|Publication number||US3903881 A|
|Publication date||Sep 9, 1975|
|Filing date||Apr 12, 1974|
|Priority date||Apr 12, 1974|
|Publication number||US 3903881 A, US 3903881A, US-A-3903881, US3903881 A, US3903881A|
|Original Assignee||Bourns Inc|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (3), Referenced by (68), Classifications (9), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States Patent 1 Weigl 52 us. c1 it 128/1456; 128/1458 5m 1m. c1. .1 A61M 16/00 5m Field of Search .v l28/l45b, 142.2-|42.4
128/1457, 145.8. [455 146.4, [46.1 I88, DlG. 17 203, 184
 References Cited UNITED STATES PATENTS 212L311 (1/1938 Anderson Q8/1458 3.046.979 7/1962 Andreasen ,1 lZ8/l458 174L208 WW7} JonsstmuH l28/l45h Primary I;.\'uminerRichard A. Gaudet Amish/n1 Eruminer-Henry J. Recla Almrney, Agent, or FirmWilliam G. Becker; Richard S. Koppel Sept. 9, 1975 l 57 ABSTRACT A respirator system and method in which a constant pressure plenum communicates through a gas bleeder with the patient gas supply system, The bleeder is adjustable so that a gas flow can be established from the plenum to the gas conduits at a level sufficient to compensate for leaks from the patients mouth and trachea, but less than that required by the patient during voluntary inhalation The pressure inside the conduit system and hence in the patients lungs, is thereby maintained at a level at least as great as a minimum desired amount. A discrimination between patient attempts at breathing and leaks from the conduit system is achieved by sensing the gas flow rate towards the patient and actuating a breath assist function only in response to that flow rate equaling or exceeding the expected inhalation rate, without reference to the ahsolute pressure within the conduit system 15 Claims. 6 Drawing Figures BREATH A55/57' CONTROL l Ass/5r TRANSDUCER 6A5 g JET PATENTED SEP 91975 I BREA TH ASS/5 T CON T/QOL SHEET 3 OF 3 PREiSURE REGUL A 727R RESPIRATOR SYSTEM AND METHOD BACKGROUND OF THE INVENTION This invention relates to medical respirator systems, and more particularly to positive pressure respirator systems having a breath assist mode in which delivery of gas to the patient is initiated when the patient at tempts to inhale.
Respirator systems are known in which a breath assist function is actuated to deliver a certain volume of gas to the patient when he or she indicates an attempt to breathe by inhaling gas from the gas supply conduit system. A common method of identifying a patient request for breath assistance involves a measurement of the gas pressure within the conduits; the patients suction reduces the pressure to a level below a predetermined threshold, triggering the breath assistance apparatus into operation. A controlled volume of air is then forced through the supply system to the patients lungs, following which the patient exhales and then attempts to breathe again, retriggering the breath assistance apparatus. An override control is generally included with the respirator to actuate breath assistance should the patient fail to voluntarily inhale within a certain time limit.
While presently available systems can function adequately in a loss-less environment, a dangerous situation can develop if there are gas leaks from the supply conduit. Such leaks often develop at the end of the flexible tube inserted into the patients trachea, since the trachea does not provide a perfect seal for the tube, and gas can escape out through the patients mouth rather than being delivered to the lungs. In this event, there is a continuous loss of gas from the supply conduit that can lead to an accumulating drop in pressure therein during expiration phases of the respirator cycle. Should the pressure drop to a level below the preset threshold. a false triggering signal is delivered to the breath assistance apparatus, which accordingly delivers an additional quantity of gas before the patient is ready to receive it. Such premature breath assistance has resulted in an unstable runaway condition in which the breath assistance apparatus cycles at several times the normal breathing rate, causing a buildup of pressure within the patients lungs above a safe amount. The patient does not have sufficient time to relieve the excess pressure by cxhaling, and if the condition is not quickly observed and corrected may suffer serious lung damage or worse.
A related problem with known respirator systems relates to the maintenance of a minimum pressure level in the lungs of patients who suffer from diseases which cause a shrinking of the alveolar sacs. in such conditions, it is important to maintain the lung pressure at a level at least sufficient to keep the sacs expanded. Some of this pressure can be lost, however, if there are leaks in the gas conduit system. such as the abovedescribed tracheal tube leak. Even if a runaway breath assistance condition is avoided, the pressure loss may be large enough to allow the sacs to shrink to an unacccpt able size.
SUMMARY OF THE INVENTION It is an object of the present invention to provide a novel and improved respirator system and operating method for delivering quantities of gas in response to patient need.
Another object is the provision of a novel and improved respirator system with the ability to discriminate between gas leaks and a patient request for breath assistance, and to operate a breath assistance function only in response to patient need.
A further object of the invention is the provision of a novel and improved respirator system having means to maintain the pressure in the gas supply conduit system at a level at least as high as a predetermined minimum pressure, regardless of gas leaks from the supply system.
Another object is the provision of a novel and improved respirator system having a high degree of sensitivity in the detection of a patient request for breath assistance, with the detection mechanism being independent of the absolute pressure within the supplied conduit system.
Still another object is the provision of a novel and improved method of operating a respirator system in such a way as to achieve the above-stated objects.
