
- the output of summing junction 176 which includes the cough waveform set at the desired intensity, is carried through line 74 to summing junction 76.
- the combined OPEP/cough signal is summed with the steady state pressure signal from low pass filter 92 and is sent to motor drive amplifier 72 along line 78.
- the pressure wave from air chamber 84 causes near zero airflow out of mouthpiece 112.
- pressure from chest wall force applicator 12a on the chest is increasing. What results is a build up of airway pressure in the lungs with very little outward flow.
- the flow rate while inspiring is lower than the flow rate while expiring, but the volume of air during each half cycle is equal. Since this is the pattern of a natural cough, a cough is simulated with each oscillatory cycle, which can be up to 20 times/second.
- simulated cough inducer 12c can be utilized instead of enhancing the increased airflow velocities created by chest wall force applicator 12a using sinusoidal enhancement with air pressure input mouthpiece system 12b.
- OPEP potentiometer 60 which adjusts the magnitude of sinusoidal enhancement
- Cough Intensity potentiometer 172 which controls the magnitude of the cough waveform
- Figures 4a and 4b illustrate the cough sequence.
- Figures 4a and 4b show pressure from chest wall force applicator 12a on the patient's chest and airflow from the patient's mouth during a cough sequence.
- Figure 4a shows one oscillatory cycle and
- Figure 4b shows multiple oscillatory cycles.
- the sinusoidal wave is a vest pressure waveform 180 and the jagged waveform 182 is airflow at the patient's mouth.
- the high frequency oscillations of the airflow waveform are caused by resonance of the tubes within the present invention and the patient's air passages and are of no consequence.
- Line 184 indicates zero airflow.
- the patient is inspiring and when below the line, the patient is expiring.
- Vest pressure increases downward from line 186.
- airflow Prior to about point 188, airflow is about zero. This is the period of building pressure in the lungs and is equivalent to the glottis closing during a natural cough in order to allow pressure to build in the lungs.
- vest pressure peaks, and airflow from the mouth is at a maximum. This coincides with the rapid increase in airflow out of the mouth when the glottis opens during a natural cough. Expiratory rate is up to 3 liters/second.
- Point 190 shows a gradual inspiration, as in a natural cough. Integration of the airflow waveform 182 below and above line 184 produces a net flow of zero.
- Figure 4b shows the cough sequence at a different time scale illustrating multiple induced coughs.
- FIG. 5 shows a third embodiment of apparatus 10 which further includes airway resistance indicator 12d.
- the embodiment shown in Figure 5 is generally similar to the embodiment shown in Figure 1 , and similar reference characters are used to designate similar elements.
- Airway resistance indicator 12d includes airway resistance module 200 (shown in Figure 6), airway resistance null detector/indicator module 210 (shown in Figure 7) and test switch 220 (having terminals 220a-220c).
- Airway resistance module 200 ( Figure 6) includes vest pressure transducer 52, phase shift network 54, lines 56 and 58, and PFT potentiometer 230, and lines 232 and 234.
- Vest pressure transducer 52 is linked to inflatable vest 42 by vest sampling tube 50.
- Phase shift network 54 is coupled to vest pressure transducer 52 via line 56.
- Line 58 connects phase shift network 54 with PFT potentiometer 230, which is connected to terminal 220a of test switch 220 by line 232.
- Line 234 couples the output of vest pressure transducer 52 with airway resistance null detector/indicator 210.
- Airway resistance null detector/indicator module 210 ( Figure 7) includes pressure tube 240, pressure transducer 242, line 244, capacitor 246, double pole switch 248, line 250, phase shift network 252, line 254, integrator 256 with integrator capacitor 258, level indicator 260, and LEDs 262 and 264.
- Pressure tube 240 is coupled to mouthpiece 112 and pressure transducer 242. Through line 244, the output of pressure transducer 242 is connected to capacitor 246 which is connected to double pole switch 248 via line 250.
- Double pole switch 248 has one output terminal connected to integrator 256 with integrator capacitor 258, and the other output terminal connected to ground.
- level indicator 260 The input of level indicator 260 is connected to integrator 256, and the output of level indicator 260 is connected with and selectively drives LEDs 262 and 264. Signals from airway resistance module 200 are carried to phase shift network 252 which is connected to the control input of double pole switch 248 via line 254.
- vest sampling tube 50 conveys vest pressure to vest pressure transducer 52 ( Figure 6) which converts it to an electrical signal.
- the electrical output signal of vest pressure transducer 52 is sent to phase shift network 54 via line 56.
- Phase shift network 54 compensates for delays in oscillatory pressure from chest wall force applicator 12a being transmitted as an oscillation within the patient's lungs and to the patient's mouth.
- the signal from phase shift network 54 (having a waveform representative of vest pressure applied by chest wall force applicator 12a) is subsequently carried by line 58 to PFT potentiometer 230 (as well as to OPEP potentiometer 60).
- pressure tube 240 samples the pressure in the patient's mouth.
- Transducer 242 ( Figure 7) converts this pressure to an electrical signal.
- the output of transducer 242 is carried to capacitor 246 via line 244.
- Line 250 then carries the signal from capacitor 250 to the input of double pole switch 248.
- Capacitor 246 removes the dc signal component from the electrical output signal of pressure transducer 242.
- a vest pressure signal is a control input into double pole switch 248.
- Line 234 inputs the vest pressure signal from vest pressure transducer 52 ( Figure 6) to phase shift network 252, which controls the switch timing of double pole switch 248.
- the signal from phase shift network 252 is carried to double pole switch 248 through line 254 and switches to ground to discharge any accumulated charge on capacitor 246, which prevents a dc voltage build up.
