US3923056A - Compliance compensation for electronically controlled volume respirator systems - Google Patents
Compliance compensation for electronically controlled volume respirator systems Download PDFInfo
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- US3923056A US3923056A US480799A US48079974A US3923056A US 3923056 A US3923056 A US 3923056A US 480799 A US480799 A US 480799A US 48079974 A US48079974 A US 48079974A US 3923056 A US3923056 A US 3923056A
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
- A61M16/022—Control means therefor
- A61M16/024—Control means therefor including calculation means, e.g. using a processor
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
- A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
- A61M2016/0039—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the inspiratory circuit
Definitions
- the [58] 5 145 6 signal is then used to compensate a volume cycled 7 id control signal for the volume of gas required to fill the interconnecting hoses and equipment between the vol- [56] References Cited ume measuring apparatus and the patient interface to assure that the prescribed volume of gas is delivered UNITED STATES PATENTS to the patient. 3,033,195 5/1962 Gilroy et a1 128/D1G. 17 3,633,576 1/1972 Gorsuch 128/145.8 13 Claims, 1 Drawing Figure +V VOSLEJ1ME 18 19 5 ,4 25
- the present invention relates to respirators and, more particularly, to a control system for a fixed volume delivery respirator.
- Forced breathing respirators are generally either of a type for providing a breathable gas to a patient at a prescribed pressure or of a type for providing a prescribed volume of breathable gas to a patient. ,These types of respirators are referred to respectively as pressurecycled and volume-cycled.
- a third type. of respirator is a time-cycled respirator in which breathable gas is made available to a patient at timed intervals.
- the volume-cycled is preferable for long-term patient ventilation since physiological changes in a patient require frequent adjustment of the pressure-cycled and time-cycled types of respirators.
- volume cycling is advantageous because a predetermined volume of gas is delivered to a patient regardless of any change in compliance of the patient.
- any change in compliance of the interconnecting hoses and equipment between the patient and the gas supply will result in a change in the volume of gas delivered to the patient.
- compliance with respect to the interconnecting hoses is defined as the change in the volume of gas in the hoses with respect to the change in pressure across the hoses, it can be seen that the volume of gas required to fill the hoses will vary with temperature and pressure thus resulting in a change in compliance. Even with a constant temperature, the volume of gas required to fill the hoses will vary as patient resistance varies and will change the amount of gas which is actually delivered to the patient. Obviously as the hose length increases the change in the volume of gas delivered to the patient increases and such change may reach a point where the patients life is threatened by the change, particularly where the change is such as to significantly reduce the volume of gas delivered.
- a volumecycled respirator of the type including a gas source, an inhale valve, a flow sensor and interconnecting hoses and further including control apparatus responsive to the flow sensor for controlling the inhale valve, is provided with pressure responsive apparatus connected to monitor the gas pressure developed at the patient interface.
- the pressure responsive apparatus is conected to adjust the control apparatus to correct for changes in pressure such that the desired volume of gas is delivered to the patient.
- the pressure responsive apparatus includes a calibrating adjustment which allows initial calibration of the volume-cycled controlled apparatus to compensate for the volume of gas required to fill the interconnecting hoses and equipment.
- FIG. 1 of the accompanying drawing showing a block diagram of a volume-cycled respirator control system incorporating a pressure responsive apparatus in accordance with the present invention.
- the respirator includes a pressurized source 10 for supplying a breathable gas through a passageway 11 to an inhale valve 12 and from inhale valve 12 through a passageway 13 to a flow sensor 14. From flow sensor 14, which provides a signal representative of the gas flow therethrough, the gas passes through a flexible interconnecting hose 15 to a patient indicated generally at 16.
- interconnecting hose 15 is formed generally in a Y configuration with one arm of the Y connected to receive a gas from flow sensor 14 during an inhalation phase and the other arm of the Y connected to expel air through an exhale valve 17 to atmosphere during an exhalation phase.
- Check valves may be incorporated in both the inhale and exhale portions of the respirator, and other controls such as, e.g., pattern or flow rate controls may also be incorporated in the inhalation passageway of the respirator intermediate the gas source and the patient, all of the thus far mentioned elements being well known in the art.
- a control system connected to respond to an electrical signal from flow sensor 14, which signal is representative of the mass flow of gas per unit time passing through flow sensor 14, for controlling the operation of inhale and exhale valves 12 and 17.