In the accomplishment of these and other objects, a respirator system is provided that includes gas conduit means having an inlet port, an outlet port, and a patient supply tap intermediate to the inlet and outlet ports for conducting gas to the patient. The inlet port receives gas from a recyclable gas charging means during inhalation phases of the patients breathing. Any outward flow of gas from the conduit system through the inlet port is blocked during expiration phases by a first valve means, while a second valve means blocks any inward flow of gas through the outlet port during inhalation phases. A pressure plenum with associated means for positively maintaining the pressure therein at a predetermined level provides a gas source to compensate for leaks, the gas flowing through a bleeder means into the conduit means when the pressure in the conduit means falls below the said predetermined level. A gas flow sensing means senses the flow of gas towards the patient du ing the expiration phase and produces a signal that at tes a control for the charging means when the gas 51.. r ;ceeds a predetermined threshold flow rate, due he onset of inspiration by the patient. The
bleeds; means provides a substantially unrestricted gas flow path from the plenum into the conduit means for flow rates up to a maximum which is approximately equal to the said threshold flow rate. Gas leaks from the patient supply tap which do not exceed the said threshold flow rate are thereby replenished by a compensating gas flow into the conduit means from the plenum, without actuating the charging means, while the pressure in the conduit means is maintained at a level which is substantially at least equal to the predetermined plenum level despite such gas leaks.
The operating method contemplated by the present invention comprises sensing the gas flow rate towards the patient through the conduit means when the inlet port is blocked by the first valve means, supplying gas to the conduit means during expiratory phases to compensate for gas leaks from the patient supply tap, limit ing such compensating flow to a rate no greater than the patients expected voluntary inhalation flow rate, and actuating the charging means control to operate the charging means when the sensed gas flow rate exceeds a predetermined threshold level which is no greater than the patients expected voluntary inhalation flow rate.
In a particular embodiment of the invention, the outlet port or expiratory end of the conduit means is en'- gaged to maintain the conduit pressure at or above the desired minimum level by connecting the bleeder means between the plenum and the said outlet port. In this embodiment, the gas flow sensor comprises a pressure differential sensor which is operably connected to sense pressure differences between the plenum and the outlet port. The bleeder means includes an adjustable flow restriction means adapted to produce a predetermined pressure differential across the bleeder when the gas flow rate therethrough equals the threshold flow rate for actuating the charging means. As the bleeder means provides the only gas inlet into the conduit dur ing expiration phases, the said pressure differential may be equated to a voluntary inhalation by the patient. The bleeder means enables an equilization of pressure between the plenum and the conduit means for normally encountered leaks that do not exceed the threshold flow rate, thereby preventing an accumulation of gas loss from the conduit means and a resulting false triggering of the charging means.
More detailed aspects of this embodiment include the provision of a second plenum that communicates with the conduit means during expiration phases through the outlet port thereof, substantially equalizing the conduit means pressure with the second plenum pressure. A check valve separates the two plenums and permits a unidirectional gas flow from the second to the first for the removal of expired air from the system. The plenums are respectively enclosed within first and second chambers, with a jet means provided to direct a substantially constant velocity gas jet through a venturi and into the first chamber for maintaining the pressure in said chamber at a substantially constant level. A third chamber is interposed between the jet means and the venturi, and includes at least one outlet orifice for venting gas expired by the patient.
In another embodiment of the invention, a sensing means is interposed in line with the patient supply tap to directly sense the gas flow towards the patient during expiration phases. In this embodiment, the pressure within the conduit means may be maintained at or above the desired minimum level by means of a simple pressure regulator communicating with the conduit means at any convenient location.
BRIEF DESCRIPTION OF THE DRAWINGS Further advantages and features of the present invention will be apparent to those skilled in the art from the ensuing detailed description thereof, taken with the accompanying drawings, in which:
FIG. I is a partially schematic diagram ofa respirator system constructed in accordance with the invention;
FIG. 2 is an illustrative graphical representation of a typical gas flow cycle encountered in a tube inserted into a patients trachea and supplied with gas by a respirator system which incorporates the present invention, illustrating the effect of a gas leak at the end of the tube;
FIG. 3 is an illustrative graphical representation of the gas pressure inside the conduit system during cycli cal operation of a respirator, with the pressure pattern characteristic of the present invention shown in solid lines and that of an unstable condition encountered in the prior art in dashed lines;
FIG. 4 is a sectional view in frontal elevation of the pressure control and sensing apparatus provided in one embodiment of the invention;
FIG. 5 is a sectional view in right-side elevation of the upper portion of the apparatus shown in FIG. 4', and
FIG. 6 is a schematic diagram of another embodimerit of the invention.
DETAILED DESCRIPTION OF PARTICULAR EMBODIMENTS Referring to FIG. I, there is shown an embodiment of the invention in which an air or air-oxygen mixture is delivered to a conduit system by a conventional charging apparatus which includes a gas mix box 10 in which gas is mixed to the desired composition, a piston 12 slidably lodged in a cylinder 14, and a manifold 16 from which gas is supplied to the delivery system. The piston 12 sucks in air from the manifold 16 through a connecting pipe 18 during baekstrokes, producing a pressure drop in the manifold 16 that draws in air from mix box 10 through a check valve 20. An adjustable pressure relief valve 22 is located in the manifold 16 to assure that the gas delivered to the patient does not exceed the pressure setting of the relief valve. The piston 12 moves forward in response to an actuating signal from a breath assist control switch 24, delivering a volume of gas from the manifold 16 to the patient supply system. The gas volume may be either a preset amount or determined dynamically by measuring the patients lung pressure and stopping piston movement when that pressure reaches a desired level.
The conduit means for guiding the flow of gas to and from a patient includes a plastic tubing network, generally indicated by numcral 26, in a T configuration. One branch 28 of the T functions as an inlet or inhalation tube, the end of which is open and fitted over an orifice in manifold 16 to form an inlet port 30 for the tube network. The other branch 32 serves as a gas outlet or expiration tube and has an open end comprising a gas outlet port 34. A spur tube 36, which may be equated to the stern of the T, is tapped into the tube network at a location intermediate the inlet and outlet ports 30 and 34, and provides a conduit for both inhaled and expired gas. An additional plastic tube 38, which may be referred to as the tracheal tube, is tightly fitted over tube 36 and passed down the trachea of the patient 40 to conduct air to and from the patients lungs. Associated with the inlet branch 28 is a pressure gauge 42 and a filter or humidifying device 44 to treat the supplied gas before delivery to the patient. The tracheal tube 38 is generally introduced through the mouth. but under certain circumstances it may be directed through a nasal passage, or surgically inserted directly into the trachea.