- double pole switch 248 connects capacitor 246 to the input of integrator 256 to sample the mouth pressure waveform fed through capacitor 246. If the average signal output of integrator 256 indicates that the oscillatory pressure in mouthpiece 112 is less than the lung oscillatory pressure, level indicator 260 lights LED 262.
- level indicator 260 lights LED 264.
- airway resistance may be checked to determine the progress of lung clearance. To accomplish this, test switch 220 is pressed so that it connects terminal 220a to terminal 220c (see Figure 5). At this point PFT potentiometer 230 of airway resistance module 200 provides an input to motor drive amplifier 72 (through test switch 220 and summing junction 76) and controls air pressure input mouthpiece system 12b. PFT potentiometer 230 is adjusted until both LED's 262 and 264 are not lit.
- This is the null point of pressure within the mouth-the oscillatory air pressure waves induced by chest wall force applicator 12a are equal and opposite to the oscillatory pressure waves provided at mouthpiece 112 by air pressure input mouthpiece system 12b.
- the airflow and air pressure in mouthpiece 112 are at a magnitude equal to that flow caused by the oscillation pressure of chest wall force applicator 12a on the patient's chest, which is transferred to the patient's lungs and is then suppressed by the resistance of the mucus in the airways as the air flows through them on the way to the patient's mouth.
- the indicator knob position of PFT potentiometer 230 provides a numerical reading of the airway resistance of the patient's lungs.
- Figures 8a, 8b, and 8c graph pressure waves from chest wall force applicator 12a (vest pressure 300) and the patient's mouth through mouthpiece 112 (mouth pressure 310) versus time.
- Figure 8a is an illustration of the force from chest wall force applicator 12a at a greater pressure than the pressure at the patient's mouth created by air pressure input mouthpiece system 12b. This is the situation where LED 262 of airway resistance module 210 would light.
- the upper waveform 300 is the oscillatory pressure of chest wall force applicator 12a.
- the lower waveform 310 is the oscillatory pressure at the patient's mouth which is the sum of the oscillations from the lungs plus oscillations from the air chamber 84 traveling down tube 110.
- Figure 8b is an illustration of waveforms during the null point of pressure. Neither LED (262, 264) would light during this period.
- the upper waveform 300 is the oscillatory pressure from chest wall force applicator 12a
- the lower waveform 310 is the pressure at the patient's mouth through mouthpiece 112.
- PFT potentiometer 230 while defining the flow rate from the patient's mouth, is an analog of the airway resistance at the null point of pressure.
- FIG. 8c is an illustration of waveforms 300 and 310 when the pressure in mouthpiece 112 measured from tube 110 is greater than the oscillatory pressure produced by chest wall force applicator 12a. LED 264 lights in this situation.
- the wave shape of waveform 310 is the result of the combining of two pressure waves having unequal magnitude and phase. The oscillations on the patient's chest become out of phase by 180° compared to airflow oscillations at the patient's mouth.
- null point of pressure is chosen, so no calibration sequence is required of system components.
- Another advantage is that it does not require any breathing maneuvers on the part of the patient. Repeatable adherence to a maneuver is necessary for standard pulmonary function testing, therefore, tests relying on breathing maneuvers may be inaccurate, or the data may not be usable.
- Figure 9 shows a fourth embodiment of apparatus 10 which includes all of the features of the first, second and third embodiments.
- each of the systems work together to efficiently remove mucus from the patient's lungs and provide a means of determining the progress of the treatment. At the same time, patient comfort is maintained during treatment.
- Airway treatment apparatus 10 performs in such a way that the patient receiving treatment perceives no external pressure on the chest which may cause discomfort depending on the disease state of the patient. Increased oscillatory airflow velocities can be achieved over prior art vest systems, which is the key to successful lung clearance. By incorporating a mechanism to simulate a cough, outcome measuring airway treatment apparatus 10 provides better lung clearance over other vest systems and induces individuals that are not able to voluntarily cough to simulate coughs.
- the present invention has been described with reference to preferred embodiments, workers skilled in the art will recognize that changes may be made in form and detail without departing from the spirit and scope of the invention. For example, although the control systems shown in the figures use analog circuitry, other embodiments use digital logic and programmable devices (such as programmable logic arrays, microcontrollers, or microprocessors) to provide the control functions.
Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP00959562A EP1225834A4 (en) | 1999-10-04 | 2000-08-29 | Airway treatment apparatus |
AU70859/00A AU7085900A (en) | 1999-10-04 | 2000-08-29 | Airway treatment apparatus |
JP2001527700A JP2004500905A (en) | 1999-10-04 | 2000-08-29 | Airflow treatment device |
Applications Claiming Priority (8)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/412,459 US6910479B1 (en) | 1999-10-04 | 1999-10-04 | Airway treatment apparatus with bias line cancellation |
US09/412,768 US6340025B1 (en) | 1999-10-04 | 1999-10-04 | Airway treatment apparatus with airflow enhancement |
US09/412,086 | 1999-10-04 | ||
US09/412,086 US6210345B1 (en) | 1999-10-04 | 1999-10-04 | Outcome measuring airway resistance diagnostic system |
US09/412,457 | 1999-10-04 | ||
US09/412,768 | 1999-10-04 | ||
US09/412,457 US6415791B1 (en) | 1999-10-04 | 1999-10-04 | Airway treatment apparatus with cough inducement |
US09/412,459 | 1999-10-04 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2001024698A1 true WO2001024698A1 (en) | 2001-04-12 |
Family
ID=27503604
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2000/023705 WO2001024698A1 (en) | 1999-10-04 | 2000-08-29 | Airway treatment apparatus |
Country Status (5)
Country | Link |
---|---|
US (4) | US6910479B1 (en) |
EP (1) | EP1225834A4 (en) |
JP (1) | JP2004500905A (en) |
AU (1) | AU7085900A (en) |
WO (1) | WO2001024698A1 (en) |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7416536B2 (en) | 2002-10-02 | 2008-08-26 | Devlieger Marten Jan | Chest vibrating device |
US7425203B2 (en) * | 2002-11-15 | 2008-09-16 | Hill-Rom Services, Inc. | Oscillatory chest wall compression device with improved air pulse generator with improved user interface |
CN103989575A (en) * | 2014-06-09 | 2014-08-20 | 河北爱西欧医疗设备科技有限公司 | Multi-cavity cam sputum excretion system |
US9572743B2 (en) | 2006-12-13 | 2017-02-21 | Hill-Rom Services Pte Ltd. | High frequency chest wall oscillation system having valve controlled pulses |
US10518048B2 (en) | 2015-07-31 | 2019-12-31 | Hill-Rom Services, PTE Ltd. | Coordinated control of HFCWO and cough assist devices |
Families Citing this family (113)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
AU8697998A (en) * | 1997-08-08 | 1999-03-01 | Hill-Rom, Inc. | Proning bed |
WO2000000152A1 (en) * | 1998-06-26 | 2000-01-06 | Hill-Rom, Inc. | Proning bed |
US6701553B1 (en) * | 1999-04-21 | 2004-03-09 | Hill-Rom Services, Inc. | Proning bed |
US7597670B2 (en) * | 1999-07-02 | 2009-10-06 | Warwick Warren J | Chest compression apparatus |
US7762967B2 (en) * | 1999-07-02 | 2010-07-27 | Respiratory Technologies, Inc. | Chest compression apparatus |
US6916298B2 (en) * | 1999-08-31 | 2005-07-12 | Advanced Respiratory, Inc. | Pneumatic chest compression vest with front panel air bladder |
US20040158177A1 (en) * | 1999-08-31 | 2004-08-12 | Van Brunt Nicholas P. | Pneumatic chest compression vest with front panel bib |
US6910479B1 (en) * | 1999-10-04 | 2005-06-28 | Advanced Respiratory, Inc. | Airway treatment apparatus with bias line cancellation |
US6557554B1 (en) * | 1999-10-29 | 2003-05-06 | Suzuki Motor Corporation | High-frequency oscillation artificial respiration apparatus |
US7059324B2 (en) * | 1999-11-24 | 2006-06-13 | Smiths Medical Asd, Inc. | Positive expiratory pressure device with bypass |
JP3721912B2 (en) * | 2000-01-11 | 2005-11-30 | スズキ株式会社 | High frequency ventilator |
US8257288B2 (en) | 2000-06-29 | 2012-09-04 | Respirtech | Chest compression apparatus having physiological sensor accessory |
CA2415694A1 (en) * | 2000-07-14 | 2002-01-24 | John P. Biondo | Pulmonary therapy apparatus |
US6539938B2 (en) * | 2000-12-15 | 2003-04-01 | Dhd Healthcare Corporation | Maximum expiratory pressure device |
US6666209B2 (en) * | 2001-02-20 | 2003-12-23 | 3M Innovative Properties Company | Method and system of calibrating air flow in a respirator system |
US7876294B2 (en) * | 2002-03-05 | 2011-01-25 | Nec Corporation | Image display and its control method |
EP1343112A1 (en) * | 2002-03-08 | 2003-09-10 | EndoArt S.A. | Implantable device |
ITMI20021273A1 (en) * | 2002-06-11 | 2003-12-11 | Milano Politecnico | SYSTEM AND METHOD FOR THE AUTOMATIC DETECTION OF THE EXPIRATORY FLOW LIMITATION |
US7338433B2 (en) | 2002-08-13 | 2008-03-04 | Allergan, Inc. | Remotely adjustable gastric banding method |
EP2181655B1 (en) * | 2002-08-28 | 2016-12-07 | Apollo Endosurgery, Inc. | Fatigue-restistant gastric banding device |
US20050183722A1 (en) * | 2002-09-27 | 2005-08-25 | Jagadish Bilgi | External chest therapy blanket for infants |
US20040064076A1 (en) * | 2002-09-27 | 2004-04-01 | Jagadish Bilgi | External chest therapy blanket for infants |
WO2004037346A1 (en) * | 2002-10-28 | 2004-05-06 | John Perrier | Ultrasonic medical device |
GB0318935D0 (en) * | 2003-08-13 | 2003-09-17 | Mossanen Shams Iden | Pulmonary evaluation device |
US7316658B2 (en) * | 2003-09-08 | 2008-01-08 | Hill-Rom Services, Inc. | Single patient use vest |
