US3875626A - Device for measuring the tidal gas volume in a lung ventilator - Google Patents

Device for measuring the tidal gas volume in a lung ventilator Download PDF

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Publication number
US3875626A
US3875626A US423789A US42378973A US3875626A US 3875626 A US3875626 A US 3875626A US 423789 A US423789 A US 423789A US 42378973 A US42378973 A US 42378973A US 3875626 A US3875626 A US 3875626A
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Prior art keywords
compartment
gas flow
constant
gas
pressure
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US423789A
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English (en)
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Jan Tysk
Goran Sjoberg
Sven Olofsson
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Jungner Instrument AB
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Jungner Instrument AB
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/091—Measuring volume of inspired or expired gases, e.g. to determine lung capacity
    • A61B5/093—Measuring volume of inspired or expired gases, e.g. to determine lung capacity the gases being exhaled into, or inhaled from, an expansible chamber, e.g. bellows or expansible bag
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
    • G01F17/00—Methods or apparatus for determining the capacity of containers or cavities, or the volume of solid bodies

Definitions

  • ABSTRACT A device in a lung ventilator for measuring the tidal Apr. 8, 1975 volume for exhaled gas volume, comprising a rigid container divided in two separate compartments by a flexible, substantially freely movable, internal partition wall so that the sum of the volumes of the two compartments is always constant and independent of the position of the partition wall.
  • One compartment is connected to a conduit leading to the respiratory ways of the patient during the exhalation phase of the ventilation cycle of the ventilator so as to receive the gas being exhaled by the patient and to the ambient atmosphere during the inhalation phase of the ventilation cycle.
  • the other compartment in the container is connected to a device for injecting a predetermined constant gas flow into this other compartment.
  • the injection of this constant gas flow is started at the end of the exhalation phase of the ventilator, when the communication between the first compartment in the container and the conduit leading to the respiratory ways of the patient is interrupted, and is automatically interrupted when said first compartment has attained its smallest possible volume, that is when it has been emptied of all exhaled gas.
  • the device for injecting the constant gas flow in the second compartment of the container is preferably controlled from a pressure transducer sensing the gas pressure in said second compartment.
  • the duration of the constant gas flow injected in the second compartment of the container is measured; this duration being directly proportional to the gas volume exhaled by the patient during the preceding exhalation phase.
  • the invention relates to a device in lung ventilators for measuring the so called tidal volume, that is the gas volume exhaled by the patient.
  • the object of the invention is therefore to provide an improved device for measuring the exhaled gas volume in lung ventilators.
  • the invention provides a device for measuring the exhaled gas volume in a lung ventilator, which comprises a rigid container provided with an internal, freely movable partition wall dividing the interior of the container in first and second separate compartments in such a manner that the sum of the volumes of said first and second compartments remains constant and independent of the actual position of the partition wall and that any change in the position of the partition wall results in equally large but opposite changes in the volumes of said first and second compartments, valve means for putting said first compare ment in communication with a conduit leading to the respiratory ways of the patient during the exhalation phase of the ventilation cycle of the lung ventilator and in communication with the ambient atmosphere during the inhalation phase of the ventilation cycle, means for injecting a predetermined constant gas flow into said second compartment, means for activating said gas flow injecting means to start said constant gas flow when at the end of the exhalation phase the communication between said first compartment and said conduit leading to the respiratory ways of the patient is interrupted, pressure transducer means responsive to the gas pressure in said second compartment for initiating said gas flow injecting