- the signal from flow sensor 14 is directed into a linearizer 18 of a type well known in the art which converts the signal from flow sensor 14 to a voltage signal proportional to flow rate.
- the voltage signal or flow rate signal from linearizer 18 is supplied to an integrator 19 also of a type well known in the art which integrates the flow rate signal.
- the amplitude of the output signal developed by flow integrator 19 is proportional to the volume of gas which has passed through flow sensor 14.
- the signal from a flow integrator such as flow integrator 19 would be compared to a volume set signal and when the two were equal would be utilized to close off an inhale valve and open an exhale valve on the assumption that the volume of air flowing through the flow sensor represented a constant volume of air being delivered to the patient under all given sets of temperature, pressure, and patient resistance.
- the output signal from flow integrator 19 is combined with a signal generated by a pressure responsive circuit to produce a resultant signal which is proportional to the actual amount of gas delivered to the patient.
- the pressure responsive circuit comprises a pressure transducer 20 and a pressure amplifier 21.
- Pressure transducer 20 is connected to monitor the gas pressure in interconnecting hose 15 and to provide an output signal to amplifier 21 which signal is proportional to the pressure of the gas in hose 15.
- Amplifier 21 includes a gain adjust 22 which provides calibration adjustment. Since hose 15 is of a semi-rigid quality and is not conducive to stretch, its geometric volume, i.e., length of hose multiplied by cross-sectional area, is substantially constant.
- the output signal developed by amplifier 21 is applied to a first input terminal of a differential amplifier 23 which differential amplifier also includes a second input terminal connected to receive the output signal from flow integrator 19.
- the output signal from differential amplifier 23 is applied to a first input terminal of a threshold detector 24.
- a second input terminal of threshold detector 24 is connected to receive a voltage from a volume set control 25 which voltage is proportional to the desired volume of gas to be supplied to patient 16.
- Threshold detector 24 is connected to supply control signals to inhale valve 12 and exhale valve 17 for controlling respectively the inhalation and exhalation phases of the respiration cycle of patient 16.
- the system is initially calibrated by energizing source and setting control 25 to cause threshold detector 24 to provide a signal to open inhale valve 12 and close exhale valve 17 such that a flow of gas is supplied to interconnecting hose 15.
- threshold detector 24 At this time the end of hose which would normally be connected to a patient is blocked off, e.g., by placing ones hand over the end of the hose, and hose 15 is allowed to be pressurized to the full pressure of source 10.
- the amplified signal from flow sensor 14 as integrated by integrator 19 will represent the amount of gas necessary to fill the volume of interconnecting hose 15.
- the output signal from pressure transducer 20 as amplified by pressure amplifier 21 will represent the pressure of the gas and thus be proportional to the volume of the gas in hose 15.
- a volt meter 26 is connected to monitor the amplitude of the signal produced by differential amplifier 23 as a result of the subtraction of the signals from integrator 19 and amplifier 21. Gain adjust 22 is then adjusted until the amplitude of the output signal from differential amplifier 23 is zero. A repeated series of steps of alternately blocking the hose and adjusting gain adjust 22 for calibration will result in zero reading of volt meter 26 when the input to the differential amplifier 23 from flow integrator 19 is equal to the input signal from pressure amplifier 21. At this point the volume of air which is required to fill the hoses has been compensated for. Any subsequent compliance change will result in a change of the output signal from transducer 20 in a direction to adjust the volume of gas supplied to the hoses 15 to assure that the prescribed volume is delivered to patient 16.
- the output signal developed by differential amplifier 23 will be directly proportional to the volume of air which is actually received by the patient independently of the interconnecting hoses.
- This output signal is then compared in threshold detector 24 with the volume set signal developed from set control 25.
- threshold detector 24 produces a signal which is applied to inhale valve 12 to terminate the inhalation cycle and to exhale valve 17 to initiate the exhalation cycle.
- suitable circuitry (not shown) is normally provided to control the duration of the exhalation cycle and to provide a reset signal to integrator 19 to initiate a new inhalation cycle.
- the present invention provides a respirator in which the volume of gas actually delivered to the patient is accurately determined and may be compensated for by a pressure transducer to assure that the prescribed volume is applied to the patient regardless of interconnecting hose or equipment compliance or patient compliance.