Gas blocking devices are provided at either branch end of the tube network 26 to insure that gas will flow through the inlet branch only in a direction from the manifold I6 to the patient, and through the outlet branch 32 only from the patient to the outlet port 34 (expect for certain triggering and leakage flows dis cussed below). The flow blocking mechanism or inlet branch 28 comprises a check valve 46 set in the inlet port 30, while the blocking mechanism for outlet branch 32 comprises the combination of a diaphragm 48 and a reciprocal piston 50 aligned to alternately flex the diaphragm 48 to a position blocking outlet port 34 and to release the diaphragm to a non-blocking posi tion.
There will frequently be a small clearance between the tracheal tube 38 shown in FIG. I and the patient's trachea, resulting in a certain loss of gas from the patient-respirator complex that escapes up through the trachea around the tracheal tube 38 and out the patients mouth, such gas losses being indicated in the figure by arrows 52. To compensate for these gas losses without subjecting the patient to the risks inherent in prior respirator systems, a structure is provided at the outlet port 34 that includes first and second chambers 54 and 56, mutually partitioned by a check valve 58 that enables a unidirectional gas flow from the chamber 56 to chamber 54. The second-mentioned chamber 56 completely surrounds the outlet port 34 so that all gas entering or leaving the said port must also pass through chamber 56, fixing the pressure in outlet branch 32 whenever the outlet port 34 is unblocked. Diaphragm 48 forms one wall of the chamber 56, the other chamber walls conveniently being formed from a plastic mold.
The pressure inside chamber 54 is maintained at a constant level by means of a gas jet source 60 that delivers a steady jet stream through openings in the longitudinally opposed walls ofa third chamber 62 to a venturi 64 that opens into the first chamber 54. The gas jet source 60 is adjustable within a range enabling the pressure inside chamber 54 to be set at between zero and centimeters H O gauge (70 centimeters H O equaling approximately 1 pound per square inch). The third chamber 62 is provided with four orifices in its transverse walls, two of which are shown in the drawings and identified by reference numerals 66 and 68, through which gas exhaled by the patient may be expelled from the respirator system.
A bleeder conduit or line 70 is connected between chambers 54 and 56, with an adjustable needle valve 72 forming a restriction in the bleeder line to limit the gas flow rate from chamber 54 to chamber 56 (gas flows in the opposite direction, from chamber 56 to chamber 54, are transmitted through check valve 58, which forms a parallel bypass to the blcedcr line 70 in this flow direction). The needle valve 72 may be adjusted from a full opcn position, at which the gas flow through the bleeder line 70 is substantially unrestricted, to a completely closed position.
A transducer 74, shown in FIG. 1, senses the pressures in chambers 54 and 56 through connecting tubes 76 and 78, respectively, and compares the two sensed pressure. When the pressure in chamber 54 exceeds that in chamber 56 by a predetermined threshold amount for which the transducer 74 is set, control sig nals are transmitted from the transducer to the breath assist control 24 for actuation of the breath assist mechanism, and to the piston 50 causing that piston to move against the diaphragm 48 and block the outlet port 34. The pickup level of transducer 74 for triggering the breath assist mechanism is adjustable within a range of. for example, 0.05 centimeter H O to 1.0 ccntimctcr H O. The needle valve 72 and transducer 74 are set at levels determined by the expected voluntary inhalation flow rate produced by the patient 40 such that gas flows through bleeder line 70 from chamber 54 to chamber 56 are substantially unrestricted by needle valve 72 for How rates that do not exceed the expected inhalation flow rate. For such flow rates, the pressure inside chambers 54 and 56 are substantially identical, and transducer 74 will not produce a control signal.
Should a back flow be established through outlet branch 32 towards the patient that exceeds the expected inhalation flow rate, needle valve 72 restricts the flow rate of gas through bleeder line to a level less than that which is necessary to equalize the pressure between chambers 54 and 56, thereby producing a pressure differential between the two chambers that causes transducer 74 to produce a control signal.
Cyclical gas flows to and from the patient and the gas pressure within the cm duit network are illustrated respectively in FIGS. 2 and 3. Referring first to FIG. 2, the cyclical respirator operation is assumed to be initiated when piston 12 is actuated by breath assist control 24 to move forward into cylinder 14, producing an inflow of gas to the patient as indicated by line 80. When the patient has inspired a sufficient quantity of gas, the respirator system switches to an exhalation mode in which gas is expired from the patients lungs, through tube 36, and out the outlet port 34, as indicated by line 82. When the patient has expelled a full quantity of gas, the respirator system pauses until the patient inhales gas from the tube network in an attempt to draw breath, the initial inhalation attempt being indicated by the in-flow surge 84. With a proper adjustment of the needle valve 72 and transducer 74, this surge will ex cced the trigger threshold 86 at which the transducer 74 is set, producing a signal to actuate the breath assist mechanism and initiate another gas charge 88 into the respirator tube network, thereby starting another breath cycle. It should be noted that a substantial amount of gas leakage, as indicated by line 90, may be tolerated from the tube network without triggering the transducer 74 to actuate the breath assist mechanism, so long as the leakage is not so gross as to exceed the trigger threshold level 86.