US20050126578A1 (en) * | 2003-12-12 | 2005-06-16 | Garrison Richard L. | External pressure garment in combination with a complementary positive pressure ventilator for pulmocardiac assistance |
EP1706044B1 (en) | 2004-01-23 | 2011-10-05 | Allergan, Inc. | Releasably-securable one-piece adjustable gastric band |
US7811299B2 (en) * | 2004-03-08 | 2010-10-12 | Allergan, Inc. | Closure system for tubular organs |
WO2005094257A2 (en) * | 2004-03-18 | 2005-10-13 | Inamed Medical Products Corporation | Apparatus and method for volume adjustment of intragastric balloons |
US20060011195A1 (en) * | 2004-07-14 | 2006-01-19 | Ric Investments, Llc. | Method and apparatus for non-rebreathing positive airway pressure ventilation |
US7195014B2 (en) * | 2005-03-22 | 2007-03-27 | Hoffman Laboratories, Llc | Portable continuous positive airway pressure system |
US8251888B2 (en) | 2005-04-13 | 2012-08-28 | Mitchell Steven Roslin | Artificial gastric valve |
US7785280B2 (en) | 2005-10-14 | 2010-08-31 | Hill-Rom Services, Inc. | Variable stroke air pulse generator |
US7798954B2 (en) | 2006-01-04 | 2010-09-21 | Allergan, Inc. | Hydraulic gastric band with collapsible reservoir |
US8043206B2 (en) | 2006-01-04 | 2011-10-25 | Allergan, Inc. | Self-regulating gastric band with pressure data processing |
US20070163600A1 (en) * | 2006-01-11 | 2007-07-19 | Leslie Hoffman | User interface and head gear for a continuous positive airway pressure device |
US7861716B2 (en) | 2006-03-15 | 2011-01-04 | Carefusion 207, Inc. | Closed loop control system for a high frequency oscillation ventilator |
EP2007461A4 (en) * | 2006-03-15 | 2014-10-22 | Hill Rom Services Pte Ltd | High frequency chest wall oscillation system |
US8460223B2 (en) | 2006-03-15 | 2013-06-11 | Hill-Rom Services Pte. Ltd. | High frequency chest wall oscillation system |
WO2008051285A2 (en) * | 2006-04-01 | 2008-05-02 | Medical Service Consultation International, Llc | Methods and compositions for detecting fungi and mycotoxins |
US7909033B2 (en) | 2006-05-03 | 2011-03-22 | Comedica Incorporated | Breathing treatment apparatus |
US8052626B2 (en) * | 2006-05-10 | 2011-11-08 | Hill-Rom Services Pte. Ltd. | Data handling for high frequency chest wall oscillation system |
US7594508B2 (en) * | 2006-07-13 | 2009-09-29 | Ric Investments, Llc. | Ventilation system employing synchronized delivery of positive and negative pressure ventilation |
US8051854B2 (en) * | 2006-09-15 | 2011-11-08 | Comedica Incorporated | Continuous high-frequency oscillation breathing treatment apparatus |
US7779841B2 (en) * | 2006-11-13 | 2010-08-24 | Carefusion 2200, Inc. | Respiratory therapy device and method |
US20080300515A1 (en) * | 2006-12-28 | 2008-12-04 | Mario Nozzarella | Focused Chest Compression System and Method of Using Same |
JP5390504B2 (en) * | 2007-04-02 | 2014-01-15 | アレジアンス、コーポレイション | Respiratory therapy device using high frequency vibration |
US8714153B2 (en) * | 2007-04-16 | 2014-05-06 | Ric Investments, Llc | Method for selecting a device adapted to treat disordered breathing |
US8192381B2 (en) * | 2007-04-19 | 2012-06-05 | RespirTech Technologies, Inc. | Air vest for chest compression apparatus |
US9050434B2 (en) * | 2007-05-18 | 2015-06-09 | Comedica Incorporated | Lung therapy device |
US8108957B2 (en) | 2007-05-31 | 2012-02-07 | Hill-Rom Services, Inc. | Pulmonary mattress |
GB0712710D0 (en) * | 2007-06-29 | 2007-08-08 | Laerdal Medical As | Method and instrument to provide ventilation and perfusion |
EP2217311B1 (en) | 2007-11-19 | 2017-10-18 | Vyaire Medical Consumables LLC | Patient interface assembly for respiratory therapy |
US8251876B2 (en) | 2008-04-22 | 2012-08-28 | Hill-Rom Services, Inc. | Breathing exercise apparatus |
US8539951B1 (en) | 2008-05-27 | 2013-09-24 | Trudell Medical International | Oscillating positive respiratory pressure device |
US20100075322A1 (en) * | 2008-08-22 | 2010-03-25 | Hooper Dennis G | Methods and Compositions for Identifying Mycotoxins and Fungal Species |
US20100068718A1 (en) | 2008-08-22 | 2010-03-18 | Hooper Dennis G | Methods and Compositions for Identifying Yeast |
WO2010042493A1 (en) | 2008-10-06 | 2010-04-15 | Allergan, Inc. | Mechanical gastric band with cushions |
US20100185049A1 (en) | 2008-10-22 | 2010-07-22 | Allergan, Inc. | Dome and screw valves for remotely adjustable gastric banding systems |
US8327849B2 (en) | 2008-10-28 | 2012-12-11 | Trudell Medical International | Oscillating positive expiratory pressure device |
US8485179B1 (en) | 2009-02-23 | 2013-07-16 | Trudell Medical International | Oscillating positive expiratory pressure device |
US9149589B2 (en) | 2009-02-23 | 2015-10-06 | Trudell Medical International | Method and device for performing orientation dependent oscillating positive expiratory pressure therapy |
BR112012001413B1 (en) | 2009-07-24 | 2021-05-18 | Koninklijke Philips N.V. | device to help cough |
US20110137112A1 (en) * | 2009-08-28 | 2011-06-09 | Allergan, Inc. | Gastric band with electric stimulation |
WO2011031400A2 (en) * | 2009-08-28 | 2011-03-17 | Allergan, Inc. | Gastric band with electric stimulation |