- a respirator including an interconnecting hose assembly adapted to be connected to a patient and connected to an inhalation passageway and to an exhalation passageway and further including a pressurized gas source connected to said inhalation passageway and a flow control valve and flow rate sensor connected in said inhalation passageway intermediate said source and said interconnecting hose, a flow control valve in said exhalation passageway and control means responsive to said flow rate sensor to control operation of said flow control valves, the improvement comprising:
- pressure responsive means connected to said interconnecting hose assembly for developing a first signal representative of a gas pressure in said interconnecting hose assembly, means for supplying said first signal to said control means for modifying the operation of said control means in proportion to gas pressure in said interconnecting hose assembly;
- an integrating circuit means connected to said flow rate sensor for developing a second signal proportional to a volume of gas passing through said flow sensor, means for supplying said second signal to said control means for controlling the operation of said control means in response to said volume of gas flowing through said flow sensor, wherein said control means responds to said second signal by controlling the operation of said flow control valves.
- said pressure responsive means includes:
- a pressure transducer connected to said interconnecting hose assembly for producing said first sig- 6 proportional to said prescribed volume of gas for controlling said flow control valves.
Abstract
A volume-cycled respirator for delivering a prescribed volume of gas to a patient utilizing pressure responsive apparatus to monitor the gas pressure developed at the patient interface. The apparatus produces a signal proportional to gas pressure and includes a variable gain amplifier to proportion the signal to volume. The signal is then used to compensate a volume cycled control signal for the volume of gas required to fill the interconnecting hoses and equipment between the volume measuring apparatus and the patient interface to assure that the prescribed volume of gas is delivered to the patient.
Description
United States Patent Bingmann et a1. Dec. 2, 1975 COMPLIANCE COMPENSATION FOR 3,677,092 7/1972 Gaurino 73/194 F ELECTRONICALLY CONTROLLED 3,729,000 4/1973 Bell 128/1456 3,768,468 10/1973 Cox 128/1458 VOLUME RESPIRATOR SYSTEMS 3,834,381 9/1974 Peterson 128/145.6 [75] Inventors: Richard Bingmann, Audobon;
Frank P west Chester; Primary ExaminerRobert W. Michell 333 l hN li r'g Assistant ExaminerLee S. Cohen 1 a e p 1a, a 0 a.
[73] Assignee: gist-rill Iilectrlc Company, New ABSTRACT [22] Filed June 19 1974 A volume-cycled respirator for delivering a prescribed volume of gas to a patient utilizing pressure responsive [21] Appl. No.: 480,799 apparatus to monitor the gas pressure developed at the patient interface. The apparatus produces a signal [52] U 8 Cl 128/145 128/DIG, 17 proportional to gas pressure and includes a variable [51] 1 A61M 16/00 gain amplifier to proportion the signal to volume. The [58] 5 145 6 signal is then used to compensate a volume cycled 7 id control signal for the volume of gas required to fill the interconnecting hoses and equipment between the vol- [56] References Cited ume measuring apparatus and the patient interface to assure that the prescribed volume of gas is delivered UNITED STATES PATENTS to the patient. 3,033,195 5/1962 Gilroy et a1 128/D1G. 17 3,633,576 1/1972 Gorsuch 128/145.8 13 Claims, 1 Drawing Figure +V VOSLEJ1ME 18 19 5 ,4 25
FLOW DIFE THRESHOLD L'NEAR'ZER INTEGRATOR AMPL DETECTOR a CALIBRATION 22 24 .ADJUST. 23 VOLTMETER AMPLIFIER 26 K (PRESSURE) 14 "l INHALE FLOW I VALVE r SENSOR l2 PRESSURE SOURCE ,t/IO l7 EXHALE VALVE A M PRESSURE T TRANSDUCER FIG US. Patent Dec.2, 1975 3,923,056
+v VOLUME '9 SET FLOW DIFE THRESHOLD '1 Z CALIBRATION 22 23 24 ADJUST VOLTMETER v AMPLIFIER 26 K (PRESSURE) I4 "1 INHALE FLOW VALVE r SENSOR l2 PRESSURE SOURCE fl/lo I7 EXHALE .S, VALVE PRESSURE M TRANSDUCER COMPLIANCE COMPENSATION FOR ELECTRONICALLY CONTROLLED VOLUME RESPIRATOR SYSTEMS The invention herein described was made under a contract with the Department of the Navy, Office of Naval Research.