  • the pres sure transducer means responsive to the gas pressure in the second compartment of the container are designed to produce an electric signal representing said gas pressure and the time measuring means are responsive to this electric signal so as to start the time measuring process in response to the pressure rise resulting from the starting of the constant gas flow and to interrupt the time measuring process in response to the pressure rise appearing when said second compartment of the container attains its maximum volume.
  • the device according to the invention has a comparatively simple structural design and is therefore inexpensive and reliable. Further, the device according to the invention makes it possible to measure large tidal volumes, as the expansible compartment, in which the exhaled gas is collected, is emptied positively during the following inhalation phase, and has at the same time a good accuracy also for small tidal volumes, as the volume measurement can be based on an electronic time measurement. Further, the accuracy of the device according to the invention is not dependent on any accurate tolerances in the design of the container and its internal partition wall or the accuracy of the movements of the partition wall as is the case in many prior art devices, where the measurement is based on observation of the movements of the partition wall.
  • FIG. 1 illustrates schematically a first embodiment of a device according to the invention
  • FIG. 2 illustrates schematically a second embodiment of a device according to the invention
  • FIG. 3 is a diagram illustrating the pressure as a function of time during the emptying of the inflatable compartment used for collecting the exhaled gas in the device illustrated in FIG. 2;
  • FIG. 4 is a diagram illustrating the time derivative of the pressure signal in FIGv 3.
  • FIGS. I and 2 electric signal connections are indicated by solid lines provided with arrows indicating the direction of signal transfer.
  • FIG. 1 as well as FIG. 2 only the device according to the invention is shown, whereas all other parts of the lung ventilator, with which the devices according to the invention is associated, are omitted, as these other parts of the lung ventilater can be of any conventional type already well known in the art.
  • the device according to the invention illustrated schematically and by way of example in FIG. 1 comprises a rigid container 1, the interior of which is divided in two separate compartments 2 and 3 by a flexible, substantially freely inflatable bag 4, which thus forms a partition wall between the two compartments 2 and 3. It is appreciated that the sum of the volumes of the two compartments 2 and 3 is always constant and that any change in the volume of one of these compartments results in an equally large but opposite change in the volume of the other compartment.
  • the compartment 3 inside the bag 4 can by means of a valve device 5 be put into communication alternatively with a pipe conduit 6 leading to the respiratory ways of the patient or with the ambient atmosphere.
  • a valve device 5 As schematically indicated with an electric signal connection 7. the valve device 5 is controlled from the control unit of the lung ventilator in such a manner that the interior 3 of the bag 4 communicates with the pipe conduit 6 leading to the respiratory ways of the patient dur ing the exhalation phase of the ventilation cycle of the ventilator. whereas it communicates with the ambient atmosphere during the inhalation phase of the ventilation cycle.
  • the compartment 2 in the container l outside the bag 4 can through a valve device 8 be connected either to a device 9 for injecting a predetermined, constant gas flow into the compartment 2 or to the ambient atmosphere.
  • the device 9 can he of any suitable conventional design, for instance consisting of a pressurized gas source with predetermined constant pressure and a restriction determining the rate of the gas flow.
  • the valve device 8 is normally in the position, in which the compartment 2 in the container 1 is communicating with the ambient atmosphere, but is operated from the control unit ofthe lung ventilator in such a manner that at the end of the exhalation phase of the ventilation cycle the valve device interrupts the communication between the ambient atmosphere and the compartment 2 and instead opens the communication between the compartment 2 and the device 9 so that a constant gas flow from the device 9 is injected into the compartment 2.