US8962251B2 (en) * | 2009-10-08 | 2015-02-24 | Medical Service Consultation International, Llc | Methods and compositions for identifying sulfur and iron modifying bacteria |
EP2311429B1 (en) * | 2009-10-14 | 2015-03-25 | Hill-Rom Services, Inc. | Three-dimensional layer for a garment of a HFCWO system |
US20110100360A1 (en) * | 2009-11-02 | 2011-05-05 | Joseph Dee Faram | Composite lung therapy device and method |
US9151425B2 (en) * | 2009-11-02 | 2015-10-06 | Comedica Incorporated | Multiple conduit connector apparatus and method |
WO2011058470A1 (en) * | 2009-11-13 | 2011-05-19 | Koninklijke Philips Electronics N.V. | Method and device for airway clearance |
US8758221B2 (en) * | 2010-02-24 | 2014-06-24 | Apollo Endosurgery, Inc. | Source reservoir with potential energy for remotely adjustable gastric banding system |
US8840541B2 (en) | 2010-02-25 | 2014-09-23 | Apollo Endosurgery, Inc. | Pressure sensing gastric banding system |
US9028394B2 (en) | 2010-04-29 | 2015-05-12 | Apollo Endosurgery, Inc. | Self-adjusting mechanical gastric band |
US9044298B2 (en) | 2010-04-29 | 2015-06-02 | Apollo Endosurgery, Inc. | Self-adjusting gastric band |
US20110270024A1 (en) | 2010-04-29 | 2011-11-03 | Allergan, Inc. | Self-adjusting gastric band having various compliant components |
US20110270025A1 (en) | 2010-04-30 | 2011-11-03 | Allergan, Inc. | Remotely powered remotely adjustable gastric band system |
US8517915B2 (en) | 2010-06-10 | 2013-08-27 | Allergan, Inc. | Remotely adjustable gastric banding system |
US20120059216A1 (en) | 2010-09-07 | 2012-03-08 | Allergan, Inc. | Remotely adjustable gastric banding system |
US8961393B2 (en) | 2010-11-15 | 2015-02-24 | Apollo Endosurgery, Inc. | Gastric band devices and drive systems |
US8676529B2 (en) | 2011-01-31 | 2014-03-18 | Covidien Lp | Systems and methods for simulation and software testing |
US8788236B2 (en) | 2011-01-31 | 2014-07-22 | Covidien Lp | Systems and methods for medical device testing |
JP6038903B2 (en) | 2011-06-06 | 2016-12-07 | トルーデル メディカル インターナショナル | Positive expiratory pressure vibration device |
JP6058676B2 (en) * | 2011-09-21 | 2017-01-11 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Upper airway resistance measuring device |
US8876694B2 (en) | 2011-12-07 | 2014-11-04 | Apollo Endosurgery, Inc. | Tube connector with a guiding tip |
US8961394B2 (en) | 2011-12-20 | 2015-02-24 | Apollo Endosurgery, Inc. | Self-sealing fluid joint for use with a gastric band |
CN104114217B (en) * | 2012-02-08 | 2017-07-18 | 皇家飞利浦有限公司 | Method and apparatus for increasing cough flow |
US9180271B2 (en) | 2012-03-05 | 2015-11-10 | Hill-Rom Services Pte. Ltd. | Respiratory therapy device having standard and oscillatory PEP with nebulizer |
US9517315B2 (en) | 2012-11-30 | 2016-12-13 | Trudell Medical International | Oscillating positive expiratory pressure device |
US9795752B2 (en) | 2012-12-03 | 2017-10-24 | Mhs Care-Innovation, Llc | Combination respiratory therapy device, system, and method |
WO2014097047A1 (en) * | 2012-12-19 | 2014-06-26 | Koninklijke Philips N.V. | Detection of respiratory disorders |
US8956821B2 (en) | 2013-02-06 | 2015-02-17 | Medical Service Consultation International, Llc | Methods and compositions for detecting Aspergillus terreus, Aspergillus niger, and mycotoxins |
US9833584B2 (en) | 2013-03-22 | 2017-12-05 | Breathe Technologies, Inc. | Portable ventilator secretion management system |
EP3019137B1 (en) | 2013-07-12 | 2019-02-06 | Trudell Medical International | Huff cough simulation device |
US9849257B2 (en) | 2013-08-22 | 2017-12-26 | Trudell Medical International | Oscillating positive respiratory pressure device |
GB201401566D0 (en) * | 2014-01-30 | 2014-03-19 | Smiths Medical Int Ltd | Respiratory therapy systems, sensors and methods |
US10363383B2 (en) | 2014-02-07 | 2019-07-30 | Trudell Medical International | Pressure indicator for an oscillating positive expiratory pressure device |
US10004872B1 (en) | 2015-03-06 | 2018-06-26 | D R Burton Healthcare, Llc | Positive expiratory pressure device having an oscillating valve |
CN111603643B (en) | 2015-04-02 | 2023-05-23 | 希尔-罗姆服务私人有限公司 | Pressure control of breathing apparatus |
JP6786198B2 (en) * | 2015-05-01 | 2020-11-18 | 株式会社フジ医療器 | Air massage device |
WO2017017657A1 (en) | 2015-07-30 | 2017-02-02 | Trudell Medical International | Combined respiratory muscle training and oscillating positive expiratory pressure device |
USD778429S1 (en) | 2015-09-02 | 2017-02-07 | Trudell Medical International | Respiratory treatment device |
USD780906S1 (en) | 2015-09-02 | 2017-03-07 | Trudell Medical International | Respiratory treatment device |
US10857317B2 (en) | 2015-12-04 | 2020-12-08 | Trudell Medical International | Huff cough simulation device |
WO2017144963A2 (en) | 2016-02-22 | 2017-08-31 | Trivikram | Respiratory care apparatus |
WO2017165359A1 (en) * | 2016-03-21 | 2017-09-28 | The Trustees Of The University Of Pennsylvania | Ambulatory respiratory assist device |
US10945699B2 (en) | 2016-12-28 | 2021-03-16 | Hill-Rom Services Pte Ltd. | Respiratory sound analysis for lung health assessment |