BACKGROUND OF THE INVENTION The present invention relates to respirators and, more particularly, to a control system for a fixed volume delivery respirator.
Forced breathing respirators are generally either of a type for providing a breathable gas to a patient at a prescribed pressure or of a type for providing a prescribed volume of breathable gas to a patient. ,These types of respirators are referred to respectively as pressurecycled and volume-cycled. A third type. of respirator is a time-cycled respirator in which breathable gas is made available to a patient at timed intervals. Of the foregoing three types, the volume-cycled is preferable for long-term patient ventilation since physiological changes in a patient require frequent adjustment of the pressure-cycled and time-cycled types of respirators.
Volume cycling is advantageous because a predetermined volume of gas is delivered to a patient regardless of any change in compliance of the patient. However, any change in compliance of the interconnecting hoses and equipment between the patient and the gas supply will result in a change in the volume of gas delivered to the patient. Since compliance with respect to the interconnecting hoses is defined as the change in the volume of gas in the hoses with respect to the change in pressure across the hoses, it can be seen that the volume of gas required to fill the hoses will vary with temperature and pressure thus resulting in a change in compliance. Even with a constant temperature, the volume of gas required to fill the hoses will vary as patient resistance varies and will change the amount of gas which is actually delivered to the patient. Obviously as the hose length increases the change in the volume of gas delivered to the patient increases and such change may reach a point where the patients life is threatened by the change, particularly where the change is such as to significantly reduce the volume of gas delivered.
Accordingly, it is an object of the present invention to provide a volume-cycled respirator control system which can be calibrated to deliver a desired volume of breathable gas to a patient.
It is a further object of the present invention to provide a volume-cycled respirator control system which automatically compensates for changes in compliance of interconnecting hoses and equipment.
It is another object of the present invention to provide a volume-cycled respirator control system which automatically adjusts the volume of gas applied to the interconnecting hoses and equipment to assure that the desired volume of gas is delivered to the patient.
SUMMARY OF THE INVENTION In accordance with the present invention, a volumecycled respirator of the type including a gas source, an inhale valve, a flow sensor and interconnecting hoses and further including control apparatus responsive to the flow sensor for controlling the inhale valve, is provided with pressure responsive apparatus connected to monitor the gas pressure developed at the patient interface. The pressure responsive apparatus is conected to adjust the control apparatus to correct for changes in pressure such that the desired volume of gas is delivered to the patient. The pressure responsive apparatus includes a calibrating adjustment which allows initial calibration of the volume-cycled controlled apparatus to compensate for the volume of gas required to fill the interconnecting hoses and equipment.
BRIEF DESCRIPTION OF THE DRAWING For a better understanding of the invention, reference may be had to FIG. 1 of the accompanying drawing showing a block diagram of a volume-cycled respirator control system incorporating a pressure responsive apparatus in accordance with the present invention.
DETAILED DESCRIPTION Referring now to the drawing, there is shown a simplified representation of an electronically controlled volume-cycled respirator in which those elements not essential to an understanding of the present invention have been omitted. The respirator includes a pressurized source 10 for supplying a breathable gas through a passageway 11 to an inhale valve 12 and from inhale valve 12 through a passageway 13 to a flow sensor 14. From flow sensor 14, which provides a signal representative of the gas flow therethrough, the gas passes through a flexible interconnecting hose 15 to a patient indicated generally at 16. As is shown, interconnecting hose 15 is formed generally in a Y configuration with one arm of the Y connected to receive a gas from flow sensor 14 during an inhalation phase and the other arm of the Y connected to expel air through an exhale valve 17 to atmosphere during an exhalation phase. Check valves may be incorporated in both the inhale and exhale portions of the respirator, and other controls such as, e.g., pattern or flow rate controls may also be incorporated in the inhalation passageway of the respirator intermediate the gas source and the patient, all of the thus far mentioned elements being well known in the art.