The gas pressure pattern in the respirator tubes is illustrated in FIG. 3 against the same time scale as that of FIG. 2. The pressure increases along line 92 as gas is charged into the tube in response to a trigger signal, reaching a peak at the end of the charging period and then gradually declining along line 94 to a level not less than the minimum required to adequately expand the alveolar sacs. The pressure pattern produced by the present invention is shown in solid lines. During the interval 96 following full breath expiration but prececd ing the beginning of the next inhalation, the pressure in the tubes remains steady and does not drop below the minimum desired level, despite the continuous leakage from the tracheal tube during this period, because a replenishing flow of gas is supplied to the tubes through bleeder line 70 and chamber 56. A slight dip in pressure 98 occurs when the patient attempts to inhale, this dip resulting from the patients intake rate exceeding the rate at which replenishing gas can be supplied through bleeder line 70. Although slight, the pressure dip 98 is sufficient to actuate the highly sensitive transducer 74 to produce a control signal, recycling the breath assist mechanism. It can be seen from the drawing that the tube pressure is maintained at a substantially constant value during the interval 96, and successful breathing is achieved. By contrast, an unstable condition that may occur with prior art respirator systems is indicated in dashed lines. Such prior art systems that do not employ compensating gas supply mechanisms will gradually undergo an accumulating pressure loss during an expiration phase due to the gas leak. As the breath assist mechanism for these systems is com monly responsive to the pressure within the tubes, rather than to the gas flow rate measured by the present invention, a point may be reached at which the pressure drop is sufficient to actuate the breath assist mechanism, and a new charge of gas is supplied to the system before the patient is ready to receive it. This occurrence is indicated at point 100 in FIG. 3. It may lead to an unstable condition in which the the patient does not have sufficient time to exhale before the next charge of gas. The pressure inside the lungs which is generally somewhat less than the tube pressure but follows a similar rise and fall pattern, can thereby build up to the point at which a pneumothorax occurs.
Referring now to FIGS. 4 and 5 for further details of the apparatus at the expiratory end of the tube network, chamber 56 is formed from a plastic block with a cylindrical tube 102 extending through one wall to form a mounting jack for outlet tube 32 on the exterior of the chamber, the other end of tube 102 forming outlet orifice 34 adjacent to flexible membrane 48. The chamber 54 comprises an inner chamber 104 downstream of winged check valve 58 that commun" with a surrounding annular gas reservoir 106 t a port 108. The bleeder line 70 of FIG. 1 com passageway 110 through the chamber block, s FIG. 5, a portion of which passageway is sh form a seat 112 for manually adjustable needl 72, which is shown in a closed position. Highly sensitive adjustments may be made to the flow restriction produced by needle valve 72 by rotating the valve handle 114 to lift or lower the valve stem 116. A similar needle valve 118 is provided in the gas jet mechanism to enable a precise control of the jet, indicated by arrow 120, before entering the venturi 64. Gas is introduced into the jet mechanism through a nozzle 122 at a pressure of approximately 50 psig, passes through a filter 124 and restriction orifice 126 to a smaller chamber 128 at a pressure in the order of I020 psig, and then proceeds through valve 118 for deflection upward to the chamber 62, venturi 64, and chamber 54. The valve 118 is adjustable within a range which results in a gas pressure in chamber 54 of between zero and centimeters H O gauge, as mentioned previously.
A solenoid 130 is arranged about a rearward extension 132 of the piston 50 to move the piston alternately into and away from the diaphragm 48, blocking and opening outlet port 34. The solenoid is connected by leads 134 for control by the transducer 74.
In operation, the tracheal tube 38 is inserted into the patients trachea and the respirator turned on with the needle valve 72 fully open. At this point, the flow of gas through bleeder line 70 from chamber 54 to chamber 56 will generally be substantially unrestricted, even for flow rates as large as that produced by the patient inhaling, and the breath assist apparatus will not respond to the patient's breathing. The needle valve 72 is then gradually closed until the restriction presented to the flow of gas through the bleeder line 70 during patient inhalation attempts is sufficient to produce a pressure drop that exceeds the threshold level of transducer 74, thus triggering the breath assist apparatus into action. This point may be detected by observing when the pressure inside the conduit network, as indicated by pressure gauge 42, first begins to follow the patients rhythmic breathing rate and exhibits a cyclical pattern such as that shown in FIG. 3 With the needle valve 72 at this setting, the flow path through bleeder 70 is sufficiently open to enable a replenishing gas flow from chamber 54 to chamber 56 and thence into the conduit network 26 to compensate for all except unusually large gas leaks from that network, without triggering the breath assist apparatus. At the same time, patient attempts to inhale will produce a pressure drop that does trigger the breath assist.
A full cycle of the respirator operation, beginning at a time just after the transducer 74 has sensed an attempt to breath, will now be described. At the beginning of the cycle to the solenoid, an energizing signal is transmitted from the transducer 74 over leads 134 to the solenoid 130, producing a magnetic field that urges piston 50 against diaphragm 48 to close the outlet port 34. The transducer 74 also transmits a control signal to the breath assist control switch 24, which actuates piston 12 to move into cylinder 14, thereby forcing gas out of manifold 16, past check valve 46, and into the conduit network through inlet port 30. With the outlet port 34 closed, a volume of gas equal to that charged into the conduit system is forced out through tap 36 and the tracheal tube 38. Most of this gas will be supplied to the patients lungs, but some may be lost by leakage at the end of the tracheal tube 38.
At the end of the inhalation phase, the piston 12 is retracted, drawing a new supply of gas into the mani' fold 16 from mix chamber 10, and the patient begins to exhale. At about the same time, the energizing signal is removed from solenoid 130 and the piston 50 is spring urged back from diaphragm 48, opening outlet port 34. Check valve 46 blocks any outflow of gas through inlet valve 30, so that all of the patients expired gas flows through outlet port 34 into chamber 56, through check valve 58 and chamber 54, and out through vents 66, 68 and the vents not shown in the drawings. After active expiration ends, there is a pause before the next breath and renewed operation of the breath assist apparatus, during which time gas leaks may continue to drain gas from the conduit network. During this period. the chamber 54 is maintained as a substantially constant pressure plenum by the gas jet mechanism 60 acting through venturi 64. The gas leaks are made up by a compensating, substantially unrestricted gas flow through the bleeder line from chamber 54 to chamber 56, thus maintaining the latter chamber also as a substantially constant pressure plenum. Since chamber 56 communicates openly with the conduit network through outlet port 34, the pressure in that network may be kept at or above a minimum desired lung pressure so long as the pressure in chamber 54 is maintained.