EP3618908A4 (en) | 2017-05-03 | 2021-01-13 | Trudell Medical International | Combined oscillating positive expiratory pressure therapy and huff cough simulation device |
US10953278B2 (en) | 2018-02-02 | 2021-03-23 | Trudell Medical International | Oscillating positive expiratory pressure device |
US11432995B2 (en) * | 2018-08-29 | 2022-09-06 | Leggett & Platt Canada Co. | Pneumatic massage |
EP4138669A1 (en) * | 2020-04-22 | 2023-03-01 | Tel Hashomer Medical Research Infrastructure And Services Ltd. | Lung airway clearance |
NL2027207B1 (en) * | 2020-12-23 | 2022-04-05 | Demcon Macawi Respiratory Systems B V | Ventilation system for ventilating a subject |
GB202214528D0 (en) | 2022-10-03 | 2022-11-16 | Owlstone Med Ltd | A compound |
US11839587B1 (en) | 2023-02-03 | 2023-12-12 | RightAir, Inc. | Systems, devices, and methods for ambulatory respiration assistance |
Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3683655A (en) * | 1970-03-27 | 1972-08-15 | Arlton H White | Breathing assist apparatus |
US3742939A (en) * | 1971-02-24 | 1973-07-03 | W Sayer | Method and apparatus for determining respiratory airway resistance |
US4051843A (en) * | 1975-02-26 | 1977-10-04 | Siemens Aktiengesellschaft | Apparatus for the determination of the respiratory passageway resistance |
US4928674A (en) * | 1988-11-21 | 1990-05-29 | The Johns Hopkins University | Cardiopulmonary resuscitation and assisted circulation system |
US4977889A (en) * | 1989-10-12 | 1990-12-18 | Regents Of The University Of Minnesota | Fitting and tuning chest compression device |
US5769797A (en) * | 1996-06-11 | 1998-06-23 | American Biosystems, Inc. | Oscillatory chest compression device |
US5806512A (en) * | 1996-10-24 | 1998-09-15 | Life Support Technologies, Inc. | Cardiac/pulmonary resuscitation method and apparatus |
US6066101A (en) * | 1998-04-20 | 2000-05-23 | University Of Maryland | Airflow perturbation device and method for measuring respiratory resistance |
US6068602A (en) * | 1997-09-26 | 2000-05-30 | Ohmeda Inc. | Method and apparatus for determining airway resistance and lung compliance |
Family Cites Families (61)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US402779A (en) * | 1889-05-07 | Emphysema | ||
US2354397A (en) | 1941-12-26 | 1944-07-25 | Gen Motors Corp | Jacket type respirator |
US2436853A (en) | 1944-04-10 | 1948-03-02 | Edwin D Coleman | Respiration apparatus |
US2588192A (en) | 1947-02-01 | 1952-03-04 | Akerman | Artificial respiration apparatus |
US2626601A (en) | 1950-07-28 | 1953-01-27 | John P Riley | Vacuum pulsating exercising apparatus |
US2772673A (en) | 1952-06-18 | 1956-12-04 | Conitech Ltd | Artificial respiration apparatus |
US2779329A (en) | 1953-06-17 | 1957-01-29 | Conitech Ltd | Artificial respiration apparatus |
US2832335A (en) | 1953-10-02 | 1958-04-29 | Conitech Ltd | Artificial respiration apparatus |
US2780222A (en) | 1953-12-18 | 1957-02-05 | J J Monaghan Company Inc | Respirators |
US2762366A (en) | 1954-12-29 | 1956-09-11 | Conitech Ltd | Artificial respiration apparatus |
US2818853A (en) | 1955-11-15 | 1958-01-07 | Conitech Ltd | Pressure regulator |
US3063444A (en) | 1956-02-13 | 1962-11-13 | Jobst Institute | Means for stimulating the flow of fluids in animal bodies |
US2869537A (en) | 1957-06-14 | 1959-01-20 | Chu John Jen-Chu | Pneumatic pressure respiratory vest |
US3043292A (en) | 1959-06-26 | 1962-07-10 | Emanuel S Mendelson | Inflatable, double-walled resuscitation garment |
US3120228A (en) | 1960-11-07 | 1964-02-04 | Harris A Thompson | Respirator apparatus |
US3333581A (en) | 1964-03-27 | 1967-08-01 | Elbert W Robinson | Pulmonary resuscitator with electrical control system |
US3310050A (en) | 1964-04-02 | 1967-03-21 | Goldfarb Herman | Massaging garment with vibrators located in back and chest sections |
CH473581A (en) | 1967-05-31 | 1969-06-15 | Werding Winfried | Therapeutic leg care facility |
US3566862A (en) | 1968-08-01 | 1971-03-02 | Paul A Schuh | Respiration apparatus |
US3802417A (en) | 1968-12-21 | 1974-04-09 | V Lang | Device for combined monitoring and stimulation of respiration |
US3760801A (en) | 1971-03-22 | 1973-09-25 | A Borgeas | Therapeutic exercising apparatus for torso and body extremities |
US3896794A (en) | 1973-12-14 | 1975-07-29 | British Oxygen Co Ltd | Venous flow stimulator |
US3993053A (en) | 1974-08-05 | 1976-11-23 | Murray Grossan | Pulsating massage system |
DE2611151A1 (en) | 1976-03-17 | 1977-09-29 | Rudolf Steuer | RELAXATION FACILITY |
US4079733A (en) | 1976-06-02 | 1978-03-21 | Hamburg Group | Percussion vibrator device for treatment of patients to assist expectoration of retained secretions |
US4398531A (en) | 1979-06-21 | 1983-08-16 | Hudson Oxygen Therapy Sales Company | Percussor |
US4311135A (en) | 1979-10-29 | 1982-01-19 | Brueckner Gerald G | Apparatus to assist leg venous and skin circulation |
US4326507A (en) | 1979-11-20 | 1982-04-27 | Michigan Instruments, Inc. | CPR Protocol and cardiopulmonary resuscitator for effecting the same |
US4349015A (en) * | 1980-11-14 | 1982-09-14 | Physio-Control Corporation | Manually-actuable CPR apparatus |