  • the valve device 8 is returned to its normal position in response to a control signal from a pressure transducer 10 connected to the compartment 2 in the container 1, as will be described more in detail in the following.
  • the device comprises a time measuring device 11. which is started by the control unit of the lung ventilator at the end of the exhalation phase ofa ventilation cycle and is stopped again in response to the sig nal from the pressure transducer 10 at the same time as the constant gas flow from the device 9 into the compartment 2 of the container is interrupted.
  • the device illustrated in FIG. 1 operates in the following manner.
  • the two valve devices 5 and 8 are in positions opposite to those illustrated in the drawing wherefore the compartment 3 inside the bag 4 communicates with the pipe conduit 6 leading to the respiratory ways of the patient. whereas the compartment 2 outside the bag 4 communicates with the ambient atmosphere.
  • the two valve devices 5 and 8 are returned in response to the control unit of the ventilator to the positions illustrated in the drawing, whereby the interior 3 of the bag 4 is put into direct communication with the ambient atmosphere, whereas the compartment 2 outside the bag 4 is connected to the device 9, which starts to inject a constant gas flow into the compartment 2.
  • the time measuring device 11 is also started. Under the effect of the constant gas flow injected into the compartment 2 outside the bag 4 from the device 9 the bag 4 is emptied through the valve device 5 to the ambient atmosphere.
  • the rate of emptying the bag 4 will be constant and directly proportional to the rate of the gas flow from the device 9, wherefore the time for a complete emptying of the bag 4, that is until the compartment 3 within the bag 4 attains its smallest possible volume, will be directly proportional to the gas volume exhaled by the patient during the preceding exhalation phase, as this gas volume was collected in the bag 4.
  • the pressure in the compartment 3 will rise steeply due to the gas flow from the device 9. This steep and large pressure rise is sensed by the pressure transducer 10, which produce's a corresponding output signal, which on the one hand stops the time measuring device ii and on the other hand returns the valve device 8 to its other position so that the gas flow from the device 9 into the compartment 2 of the container 1 is interrupted and the compartment 2 is instead put into communication with the ambient atmosphere.
  • the time interval measured by the time measuring device ll will be directly proportional to the gas volume which is expelled from the interior 3 of the bag 4 and thus to the gas volume exhaled by the patient during the preceding exhalation phase.
  • a direct measure of this gas volume is obtained by multiplying the time measured by the time measuring device 11 and the rate of the constant gas flow from the device 9.
  • FIG. 1 has obviously a gas consumption from the device 9 which is equal to the gas volume exhaled by the patient.
  • This comparatively large gas consumption may be a disadvantage, particularly if the lung ventilator is driven from its own compressor.
  • FIG. 2 in the drawings shows schematically a device according to the invention, which constitutes an improvement in this respect and which is also simplified in some other respects.
  • the device according to the invention shown in FIG. 2 comprises also a rigid container 12, the interior of which is divided in two separate compartments [3 and 14 by a flexible, substantially freely movable dia phragm 15, which can move between the two extreme positions indicated with dotted lines.
  • the compartment 14 can be put into communication with the pipe conduit 17 leading to the respiratory ways of the patient through a valve 16 operated from the control unit of the lung ventilator and with the ambient atmosphere through a biased check valve 18.
  • the valve 16 is operated from the control unit of the ventilator in such a manner that it is closed during the inhalation phase and open during the exhalation phase of the ventilation cycle of the ventilator. Consequently, the gas volume exhaledby the patient during the exhalation phase flows into the compartment 14 of the container 12 resulting in an increase of the volume of the compartment l4 and a corresponding reduction of the volume of the compartment 13.
  • the biassing of the check valve 18 is such that the valve does not open under the influence of the pressure arising in the compartment 14 during the exhalation phase but only for a predetermined higher pressure.