When the patient attempts to draw breath, a sudden inflow of gas to the tap 36 is created which, due to the restriction of needle valve 72, cannot be fully met by a compensating flow through bleeder line 70. As a result, the pressure within the conduit network drops momentarily, creating a pressure differential between the plenums of chambers 54 and 56 that exceeds the threshold of transducer 74, which instrument thereupon produces appropriatc signals to start another respirator cycle.
The abovcdescribed embodiment is highly sensitive to gas flows, and is therefore particularly useful for patients such as infants who process a relatively small amount of gas with each breath. Another embodiment of the invention shown in FIG. 6 that is intended to be used with adults. This embodiment employs a simplifled apparatus to achieve a somewhat lesser degree of sensitivity that nonetheless is sensitive enough for older patients. Several elements of this embodiment are carried over from the embodiment of FIG. 1, and the same numerals have been used to indicate elements common to both.
Gas is cyclically charged into the conduit network, as in the previous embodiment, by breath assist apparatus which includes a piston 12 slidably lodged in cylinder 14, a gas mix chamber 10, and a manifold 16 which is connected by pipes or tubes to the last two elements. Check valve 46 prevents any reverse gas flow out of the conduit inlet port 30, while an expandable balloon or bladder 136 is positioned adjacent to outlet port 34 to block that port during inhalation by expanding under the influence of air pumped in through a balloon stem 138.
lnstead of sensing a patients attempt to breathe by measuring pressure differentials at the expiration end of the 'onduit network, a gas flow sensing mechanism 140 is interposed directly in line with the patient tap 36. Gas flow sensor 140 may be of any convenient type, for example an ultrasonic device such as the sensor described in US. Pat. NO. 3,680,375 to Joy et al., so long as it is able to detect gas flows caused by a patients attempt to inhale. A pressure regulator 142 is tapped into the inlet conduit branch 28 through a bleeder arrangement such as check valve 144 that permits gas to flow only into the conduit, the pressure regulator 142 comprising essentially a constant pressure plenum which is maintained at the minimum desired expiratory pressure.
Gas flow sensor 140 is connected in a control circuit with the breath assist control 24 through a switch 146, and also to the balloon I36, switch 146 being closed during expiration but open during inhalation to prevent the breath assist apparatus from being triggered. in operation, gas is charged into the conduit network to the patient for the patient to inhale, with balloon 136 expanded to block outlet port 30. After the patient has received a full breath, balloon 136 is permitted to go flacid and the patient expires through outlet branch 32 and outlet port 34. Should the pressure in the conduit network begin to fall below the level necessary to keep the alveolar sacs expanded, for instance because of gas leakage from tracheal tube 38, a gas flow commences from the pressure regulator 142 into the conduit system that holds the pressure therein at an acceptable level. When the patient again attempts to inhale. the large inrush of gas exceeds the setting of flow sensor 140, which thereupon initiates a control signal to trigger the breath assist control 24 and the input mechanism for balloon 136, beginning a new breath cycle.
lt is obvious that many modifications may be made to the subject invention which come within its true scope and spirit. Thus, the scope of the subject invention is considered to be limited only by the appended claims,
What is desired to be secured by Letters Patent of the United States is:
l. A respirator system for assisting a patient's breathing during alternate inhalation and expiration phases, said system including gas conduit means having an inlet port, an outlet port, and a patient supply tap intermediate said inlet and outlet ports, recyclable means for charging gas into said inlet port during inhalation phases for delivery to a patient, a control means for actuating said charging means. first valve means adapted to (ill block an outward flow of gas through said inlet port during expiration phases, and second valve means adapted to block an inward flow of gas through said outlet port during inhalation phases, wherein the improvement comprises the provision of:
a pressure plenum,
means for positively maintaining said plenum at a predetermined pressure level,
bleeder means adapted to conduct gas from said plenum into said gas conduit means, and
a gas flow sensing means adapted to sense a flow of gas through said conduit means towards the patient during expiration phases and to produce a control signal in response to said flow exceeding a predetermined threshold flow rate,
said control means being connected to said sensing means for actuation by said control signal, and said bleeder means providing a gas flow path of sufficient conductance to enable a substantially unrestricted inflow of gas into said conduit means from said plenum at a maximum rate approximately equal to said threshold flow rate, whereby gas leaks from the patient supply tap at leak rates not exceeding the said threshold flow rate are replenished by a compensating gas flow into the conduit means from the pressure plenum without producing a control signal for actuating the gas charging means, and the pressure in said conduit means is maintained at a level substantially at least equal to said predetermined plenum level despite said gas leaks.
2. The respirator system of claim 1, wherein said bleeder means provides a gas flow path from said plenum to the outlet port of said conduit means, and said gas flow sensing means comprises a pressure differential sensor means operably connected to sense pressure differences between said plenum and said outlet port, said bleeder means including flow restriction means adapted to produce a predetermined pressure differential across said bleeder means when the gas flow rate therct nugh to said outlet port equals said threshold flow we said pressure differential sensor means being ada" .o produce a control signal in response to the sen. 5 pressure differential exceeding said predetermined amount.
3. The respirator system of claim 2, said flow restriction means including adjustment means for adjusting the maximum gas flow rate through said bleeder means within a range corresponding to the expected range of voluntary inhalation flow rates produced by a patient.