In order to control the opening and closing of the inhale and exhale valves 12 and 17, respectively, to thereby provide a prescribed volume of gas to the patient 16, there is provided a control system connected to respond to an electrical signal from flow sensor 14, which signal is representative of the mass flow of gas per unit time passing through flow sensor 14, for controlling the operation of inhale and exhale valves 12 and 17. The signal from flow sensor 14 is directed into a linearizer 18 of a type well known in the art which converts the signal from flow sensor 14 to a voltage signal proportional to flow rate. The voltage signal or flow rate signal from linearizer 18 is supplied to an integrator 19 also of a type well known in the art which integrates the flow rate signal. Since the integral of flow rate is a volume equivalent, the amplitude of the output signal developed by flow integrator 19 is proportional to the volume of gas which has passed through flow sensor 14. In the prior art systems, the signal from a flow integrator such as flow integrator 19 would be compared to a volume set signal and when the two were equal would be utilized to close off an inhale valve and open an exhale valve on the assumption that the volume of air flowing through the flow sensor represented a constant volume of air being delivered to the patient under all given sets of temperature, pressure, and patient resistance.
In the present invention the output signal from flow integrator 19 is combined with a signal generated by a pressure responsive circuit to produce a resultant signal which is proportional to the actual amount of gas delivered to the patient. The pressure responsive circuit comprises a pressure transducer 20 and a pressure amplifier 21. Pressure transducer 20 is connected to monitor the gas pressure in interconnecting hose 15 and to provide an output signal to amplifier 21 which signal is proportional to the pressure of the gas in hose 15. Amplifier 21 includes a gain adjust 22 which provides calibration adjustment. Since hose 15 is of a semi-rigid quality and is not conducive to stretch, its geometric volume, i.e., length of hose multiplied by cross-sectional area, is substantially constant. Under such conditions and considering the small pressure range over which a gas is supplied to a patient, the well-known relationship of pressure being equal to a constant times volume is applicable. Therefore, a measurement of pressure in hose 15 will yield a signal directly proportional to the volume of gas in the hose.
The output signal developed by amplifier 21 is applied to a first input terminal of a differential amplifier 23 which differential amplifier also includes a second input terminal connected to receive the output signal from flow integrator 19. The output signal from differential amplifier 23 is applied to a first input terminal of a threshold detector 24. A second input terminal of threshold detector 24 is connected to receive a voltage from a volume set control 25 which voltage is proportional to the desired volume of gas to be supplied to patient 16. Threshold detector 24 is connected to supply control signals to inhale valve 12 and exhale valve 17 for controlling respectively the inhalation and exhalation phases of the respiration cycle of patient 16.
In operation, the system is initially calibrated by energizing source and setting control 25 to cause threshold detector 24 to provide a signal to open inhale valve 12 and close exhale valve 17 such that a flow of gas is supplied to interconnecting hose 15. At this time the end of hose which would normally be connected to a patient is blocked off, e.g., by placing ones hand over the end of the hose, and hose 15 is allowed to be pressurized to the full pressure of source 10. The amplified signal from flow sensor 14 as integrated by integrator 19 will represent the amount of gas necessary to fill the volume of interconnecting hose 15. Likewise, the output signal from pressure transducer 20 as amplified by pressure amplifier 21 will represent the pressure of the gas and thus be proportional to the volume of the gas in hose 15. These two signals are combined in subtractive relationship in differential amplifier 23.
A volt meter 26 is connected to monitor the amplitude of the signal produced by differential amplifier 23 as a result of the subtraction of the signals from integrator 19 and amplifier 21. Gain adjust 22 is then adjusted until the amplitude of the output signal from differential amplifier 23 is zero. A repeated series of steps of alternately blocking the hose and adjusting gain adjust 22 for calibration will result in zero reading of volt meter 26 when the input to the differential amplifier 23 from flow integrator 19 is equal to the input signal from pressure amplifier 21. At this point the volume of air which is required to fill the hoses has been compensated for. Any subsequent compliance change will result in a change of the output signal from transducer 20 in a direction to adjust the volume of gas supplied to the hoses 15 to assure that the prescribed volume is delivered to patient 16. This means that when a patient is connected to the respirator, the output signal developed by differential amplifier 23 will be directly proportional to the volume of air which is actually received by the patient independently of the interconnecting hoses. This output signal is then compared in threshold detector 24 with the volume set signal developed from set control 25. When the amplitude of the signal from differential amplifier 23 indicates that the prescribed volume of gas has been delivered to patient 16, threshold detector 24 produces a signal which is applied to inhale valve 12 to terminate the inhalation cycle and to exhale valve 17 to initiate the exhalation cycle. It is noted that suitable circuitry (not shown) is normally provided to control the duration of the exhalation cycle and to provide a reset signal to integrator 19 to initiate a new inhalation cycle.