  • the compartment 13 in the container 12 communicates with the ambient atmosphere through an ejector device 19, which is connected to a device producing a drive gas flow for the ejector 19 having a predetermined constant flow rate and pressure, whereby the ejector device 19 will under the influence of this drive gas flow inject a predetermined constant gas flow into the compartment 13 of the container 12.
  • the major portion of this gas flow is of course taken from the am bient atmosphere.
  • the ejector device 19 it is possible to achieve that at least 90 percent of the gas flow injected into the compartment 13 is taken from the ambient atmosphere. It is appreciated that in the absence of a drive gas flow from the device 20 to the ejector device 19 the compartment 13 of the container 12 is communicating directly with the am bient atmosphere through the ejector device.
  • the device 20 can be of any suitable conventional type and for instance consist of a source of pressurized gas with predetermined constant pressure and a restriction for deter mining the rate of the gas flow; the drive gas flow to the ejector 19 being started and interrupted respectively by means of any suitable valve device.
  • the device 20 is started to supply the necessary drive gas flow to the ejector 19, whereby a constant gas flow is injected into the compartment 13 of the container 12, by actuation from the control unit of the ventilator at the end of the exhalation phase simultaneously with the closing of the valve 16.
  • the injection of the constant gas flow in the compartment 13 results in a very rapid increase of the pressure in the compartment 13 up to the opening pressure for the check valve 18, as shown at the time t, in the pressure diagram in FIG. 3.
  • This pressure rise is sensed by the pressure transducer 21 connected to the compartment 13.
  • the pressure signal from the pressure transducer 21 is preferably differentiated so that a corresponding signal pulse A is.produced. as shown in the diagram in FIG. 4. This signal pulse starts a time measuring device 22.
  • time interval At in FIGS. 3 and 4 as measured by the time measuring device 22 will be directly proportional to the gas volume expelled from the compartment 14 to the ambient atmosphere and thus also directly proportional to the gas volume exhaled by the patient during the preceding exhalation phase.
  • a device in a lung ventilator for measuring the gas volume exhaled by a patient comprising a rigid con tainer provided with an internal freely movable partition wall dividing the interior of the container into a first and a second compartment in such a way that the sum of the volumes of said first and second compartments is constant and independent of the position of said partition wall and any change of the position of said partition wall results in equally large but opposite changes in the volumes of said first and second compartments; valve means for putting said first compartment into communication with a gas conduit leading to the respiratory ways of the patient during the exhalation phase of the ventilation cycle of the ventilator and in communication with the ambient atmosphere during the inhalation phase of the ventilation cycle; means for producing a predetermined constant gas flow and in jecting this constant gas flow into said second compartment; means for activating said gas flow producing means to start the injection of said constant gas flow into said second compartment when at the end of the exhalation phase the communication between said first compartment and said conduit leading to the respiratory ways of the patient is interrupted; pressure trans ducer means responsive to the gas pressure
  • said pres sure transducer means provides an electric output sig nal representing the gas pressure in said second c0mpartment and said time measuring means is controlled by said electric output signal so as to start its time measuring process in response to the pressure rise caused by the starting of said constant gas flow and to interrupt its time measuring process in response to the pressure rise produced when said second compartment attains its maximum possible volume.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Pulmonology (AREA)
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  • Heart & Thoracic Surgery (AREA)
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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
US423789A 1972-12-12 1973-12-11 Device for measuring the tidal gas volume in a lung ventilator Expired - Lifetime US3875626A (en)