4. The respirator system of claim 1, wherein said gas flow sensing means is interposed in line with said pa tient supply tap.
5. A respirator system for assisting a patients breath ing during alternate inhalation and expiration phases, said system including gas conduit means having an inlet port, an outlet port, and a patient supply tap intermediate said inlet and outlet ports, recyclable means for charging gas into said inlet port during inhalation phases for delivery to a patient, a control means for actuating said charging means, first valve means adapted to block an outward flow of gas through said inlet port during expiration phases, and second valve means adapted to block an inward flow of gas through said outlet port during inhalation phases, wherein the improvement comprises the provision of:
first and second pressure plenums, means for positively maintaining the pressure in said first plenum at a predetermined level, adjustable bleeder means adapted to conduct gas from said first plenum to said second plenum to provide a pressure therein, said second plenum communicating with said conduit means during the expiration phases of said respirator so as to maintain said conduit means at a pressure substantially equal to the pressure of the second plenum during such expiration phases, and a pressure differential sensor means operably connected to sense pressure differences between said first and second plenums and to produce a control signal for actuation of the control means in response to the sensed pressure differential exceeding a predetermined amount.
6. The respirator system of claim 5, wherein said second plenum communicates with said conduit means through the outlet port thereof, said bleeder means providing a gas flow path from said first plenum to said second plenum and thereby to said conduit means during expiration phases when said sccondvalve means is open. and further including vent means communicating with said first plenum to vent expired air from the systern.
7. The respirator system of claim 6, and further including a passageway between said first and second plenums, said passageway including a check valve en abling a unidirectional gas flow from the second plenum to the first plenum in response to a pressure differential therebetween of appropriate polarity.
8. A respirator system for assisting a patients breathing during alternate inhalation and expiration phases, said system including gas conduit means having an inlet port, an outlet port, and a patient supply tap intermediate said inlet and outlet ports, recyclable means for charging gas into said inlet port during inhalation phases for delivery to a patient, a control means for actuating said charging means, first valve means adapted to block an outward flow of gas through said inlet port during expiration phases, and second valve means adapted to block an inward flow of gas through said outlet port during inhalation phases, wherein the im provement comprises the provision of:
means responsive to a predetermined flow rate of gas through said conduit means to said patient supply tap during an expiration phase for producing a control signal to actuate said control means, and pressure maintenance apparatus for said conduit means, said apparatus comprising a first plenum maintained at a predetermined pressure level, a second plenum in gas flow communication with said conduit means through said outlet port, check valve means enabling a unidirectional gas flow from the second plenum to the first plenum, and a bleeder conduit connected in parallel with said check valve means between said first and second plenums, said second plenum having a pressure during expiration phases determined by the pressure in said conduit means, said bleeder conduit including a gas flow restriction valve capable of being set to restrict the flow of gas between said plenums to a level no greater than the expected voluntary inhalation flow rate produced by a patient.
9. A respirator system for assisting a patients breathing during alternate inhalation and expiration phases, said system including gas conduit means having an inlet port, an outlet port, and a patient supply tap intermediate said inlet and outlet ports, recyclable means for charging gas into said inlet port during inhalation phases for delivery to a patient, a control means for actuating said charging means, first valve means adapted to block an outward flow of gas through said inlet port during expiration phases, and second valve means adapted to block an inward flow of gas through said outlet port during inhalation phases, wherein the improvement comprises the provision of:
a first chamber, a second chamber surrounding said conduit means outlet port and communicating thercthrough with said conduit means when said second valve means is open, a check valve means enabling a unidirectional gas flow from the second to the first chamber, a bleeder conduit connected it parallel with said check valve means between said first and second chambers, said bleeder conduit including an adjustable gas flow restriction valve for controlling the gas flow rate therethrough, vent means communicating with said first chamber for venting expired air from the system, a venturi in gas flow communication with said first chamber, and jet means adapted to direct a sub stantially constant velocity gas jet through said venturi to said first chamber. thereby maintaining the pressure in said first chamber at a substantially constant level.
10. The respirator system of claim 9, and further including a pressure differential sensor means operably connected to sense pressure differences between said first and second plenums and to produce a control signal for actuation of the control means in response to the sensed pressure differential exceeding a predeter mined amount.
11. The respirator system of claim 9, and further including a third chamber interposed between said jet means and said venturi, said third chamber including longitudinally opposed walls having ports therein enabling the gas jet to pass through the chamber, and at least one outlet orifice in a transverse wall of said third chamber providing a vent for expired gas transmitted through said check valve means.
12. The respirator of claim 9, wherein said second valve means comprises the combination of a diaphragm and means for releasably closing said diaphragm over said conduit means outlet port, said diaphragm forming a wall of said second chamber.
13. A method of operating a respirator system of the type which includes gas conduit means having an inlet port, an outlet port, and a patient supply tap intermediate said inlet and outlet ports, recyclable means for charging gas inwardly into said inlet port during inhalation phases for delivery to a patient, a control means for actuating said charging means, first valve means adapted to block an outflow of gas through said inlet port during expiration phases, and second valve means adapted t) block an inward flow of gas through said outlet port during inhalation phases, said method comprising:
sensing the flow rate of gas toward a patient through said conduit means during expiratory phases when the inlet port is blocked by said first valve means,
supplying gas to said conduit means during expiratory phases to compensate for gas leaks from the patient supply tap,
limiting the compensating gas flow to a rate no greater than the patients expected voluntary inhalation flow rate, and
through the outlet port thereof, and the gas flow rate to the patient is sensed by sensing the gas flow rate from the plenum to the conduit means.