It will thus be seen that the present invention provides a respirator in which the volume of gas actually delivered to the patient is accurately determined and may be compensated for by a pressure transducer to assure that the prescribed volume is applied to the patient regardless of interconnecting hose or equipment compliance or patient compliance.
Although the invention has been described with respect to a single embodiment, it is intended that the appended claims not be limited to the specific embodiment of the invention described, but that they cover modifications falling within the spirit and scope of the claims.
What is new and desired to be secured by Letters Patent of the United States is:
1. In a respirator including an interconnecting hose assembly adapted to be connected to a patient and connected to an inhalation passageway and to an exhalation passageway and further including a pressurized gas source connected to said inhalation passageway and a flow control valve and flow rate sensor connected in said inhalation passageway intermediate said source and said interconnecting hose, a flow control valve in said exhalation passageway and control means responsive to said flow rate sensor to control operation of said flow control valves, the improvement comprising:
pressure responsive means connected to said interconnecting hose assembly for developing a first signal representative of a gas pressure in said interconnecting hose assembly, means for supplying said first signal to said control means for modifying the operation of said control means in proportion to gas pressure in said interconnecting hose assembly; and
an integrating circuit means connected to said flow rate sensor for developing a second signal proportional to a volume of gas passing through said flow sensor, means for supplying said second signal to said control means for controlling the operation of said control means in response to said volume of gas flowing through said flow sensor, wherein said control means responds to said second signal by controlling the operation of said flow control valves.
2. The apparatus as defined in claim 1 wherein said pressure responsive means includes:
a pressure transducer connected to said interconnecting hose assembly for producing said first sig- 6 proportional to said prescribed volume of gas for controlling said flow control valves. 3. The apparatus as defined in claim 2 and including a variable gain amplifier connected intermediate said pressure transducer and said differential amplifier means for adjusting the amplitude of said first signal to proportion said first signal to a volume signal.
Claims (3)
1. In a respirator including an interconnecting hose assembly adapted to be connected to a patient and connected to an inhalation passageway and to an exhalation passageway and further including a pressurized gas source connected to said inhalation passageway and a flow control valve and flow rate sensor connected in said inhalation passageway intermediate said source and said interconnecting hose, a flow control valve in said exhalation passageway and control means responsive to said flow rate sensor to control operation of said flow control valves, the improvement comprising: pressure responsive means connected to said interconnecting hose assembly for developing a first signal representative of a gas pressure in said interconnecting hose assembly, means for supplying said first signal to said control means for modifying the operation of said control means in proportion to gas pressure in said interconnecting hose assembly; and an integrating circuit means connected to said flow rate sensor for developing a second signal proportional to a volume of gas passing through said flow sensor, means for supplying said second signal to said control means for controlling the operation of said control means in response to said volume of gas flowing through said flow sensor, wherein said control means responds to said second signal by controlling the operation of said flow control valves.
2. The apparatus as defined in claim 1 wherein said pressure responsive means includes: a pressure transducer connected to said interconnecting hose assembly for producing said first signal representative of said gas pressure in said hose assembly; differential amplifier means for combining said first signal with said second signal representative of said volume of gas flowing into said hose assembly to produce a third signal representative of a difference therebetween; and means for comparing said third signal to a voltage proportional to said prescribed volume of gas for controlling said flow control valves.
3. The apparatus as defined in claim 2 and including a variable gain amplifier connected intermediate said pressure transducer and said differential amplifier means for adjusting the amplitude of said first signal to proportion said first signal to a volume signal.