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SE7216188A SE380724B (sv) 1972-12-12 1972-12-12 Anordning vid en lungventilator for metning av den av patienten utandade gasvolymen

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DE (1) DE2361165A1 (enExample)
FR (1) FR2209926B1 (enExample)
GB (1) GB1451360A (enExample)
IT (1) IT1004043B (enExample)
SE (1) SE380724B (enExample)

Cited By (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4112931A (en) * 1977-01-05 1978-09-12 Cavitron Corporation Tidal volume display
US4233990A (en) * 1979-03-20 1980-11-18 Empire Plastics Manufacturing Inc. Volume and flow-rate dependent inspirator
US4359057A (en) * 1980-09-30 1982-11-16 Giovanni Manzella Apparatus for measuring oxygen consumption and the exchange of other breathing gases
US4364413A (en) * 1981-01-07 1982-12-21 The Perkin-Elmer Corporation Molar gas-flow controller
US4406291A (en) * 1980-04-07 1983-09-27 Schwesinger Dennis W Exhalation monitoring apparatus
WO1990008504A1 (de) * 1989-02-04 1990-08-09 Ganshorn Medizin Elektronik Gmbh Exspirationsluft-aufnahmegefäss
US5115682A (en) * 1990-05-21 1992-05-26 Feiler Ernest M Coronary artery graft flow-meter
US20070221222A1 (en) * 2003-09-11 2007-09-27 Advanced Circulatory Systems, Inc. Cpr devices and methods utilizing a continuous supply of respiratory gases
US20080047555A1 (en) * 2003-09-11 2008-02-28 Advanced Circulatory Systems, Inc. Bag-valve resuscitation for treating of hypotension, head trauma, and cardiac arrest
US20080257344A1 (en) * 2007-04-19 2008-10-23 Advanced Circulatory Systems, Inc. Volume exchanger valve system and method to increase circulation during cpr
US9238115B2 (en) 2011-12-19 2016-01-19 ResQSystems, Inc. Systems and methods for therapeutic intrathoracic pressure regulation
US9352111B2 (en) 2007-04-19 2016-05-31 Advanced Circulatory Systems, Inc. Systems and methods to increase survival with favorable neurological function after cardiac arrest
US20160279378A1 (en) * 2015-03-24 2016-09-29 Ventec Life Systems, Inc. Passive leak valve
WO2016202936A1 (fr) 2015-06-16 2016-12-22 Commissariat A L'energie Atomique Et Aux Energies Alternatives Dispositif de mesure de volumes d'emanation de gaz
US9724266B2 (en) 2010-02-12 2017-08-08 Zoll Medical Corporation Enhanced guided active compression decompression cardiopulmonary resuscitation systems and methods
US9811634B2 (en) 2013-04-25 2017-11-07 Zoll Medical Corporation Systems and methods to predict the chances of neurologically intact survival while performing CPR
US9949686B2 (en) 2013-05-30 2018-04-24 Zoll Medical Corporation End-tidal carbon dioxide and amplitude spectral area as non-invasive markers of coronary perfusion pressure
US10265495B2 (en) 2013-11-22 2019-04-23 Zoll Medical Corporation Pressure actuated valve systems and methods
US10512749B2 (en) 2003-04-28 2019-12-24 Zoll Medical Corporation Vacuum and positive pressure ventilation systems and methods for intrathoracic pressure regulation
US10773049B2 (en) 2016-06-21 2020-09-15 Ventec Life Systems, Inc. Cough-assist systems with humidifier bypass
US11191915B2 (en) 2018-05-13 2021-12-07 Ventec Life Systems, Inc. Portable medical ventilator system using portable oxygen concentrators
US11247015B2 (en) 2015-03-24 2022-02-15 Ventec Life Systems, Inc. Ventilator with integrated oxygen production
US12016820B2 (en) 2010-02-12 2024-06-25 Zoll Medical Corporation Enhanced guided active compression decompression cardiopulmonary resuscitation systems and methods
US12440634B2 (en) 2020-12-21 2025-10-14 Ventec Life Systems, Inc. Ventilator systems with integrated oxygen delivery, and associated devices and methods

Families Citing this family (1)

* Cited by examiner, † Cited by third party
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US4203316A (en) * 1978-09-29 1980-05-20 Jones Medical Instrument Company Device and method for calibrating pulmonary function testing equipment

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US3659590A (en) * 1969-10-13 1972-05-02 Jones Medical Instr Co Respiration testing system
US3718044A (en) * 1971-12-07 1973-02-27 Us Army Flow meter for indirectly measuring the flow of blood from a blood pump

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US3059469A (en) * 1961-06-12 1962-10-23 Jersey Prod Res Co Determination of cavity size in earth formations penetrated by a borehole
US3499438A (en) * 1966-05-19 1970-03-10 Blease Anaesthetic Equip Ltd Respiratory metering device
US3690143A (en) * 1970-11-27 1972-09-12 American Optical Corp Self calibrating tidal volume impedance pneumograph

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Publication number Priority date Publication date Assignee Title
US3467078A (en) * 1965-05-10 1969-09-16 Bird F M Spirometer
US3659590A (en) * 1969-10-13 1972-05-02 Jones Medical Instr Co Respiration testing system
US3718044A (en) * 1971-12-07 1973-02-27 Us Army Flow meter for indirectly measuring the flow of blood from a blood pump