15. The method of claim 14, wherein said compensating gas flow is limited by restricting the gas flow from the plenum to the conduit means, and the rate of said restricted gas flow is sensed by sensing the pressure differential between said plenum and conduit means.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2121311 *||Apr 1, 1935||Jun 21, 1938||Gasaccumulator Svenska Ab||Respiration apparatus|
|US3046979 *||Dec 5, 1958||Jul 31, 1962||Air Shields||Lung ventilators and control mechanism therefor|
|US3741208 *||Feb 23, 1971||Jun 26, 1973||Ingelstedt S||Lung ventilator|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3981301 *||Jun 26, 1975||Sep 21, 1976||Dragerwerk Aktiengesellschaft||Pneumatically controlled respiration device|
|US4020834 *||May 16, 1975||May 3, 1977||Bird F M||Respirator and method|
|US4060078 *||Aug 18, 1975||Nov 29, 1977||Bird F M||Ventilator and method|
|US4082093 *||Apr 27, 1977||Apr 4, 1978||Bourns, Inc.||Compensator valve|
|US4141356 *||Nov 18, 1977||Feb 27, 1979||Bourns, Inc.||Respirator system and method|
|US4318399 *||Nov 28, 1979||Mar 9, 1982||Aga Aktiebolag||Respirator apparatus|
|US4417573 *||Jul 2, 1981||Nov 29, 1983||Bear Medical Systems, Inc.||Patient adaptor for medical ventilator|
|US4459982 *||Sep 13, 1982||Jul 17, 1984||Bear Medical Systems, Inc.||Servo-controlled demand regulator for respiratory ventilator|
|US4527557 *||Nov 1, 1984||Jul 9, 1985||Bear Medical Systems, Inc.||Medical ventilator system|
|US4770654 *||Aug 5, 1987||Sep 13, 1988||Alcon Laboratories Inc.||Multimedia apparatus for driving powered surgical instruments|
|US4813409 *||Sep 27, 1985||Mar 21, 1989||Aaron Ismach||Ventilator system having improved means for assisting and controlling a patient's breathing|
|US4838257 *||Jul 17, 1987||Jun 13, 1989||Hatch Guy M||Ventilator|
|US4838281 *||Oct 13, 1987||Jun 13, 1989||Alcon Laboratories, Inc.||Linear suction control system|
|US4883051 *||Feb 18, 1988||Nov 28, 1989||Summa Vest, Inc.||Disposable breathing system and components|
|US5544674 *||Jul 14, 1995||Aug 13, 1996||Infrasonics, Inc.||Gas mixing apparatus for respirator|
|US5671767 *||Jun 26, 1996||Sep 30, 1997||Infrasonics, Inc.||Gas mixing apparatus for respirator|
|US5833643 *||Nov 18, 1997||Nov 10, 1998||Scieran Technologies, Inc.||Apparatus for performing ophthalmic procedures|
|US5857458 *||Sep 26, 1997||Jan 12, 1999||Ohmeda Inc.||Automatic bellows refill|
|US6258111||Aug 5, 1999||Jul 10, 2001||Scieran Technologies, Inc.||Apparatus and method for performing ophthalmic procedures|
|US6358260||Apr 20, 1998||Mar 19, 2002||Med-Logics, Inc.||Automatic corneal shaper with two separate drive mechanisms|
|US6425905||Nov 29, 2000||Jul 30, 2002||Med-Logics, Inc.||Method and apparatus for facilitating removal of a corneal graft|
|US6428508||Feb 1, 2000||Aug 6, 2002||Enlighten Technologies, Inc.||Pulsed vacuum cataract removal system|
|US6520180 *||Nov 16, 2000||Feb 18, 2003||DRäGER MEDIZINTECHNIK GMBH||Device for measuring a breathing gas component in a breathing gas line|
|US6644313 *||Jan 25, 2002||Nov 11, 2003||Fisher & Paykel Healthcare Limited||Breathing assistance apparatus|
|US6663644||Jun 2, 2000||Dec 16, 2003||Med-Logics, Inc.||Cutting blade assembly for a microkeratome|
|US6699285||Feb 9, 2001||Mar 2, 2004||Scieran Technologies, Inc.||Eye endoplant for the reattachment of a retina|
|US6702832||Oct 15, 2002||Mar 9, 2004||Med Logics, Inc.||Medical device for cutting a cornea that has a vacuum ring with a slitted vacuum opening|
|US7311700||Nov 29, 2000||Dec 25, 2007||Med-Logics, Inc.||LASIK laminar flow system|
|US7661428 *||Sep 8, 2005||Feb 16, 2010||Resmed Limited||Determination of leak and respiratory airflow|
|US8136527||Mar 13, 2008||Mar 20, 2012||Breathe Technologies, Inc.||Method and device for non-invasive ventilation with nasal interface|
|US8230857 *||Nov 9, 2005||Jul 31, 2012||Ric Investments, Llc.||Expiratory pressure regulation in a ventilator|
|US8381729||Aug 3, 2007||Feb 26, 2013||Breathe Technologies, Inc.||Methods and devices for minimally invasive respiratory support|
|US8396232||Jul 25, 2007||Mar 12, 2013||Novartis Ag||Surgical console operable to playback multimedia content|
|US8418694||Apr 30, 2010||Apr 16, 2013||Breathe Technologies, Inc.||Systems, methods and apparatus for respiratory support of a patient|
|US8528555 *||Nov 17, 2009||Sep 10, 2013||B/E Aerospace Systems Gmbh||Cockpit oxygen supply device|
|US8567399||Sep 26, 2008||Oct 29, 2013||Breathe Technologies, Inc.||Methods and devices for providing inspiratory and expiratory flow relief during ventilation therapy|
|US8573219||Dec 9, 2011||Nov 5, 2013||Breathe Technologies, Inc.||Method and device for non-invasive ventilation with nasal interface|