US4429688A (en) | 1980-12-08 | 1984-02-07 | Duffy Peter B | Medical appliance for percussive respiratory therapy |
US4424806A (en) | 1981-03-12 | 1984-01-10 | Physio-Control Corporation | Automated ventilation, CPR, and circulatory assistance apparatus |
US4397306A (en) | 1981-03-23 | 1983-08-09 | The John Hopkins University | Integrated system for cardiopulmonary resuscitation and circulation support |
DE3242814A1 (en) | 1982-11-19 | 1984-05-24 | Siemens AG, 1000 Berlin und 8000 München | METHOD AND RESPIRATOR FOR BREATHING A PATIENT IN THE HEART RHYMUS AND FOR SUPPORTING THE BLOOD CIRCULATION |
US4546764A (en) | 1983-04-08 | 1985-10-15 | Invacare Corporation | Postural drainage bed |
SU1247009A1 (en) | 1985-01-28 | 1986-07-30 | Тульский Ордена Трудового Красного Знамени Политехнический Институт | Artificial respiration apparatus |
US4621621A (en) | 1985-02-19 | 1986-11-11 | Marsalis John P | Vacuum valve system |
CA1307712C (en) | 1986-02-04 | 1992-09-22 | Zamir Hayek | Ventilator apparatus and fluid control valve |
US4838263A (en) | 1987-05-01 | 1989-06-13 | Regents Of The University Of Minnesota | Chest compression apparatus |
US5056505A (en) | 1987-05-01 | 1991-10-15 | Regents Of The University Of Minnesota | Chest compression apparatus |
US4886057A (en) | 1987-11-30 | 1989-12-12 | E Z Breathe, Inc. | Assisted breathing interface device |
JPH01223966A (en) | 1988-03-01 | 1989-09-07 | Sumitomo Bakelite Co Ltd | Respirator |
AU632469B2 (en) | 1988-04-04 | 1993-01-07 | Johns Hopkins University, The | A method for early detection of lung cancer |
US4971042A (en) * | 1988-11-14 | 1990-11-20 | Lerman Samuel I | Cardiac assist curiass |
US5222478A (en) | 1988-11-21 | 1993-06-29 | Scarberry Eugene N | Apparatus for application of pressure to a human body |
GB2226959B (en) | 1989-01-16 | 1992-11-18 | Zamir Hayek | Chest enclosures for ventilators |
US5193745A (en) | 1989-03-07 | 1993-03-16 | Karl Holm | Atomizing nozzle device for atomizing a fluid and an inhaler |
US5606754A (en) | 1989-03-09 | 1997-03-04 | Ssi Medical Services, Inc. | Vibratory patient support system |
JPH0336640U (en) | 1989-08-23 | 1991-04-10 | ||
US5261394A (en) | 1991-09-30 | 1993-11-16 | Triangle Research And Development Corporation | Percussive aid for the treatment of chronic lung disease |
CA2071379C (en) | 1991-11-12 | 1998-11-10 | John F. Dye | Compression device |
US5299599A (en) | 1992-09-17 | 1994-04-05 | Lifecare International, Inc. | Valving arrangement for a negative pressure ventilator |
US5453081A (en) | 1993-07-12 | 1995-09-26 | Hansen; Craig N. | Pulsator |
US5492115A (en) * | 1993-12-08 | 1996-02-20 | Abramov; Vladimir V. | Resuscitation breathing apparatus |
DE4416575A1 (en) | 1994-05-11 | 1995-11-16 | Ulrich H Prof Dr Med Cegla | Therapy device |
US5630789A (en) | 1994-10-07 | 1997-05-20 | Datascope Investment Corp. | Active compression/decompression device for cardiopulmonary resuscitation |
US5658221A (en) | 1995-02-10 | 1997-08-19 | Hougen; Everett D. | Portable personal breathing apparatus and method of using same |
IL115760A (en) * | 1995-10-25 | 1999-09-22 | S M C Sleep Medicine Center | Apparatus and method for measuring respiratory airways resistance and airways collapsibility in patients |
US5833711A (en) * | 1996-04-01 | 1998-11-10 | Cardi-Act, L.L.C. | Method and means for portable emergency cardiopulmonary resuscitation |
US5772613A (en) * | 1996-10-09 | 1998-06-30 | Cardiologic Systems, Inc. | Cardiopulmonary resuscitation system with centrifugal compression pump |
US6030353A (en) | 1998-04-28 | 2000-02-29 | American Biosystems, Inc. | Pneumatic chest compression apparatus |
US6910479B1 (en) * | 1999-10-04 | 2005-06-28 | Advanced Respiratory, Inc. | Airway treatment apparatus with bias line cancellation |
-
1999
- 1999-10-04 US US09/412,459 patent/US6910479B1/en not_active Expired - Lifetime
- 1999-10-04 US US09/412,768 patent/US6340025B1/en not_active Expired - Lifetime
- 1999-10-04 US US09/412,086 patent/US6210345B1/en not_active Expired - Lifetime
- 1999-10-04 US US09/412,457 patent/US6415791B1/en not_active Expired - Lifetime
-
2000
- 2000-08-29 JP JP2001527700A patent/JP2004500905A/en not_active Withdrawn
- 2000-08-29 WO PCT/US2000/023705 patent/WO2001024698A1/en not_active Application Discontinuation
- 2000-08-29 AU AU70859/00A patent/AU7085900A/en not_active Abandoned
- 2000-08-29 EP EP00959562A patent/EP1225834A4/en not_active Withdrawn
Patent Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3683655A (en) * | 1970-03-27 | 1972-08-15 | Arlton H White | Breathing assist apparatus |
US3742939A (en) * | 1971-02-24 | 1973-07-03 | W Sayer | Method and apparatus for determining respiratory airway resistance |
US4051843A (en) * | 1975-02-26 | 1977-10-04 | Siemens Aktiengesellschaft | Apparatus for the determination of the respiratory passageway resistance |
US4928674A (en) * | 1988-11-21 | 1990-05-29 | The Johns Hopkins University | Cardiopulmonary resuscitation and assisted circulation system |
US4977889A (en) * | 1989-10-12 | 1990-12-18 | Regents Of The University Of Minnesota | Fitting and tuning chest compression device |