Cited By (52)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4112931A (en) * 1977-01-05 1978-09-12 Cavitron Corporation Tidal volume display
US4233990A (en) * 1979-03-20 1980-11-18 Empire Plastics Manufacturing Inc. Volume and flow-rate dependent inspirator
US4406291A (en) * 1980-04-07 1983-09-27 Schwesinger Dennis W Exhalation monitoring apparatus
US4359057A (en) * 1980-09-30 1982-11-16 Giovanni Manzella Apparatus for measuring oxygen consumption and the exchange of other breathing gases
US4364413A (en) * 1981-01-07 1982-12-21 The Perkin-Elmer Corporation Molar gas-flow controller
WO1990008504A1 (de) * 1989-02-04 1990-08-09 Ganshorn Medizin Elektronik Gmbh Exspirationsluft-aufnahmegefäss
US5115682A (en) * 1990-05-21 1992-05-26 Feiler Ernest M Coronary artery graft flow-meter
US10512749B2 (en) 2003-04-28 2019-12-24 Zoll Medical Corporation Vacuum and positive pressure ventilation systems and methods for intrathoracic pressure regulation
US20070221222A1 (en) * 2003-09-11 2007-09-27 Advanced Circulatory Systems, Inc. Cpr devices and methods utilizing a continuous supply of respiratory gases
US20080047555A1 (en) * 2003-09-11 2008-02-28 Advanced Circulatory Systems, Inc. Bag-valve resuscitation for treating of hypotension, head trauma, and cardiac arrest
US8011367B2 (en) 2003-09-11 2011-09-06 Advanced Circulatory Systems, Inc. CPR devices and methods utilizing a continuous supply of respiratory gases
US9352111B2 (en) 2007-04-19 2016-05-31 Advanced Circulatory Systems, Inc. Systems and methods to increase survival with favorable neurological function after cardiac arrest
US10478374B2 (en) 2007-04-19 2019-11-19 Zoll Medical Corporation Systems and methods to increase survival with favorable neurological function after cardiac arrest
US11020313B2 (en) 2007-04-19 2021-06-01 Zoll Medical Corporation Systems and methods to increase survival with favorable neurological function after cardiac arrest
US20080257344A1 (en) * 2007-04-19 2008-10-23 Advanced Circulatory Systems, Inc. Volume exchanger valve system and method to increase circulation during cpr
US12220378B2 (en) 2007-04-19 2025-02-11 Zoll Medical Corporation Systems and methods to increase survival with favorable neurological function after cardiac arrest
US8151790B2 (en) 2007-04-19 2012-04-10 Advanced Circulatory Systems, Inc. Volume exchanger valve system and method to increase circulation during CPR
US8985098B2 (en) 2007-04-19 2015-03-24 Advanced Circulatory Systems, Inc. CPR volume exchanger valve system with safety feature and methods
US9675770B2 (en) 2007-04-19 2017-06-13 Advanced Circulatory Systems, Inc. CPR volume exchanger valve system with safety feature and methods
US11679061B2 (en) 2007-04-19 2023-06-20 Zoll Medical Corporation Systems and methods to increase survival with favorable neurological function after cardiac arrest
US11583645B2 (en) 2009-06-19 2023-02-21 Zoll Medical Corporation Vacuum and positive pressure ventilation systems and methods for intrathoracic pressure regulation
US11969551B2 (en) 2009-06-19 2024-04-30 Zoll Medical Corporation Vacuum and positive pressure ventilation systems and methods for intrathoracic pressure regulation
US9724266B2 (en) 2010-02-12 2017-08-08 Zoll Medical Corporation Enhanced guided active compression decompression cardiopulmonary resuscitation systems and methods
US12016820B2 (en) 2010-02-12 2024-06-25 Zoll Medical Corporation Enhanced guided active compression decompression cardiopulmonary resuscitation systems and methods
US11123261B2 (en) 2010-02-12 2021-09-21 Zoll Medical Corporation Enhanced guided active compression decompression cardiopulmonary resuscitation systems and methods