|US8677999||Aug 21, 2009||Mar 25, 2014||Breathe Technologies, Inc.||Methods and devices for providing mechanical ventilation with an open airway interface|
|US8770193||Apr 17, 2009||Jul 8, 2014||Breathe Technologies, Inc.||Methods and devices for sensing respiration and controlling ventilator functions|
|US8776793||Apr 17, 2009||Jul 15, 2014||Breathe Technologies, Inc.||Methods and devices for sensing respiration and controlling ventilator functions|
|US8844526||Mar 30, 2012||Sep 30, 2014||Covidien Lp||Methods and systems for triggering with unknown base flow|
|US8925545||Sep 26, 2008||Jan 6, 2015||Breathe Technologies, Inc.||Methods and devices for treating sleep apnea|
|US8939152||Sep 30, 2011||Jan 27, 2015||Breathe Technologies, Inc.||Methods, systems and devices for humidifying a respiratory tract|
|US8955518||Feb 3, 2012||Feb 17, 2015||Breathe Technologies, Inc.||Methods, systems and devices for improving ventilation in a lung area|
|US8985099||Feb 17, 2012||Mar 24, 2015||Breathe Technologies, Inc.||Tracheostoma spacer, tracheotomy method, and device for inserting a tracheostoma spacer|
|US9132250||Sep 3, 2010||Sep 15, 2015||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|
|US9180270||Apr 2, 2010||Nov 10, 2015||Breathe Technologies, Inc.||Methods, systems and devices for non-invasive open ventilation with gas delivery nozzles within an outer tube|
|US9227034||Apr 2, 2010||Jan 5, 2016||Beathe Technologies, Inc.||Methods, systems and devices for non-invasive open ventilation for treating airway obstructions|
|US9358358||Oct 29, 2013||Jun 7, 2016||Breathe Technologies, Inc.||Methods, systems and devices for humidifying a respiratory tract|
|US9364624||Dec 7, 2011||Jun 14, 2016||Covidien Lp||Methods and systems for adaptive base flow|
|US9498589||Dec 31, 2011||Nov 22, 2016||Covidien Lp||Methods and systems for adaptive base flow and leak compensation|
|US9649458||Oct 24, 2012||May 16, 2017||Covidien Lp||Breathing assistance system with multiple pressure sensors|
|US9675774||Apr 2, 2010||Jun 13, 2017||Breathe Technologies, Inc.||Methods, systems and devices for non-invasive open ventilation with gas delivery nozzles in free space|
|US9808591||Aug 15, 2014||Nov 7, 2017||Covidien Lp||Methods and systems for breath delivery synchronization|
|US20060005835 *||Sep 8, 2005||Jan 12, 2006||Michael Berthon-Jones||Determination of leak and respiratory airflow|
|US20070227541 *||Mar 28, 2007||Oct 4, 2007||Erik Van den Akker||Hyperoxic breathing system|
|US20080027574 *||Jul 25, 2007||Jan 31, 2008||Thomas Roger D||Surgical console operable to playback multimedia content|
|US20080085499 *||Oct 4, 2007||Apr 10, 2008||Christopher Horvath||Surgical console operable to simulate surgical procedures|
|US20080168989 *||Nov 9, 2005||Jul 17, 2008||Goran Cewers||Expiratory Pressure Regulation in a Ventilator|
|US20100071693 *||Aug 21, 2009||Mar 25, 2010||Breathe Technologies||Methods and devices for providing mechanical ventilation with an open airway interface|
|US20100122700 *||Nov 17, 2009||May 20, 2010||Conrad Ruediger||Cockpit oxygen supply device|
|US20120060839 *||May 11, 2010||Mar 15, 2012||Koninklijke Philips Electronics N.V.||System and method for controlling leakage of a circuit delivering a pressurized flow of breathable gas to a subject|
|CN102448530A *||May 11, 2010||May 9, 2012||皇家飞利浦电子股份有限公司||System and method for controlling leakage of a circuit delivering a pressurized flow of breathable gas to a subject|
|CN102448530B *||May 11, 2010||Sep 23, 2015||皇家飞利浦电子股份有限公司||用于控制向对象输送加压可呼吸气体流的线路的泄漏的系统和方法|
|DE4432219C1 *||Sep 10, 1994||Apr 11, 1996||Draegerwerk Ag||Automatic breathing system for patients|
|EP0243484A1 *||Oct 24, 1986||Nov 4, 1987||Vital Signals, Inc.||Method/apparatus for monitoring infants on assisted ventilation|
|EP0243484A4 *||Oct 24, 1986||Jan 11, 1988||Karl Frederick Schulze Jr||Method/apparatus for monitoring infants on assisted ventilation.|
|WO1992011054A1 *||Jun 7, 1991||Jul 9, 1992||Puritan-Bennett Corporation||Inspiratory airway pressure system|
|U.S. Classification||128/204.25, 128/205.13, 128/204.26|
|International Classification||A61M16/20, A61M16/00|
|Cooperative Classification||A61M16/00, A61M2016/206, A61M2016/0021|
|Oct 5, 1981||AS||Assignment|
Owner name: BEAR MEDICAL SYSTEMS, INC.,
Free format text: CHANGE OF NAME;ASSIGNOR:BOURNS MEDICAL SYSTEMS, INC.;REEL/FRAME:003915/0722
Effective date: 19810915
Owner name: BEAR MEDICAL SYSTEMS, INC.,, STATELESS
|Jun 5, 1981||AS||Assignment|
Owner name: BOURNS MEDICAL SYSTEMS, INC., A CORP. OF CA.
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST.;ASSIGNOR:BOURNS MEDICAL SYSTEMS, INC., A CORP. OF UTAH;REEL/FRAME:003860/0419
Effective date: 19810519