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| US480799A US3923056A (en) | 1974-06-19 | 1974-06-19 | Compliance compensation for electronically controlled volume respirator systems |
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| US480799A US3923056A (en) | 1974-06-19 | 1974-06-19 | Compliance compensation for electronically controlled volume respirator systems |
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Cited By (43)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4031885A (en) * | 1975-10-15 | 1977-06-28 | Puritan-Bennett Corporation | Method and apparatus for determining patient lung pressure, compliance and resistance |
| US4121581A (en) * | 1976-11-01 | 1978-10-24 | Sandoz, Inc. | Patient ventilator monitor |
| US4421113A (en) * | 1980-06-18 | 1983-12-20 | Engstrom Medical Aktiebolag | Method and apparatus for controlling lung ventilators |
| EP0118850A2 (en) * | 1983-03-04 | 1984-09-19 | Polska Akademia Nauk Instytut Biocybernetyki i Inzynierii Biomedycznej | Apparatus for independent ventilation of two lungs with selective use of positive end-expiratory pressures |
| US4624251A (en) * | 1984-09-13 | 1986-11-25 | Riker Laboratories, Inc. | Apparatus for administering a nebulized substance |
| US4635627A (en) * | 1984-09-13 | 1987-01-13 | Riker Laboratories, Inc. | Apparatus and method |
| US4651729A (en) * | 1982-07-30 | 1987-03-24 | Rae Ronald D | Fluid flow regulator |
| US4819629A (en) * | 1986-10-28 | 1989-04-11 | Siemens Aktiengesellschaft | Method and apparatus for delivering aerosol to the airways and/or lungs of a patient |
| US4827964A (en) * | 1987-04-23 | 1989-05-09 | Mine Safety Appliances Company | System for metering of breathing gas for accommodation of breathing demand |
| US4957107A (en) * | 1988-05-10 | 1990-09-18 | Sipin Anatole J | Gas delivery means |
| US5048515A (en) * | 1988-11-15 | 1991-09-17 | Sanso David W | Respiratory gas supply apparatus and method |
| US5072728A (en) * | 1989-09-12 | 1991-12-17 | Dragerwerk Ag | Recirculating respirator |
| EP0560490A1 (en) * | 1992-02-12 | 1993-09-15 | Puritan-Bennett Corporation | System and method for controlling a periodically actuated ventilation flow system |
| US5331995A (en) * | 1992-07-17 | 1994-07-26 | Bear Medical Systems, Inc. | Flow control system for medical ventilator |
| US5345930A (en) * | 1992-02-10 | 1994-09-13 | National Research Council Canada Intellectual Property Services Office | Method and apparatus for assisting expulsional movement of pulmonary secretions via supramaximal flows |
| US5535737A (en) * | 1993-11-16 | 1996-07-16 | The Boc Group, Inc. | Anesthetic vaporizers |
| EP0742027A2 (en) * | 1995-05-12 | 1996-11-13 | Instrumentarium Oy | Arrangement for leak testing taking place in connection with a ventilator |
| US5794614A (en) * | 1989-05-19 | 1998-08-18 | Gruenke; Roger A. | Apparatus for compensating for flow and pressure variances in pneumatic circuits |
| US5797393A (en) * | 1995-05-05 | 1998-08-25 | Dragerwerk Aktiengesellschaft | Method for controlling the respirating phase in a ventilating apparatus |
| US5810002A (en) * | 1996-09-26 | 1998-09-22 | Dragerwerk Ag | Respirator |
| EP0965356A1 (en) * | 1998-06-15 | 1999-12-22 | Siemens-Elema AB | A method for determining the volume of a tubing system and a breathing apparatus system |
| US6041780A (en) * | 1995-06-07 | 2000-03-28 | Richard; Ron F. | Pressure control for constant minute volume |
| US6142150A (en) * | 1998-03-24 | 2000-11-07 | Nellcor Puritan-Bennett | Compliance compensation in volume control ventilator |
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| US20080264419A1 (en) * | 2007-04-26 | 2008-10-30 | Joseph Lomask | Integrated ventilator with calibration |
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| US9981096B2 (en) | 2013-03-13 | 2018-05-29 | Covidien Lp | Methods and systems for triggering with unknown inspiratory flow |
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| US10434270B2 (en) | 2011-12-27 | 2019-10-08 | Koninklijke Philips N.V. | Compensation of breath delivery |
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| US20030079750A1 (en) * | 1996-09-23 | 2003-05-01 | Michael Berthon-Jones | Assisted ventilation to match patient respiratory need |