US5769797A (en) * | 1996-06-11 | 1998-06-23 | American Biosystems, Inc. | Oscillatory chest compression device |
US5806512A (en) * | 1996-10-24 | 1998-09-15 | Life Support Technologies, Inc. | Cardiac/pulmonary resuscitation method and apparatus |
US6068602A (en) * | 1997-09-26 | 2000-05-30 | Ohmeda Inc. | Method and apparatus for determining airway resistance and lung compliance |
US6066101A (en) * | 1998-04-20 | 2000-05-23 | University Of Maryland | Airflow perturbation device and method for measuring respiratory resistance |
Non-Patent Citations (1)
Title |
---|
See also references of EP1225834A4 * |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7416536B2 (en) | 2002-10-02 | 2008-08-26 | Devlieger Marten Jan | Chest vibrating device |
US7425203B2 (en) * | 2002-11-15 | 2008-09-16 | Hill-Rom Services, Inc. | Oscillatory chest wall compression device with improved air pulse generator with improved user interface |
US7491182B2 (en) | 2002-11-15 | 2009-02-17 | Hill-Rom Services, Inc. | High frequency chest wall oscillation apparatus having plurality of modes |
US7582065B2 (en) * | 2002-11-15 | 2009-09-01 | Hill-Rom Services, Inc. | Air pulse generator with multiple operating modes |
US7615017B2 (en) | 2002-11-15 | 2009-11-10 | Hill-Rom Services, Inc. | High frequency chest wall oscillation system |
US8038633B2 (en) | 2002-11-15 | 2011-10-18 | Hill-Rom Services Pte. Ltd. | High frequency chest wall oscillation system with crankshaft assembly |
US8708937B2 (en) | 2002-11-15 | 2014-04-29 | Hill-Rom Services Pte. Ltd. | High frequency chest wall oscillation system |
US9572743B2 (en) | 2006-12-13 | 2017-02-21 | Hill-Rom Services Pte Ltd. | High frequency chest wall oscillation system having valve controlled pulses |
CN103989575A (en) * | 2014-06-09 | 2014-08-20 | 河北爱西欧医疗设备科技有限公司 | Multi-cavity cam sputum excretion system |
US10518048B2 (en) | 2015-07-31 | 2019-12-31 | Hill-Rom Services, PTE Ltd. | Coordinated control of HFCWO and cough assist devices |
Also Published As
Publication number | Publication date |
---|---|
AU7085900A (en) | 2001-05-10 |
US6415791B1 (en) | 2002-07-09 |
EP1225834A4 (en) | 2004-12-29 |
JP2004500905A (en) | 2004-01-15 |
US6910479B1 (en) | 2005-06-28 |
US6340025B1 (en) | 2002-01-22 |
EP1225834A1 (en) | 2002-07-31 |
US6210345B1 (en) | 2001-04-03 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6210345B1 (en) | Outcome measuring airway resistance diagnostic system | |
US5555880A (en) | High frequency oscillatory ventilator and respiratory measurement system | |
JP3635097B2 (en) | Leak and respiratory airflow determination | |
US6030353A (en) | Pneumatic chest compression apparatus | |
US4977889A (en) | Fitting and tuning chest compression device | |
US8905025B2 (en) | Closed loop control system for a high frequency oscillation ventilator | |
JP2003102838A5 (en) | ||
JPH08229129A (en) | Method to determine transfer function for connecting device,and device for feeding and discharging of gas for breathing | |
EP2758112B1 (en) | Upper airway resistance measurement device | |
SE9702710L (en) | A method for determining the mechanical properties of the respiratory system of a patient breathing and a device for carrying out the procedure | |
EP1270036A3 (en) | Breathing gas delivery method and apparatus | |
EP1132105B1 (en) | High frequency oscillation ventilator | |
CN107412930B (en) | A kind of respiratory assistance apparatus | |
CN106964043B (en) | A kind of respiratory auxiliary system based on cloud computing | |
JP3655792B2 (en) | Breathing oxygen delivery system | |
US20230116467A1 (en) | High frequency chest wall oscillation air pulse generator having pressure sensor for feedback control | |
JP3767329B2 (en) | Computer-readable recording medium on which high-frequency ventilator and its operation control program are recorded | |
AU756622B2 (en) | Determination of leak and respiratory airflow | |
CA2520745C (en) | Determination of leak and respiratory airflow | |
AU2002306200B2 (en) | Determination of Leak and Respiratory Airflow | |
SU1391647A1 (en) | Apparatus for artificial ventilation of the lungs | |
RU19264U1 (en) | EMERGENCY RESPIRATORY RESPONSE | |
AU2005200987B2 (en) | Determination of Leak and Respiratory Airflow |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BY BZ CA CH CN CR CU CZ DE DK DM DZ EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG UZ VN YU ZA ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
WWE | Wipo information: entry into national phase |
Ref document number: 2000959562 Country of ref document: EP |
|
ENP | Entry into the national phase |
Ref country code: JP Ref document number: 2001 527700 Kind code of ref document: A Format of ref document f/p: F |
|
WWP | Wipo information: published in national office |
Ref document number: 2000959562 Country of ref document: EP |
|
REG | Reference to national code |
Ref country code: DE Ref legal event code: 8642 |
|
WWW | Wipo information: withdrawn in national office |
Ref document number: 2000959562 Country of ref document: EP |