US11654253B2 (en) 2011-12-19 2023-05-23 Zoll Medical Corporation Systems and methods for therapeutic intrathoracic pressure regulation
US10034991B2 (en) 2011-12-19 2018-07-31 Zoll Medical Corporation Systems and methods for therapeutic intrathoracic pressure regulation
US10874809B2 (en) 2011-12-19 2020-12-29 Zoll Medical Corporation Systems and methods for therapeutic intrathoracic pressure regulation
US9238115B2 (en) 2011-12-19 2016-01-19 ResQSystems, Inc. Systems and methods for therapeutic intrathoracic pressure regulation
US11488703B2 (en) 2013-04-25 2022-11-01 Zoll Medical Corporation Systems and methods to predict the chances of neurologically intact survival while performing CPR
US9811634B2 (en) 2013-04-25 2017-11-07 Zoll Medical Corporation Systems and methods to predict the chances of neurologically intact survival while performing CPR
US10835175B2 (en) 2013-05-30 2020-11-17 Zoll Medical Corporation End-tidal carbon dioxide and amplitude spectral area as non-invasive markers of coronary perfusion pressure
US9949686B2 (en) 2013-05-30 2018-04-24 Zoll Medical Corporation End-tidal carbon dioxide and amplitude spectral area as non-invasive markers of coronary perfusion pressure
US10265495B2 (en) 2013-11-22 2019-04-23 Zoll Medical Corporation Pressure actuated valve systems and methods
US11992619B2 (en) 2015-03-24 2024-05-28 Ventec Life Systems, Inc. Ventilator with integrated cough-assist
US20160279378A1 (en) * 2015-03-24 2016-09-29 Ventec Life Systems, Inc. Passive leak valve
US11247015B2 (en) 2015-03-24 2022-02-15 Ventec Life Systems, Inc. Ventilator with integrated oxygen production
US11291791B2 (en) 2015-03-24 2022-04-05 Ventee Life Systems, Inc. Ventilator with integrated cough-assist
US11344692B2 (en) * 2015-03-24 2022-05-31 Ventec Life Systems, Inc. Respiratory therapy systems and methods
US10518059B2 (en) * 2015-03-24 2019-12-31 Ventec Life Systems, Inc. Passive leak valve
US11185655B2 (en) 2015-03-24 2021-11-30 Ventec Life Systems, Inc. Passive leak valve
US10576237B2 (en) 2015-03-24 2020-03-03 Ventec Life Systems, Inc. Active exhalation valve
US10758699B2 (en) 2015-03-24 2020-09-01 Ventec Life Systems, Inc. Secretion trap
FR3037648A1 (fr) * 2015-06-16 2016-12-23 Commissariat Energie Atomique Dispositif de mesure de volumes d'emanation de gaz
WO2016202936A1 (fr) 2015-06-16 2016-12-22 Commissariat A L'energie Atomique Et Aux Energies Alternatives Dispositif de mesure de volumes d'emanation de gaz
US11679229B2 (en) 2016-06-21 2023-06-20 Ventec Life Systems, Inc. Cough-assist systems with humidifier bypass
US10773049B2 (en) 2016-06-21 2020-09-15 Ventec Life Systems, Inc. Cough-assist systems with humidifier bypass
US12246135B2 (en) 2016-06-21 2025-03-11 Ventec Life Systems, Inc. Cough-assist systems with humidifier bypass
US11191915B2 (en) 2018-05-13 2021-12-07 Ventec Life Systems, Inc. Portable medical ventilator system using portable oxygen concentrators
US12370333B2 (en) 2018-05-13 2025-07-29 Ventec Life Systems, Inc. Portable medical ventilator system using portable oxygen concentrators
US12434026B2 (en) 2018-05-13 2025-10-07 Ventec Life Systems, Inc. Portable medical ventilator system using portable oxygen concentrators
US12440634B2 (en) 2020-12-21 2025-10-14 Ventec Life Systems, Inc. Ventilator systems with integrated oxygen delivery, and associated devices and methods

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Publication number Publication date
GB1451360A (en) 1976-09-29
FR2209926A1 (enExample) 1974-07-05
FR2209926B1 (enExample) 1978-02-10
SE380724B (sv) 1975-11-17
IT1004043B (it) 1976-07-10
DE2361165A1 (de) 1974-06-20

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