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| EP0965356A1 (en) * | 1998-06-15 | 1999-12-22 | Siemens-Elema AB | A method for determining the volume of a tubing system and a breathing apparatus system |
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| EP1355689A4 (en) * | 2000-12-29 | 2007-08-08 | Resmed Ltd | Characterisation of mask systems |
| US8677997B2 (en) | 2000-12-29 | 2014-03-25 | Resmed Limited | Characterisation of mask systems |
| US20040074495A1 (en) * | 2000-12-29 | 2004-04-22 | Wickham Peter John Deacon | Characterisation of mask systems |
| US7987847B2 (en) | 2000-12-29 | 2011-08-02 | Resmed Limited | Characterisation of mask systems |
| US10252013B2 (en) | 2004-02-10 | 2019-04-09 | Lowenstein Medical Technology S.A. | Respiratory device and method for controlling a respiratory device |
| US11660411B2 (en) | 2004-02-10 | 2023-05-30 | Loewenstein Medical Technology S.A. | Respiratory device and method for controlling a respiratory device |
| US20110100365A1 (en) * | 2004-02-10 | 2011-05-05 | Wolfgang Wedler | Respiratory device and method for controlling a respiratory device |
| US20060037616A1 (en) * | 2004-08-17 | 2006-02-23 | Drager Medical Ag & Co. Kgaa | Process for the automatic recording of pressure-vs.-volume curves during artificial respiration |
| US7708015B2 (en) * | 2004-08-17 | 2010-05-04 | Dräger Medical AG & Co. KG | Process for the automatic recording of pressure-vs.-volume curves during artificial respiration |
| US7487773B2 (en) | 2004-09-24 | 2009-02-10 | Nellcor Puritan Bennett Llc | Gas flow control method in a blower based ventilation system |
| US20060065270A1 (en) * | 2004-09-24 | 2006-03-30 | Kun Li | Gas flow control method in a blower based ventilation system |
| FR2887777A1 (en) * | 2005-06-29 | 2007-01-05 | Taema Sa | Medical ventilator for e.g. administering gas to patient, has control unit with data storage and/or processing unit, estimating patient`s biomechanical condition based on gaseous circuit`s pressure, gas flow and preset compliance value |
| CN101365507B (en) * | 2005-10-11 | 2013-03-06 | 卡尔夫207有限公司 | System and method for circuit compliance compensated volume control in a patient respiratory ventilator |
| US20110214672A1 (en) * | 2005-11-09 | 2011-09-08 | Soliman Ihab S | System and method for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilator |
| US8453644B2 (en) | 2005-11-09 | 2013-06-04 | Carefusion 207, Inc. | System and method for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilator |
| US20070101992A1 (en) * | 2005-11-09 | 2007-05-10 | Viasys Manufacturing, Inc. | System and method for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilator |
| US7918223B2 (en) * | 2005-11-09 | 2011-04-05 | Carefusion 207, Inc. | System and method for circuit compliance compensated pressure-regulated volume control in a patient respiratory ventilator |
| US20080264419A1 (en) * | 2007-04-26 | 2008-10-30 | Joseph Lomask | Integrated ventilator with calibration |
| US8316849B2 (en) * | 2007-04-26 | 2012-11-27 | Buxco Electronics, Inc. | Integrated ventilator with calibration |
| US10434270B2 (en) | 2011-12-27 | 2019-10-08 | Koninklijke Philips N.V. | Compensation of breath delivery |
| US20140360497A1 (en) * | 2012-03-30 | 2014-12-11 | Covidien Lp | Methods and systems for triggering with unknown base flow |
| US10029057B2 (en) * | 2012-03-30 | 2018-07-24 | Covidien Lp | Methods and systems for triggering with unknown base flow |
| US9981096B2 (en) | 2013-03-13 | 2018-05-29 | Covidien Lp | Methods and systems for triggering with unknown inspiratory flow |
| CN104874065A (en) * | 2014-02-28 | 2015-09-02 | 北京谊安医疗系统股份有限公司 | Respirator and method of suppressing core jitter of inhalation valve of respirator |
| US9925346B2 (en) | 2015-01-20 | 2018-03-27 | Covidien Lp | Systems and methods for ventilation with unknown exhalation flow |
| CN109152899A (en) * | 2016-03-01 | 2019-01-04 | 万提诺瓦技术有限责任公司 | Method and apparatus for giving patient ventilating |
| US11918744B2 (en) * | 2016-11-04 | 2024-03-05 | Viomedex Limited | Therapy delivery device |
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