US3859995A - Breathing assist apparatus - Google Patents

Breathing assist apparatus Download PDF

Info

Publication number
US3859995A
US3859995A US376003A US37600373A US3859995A US 3859995 A US3859995 A US 3859995A US 376003 A US376003 A US 376003A US 37600373 A US37600373 A US 37600373A US 3859995 A US3859995 A US 3859995A
Authority
US
United States
Prior art keywords
jet pump
gas
breathing
supply
coupling
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
US376003A
Other languages
English (en)
Inventor
John R Colston
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Westinghouse Electric Corp
Original Assignee
Westinghouse Electric Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Westinghouse Electric Corp filed Critical Westinghouse Electric Corp
Priority to US376003A priority Critical patent/US3859995A/en
Priority to CA201,437A priority patent/CA990611A/en
Priority to DE2430096A priority patent/DE2430096A1/de
Priority to JP49075073A priority patent/JPS5038397A/ja
Application granted granted Critical
Publication of US3859995A publication Critical patent/US3859995A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B63—SHIPS OR OTHER WATERBORNE VESSELS; RELATED EQUIPMENT
    • B63C—LAUNCHING, HAULING-OUT, OR DRY-DOCKING OF VESSELS; LIFE-SAVING IN WATER; EQUIPMENT FOR DWELLING OR WORKING UNDER WATER; MEANS FOR SALVAGING OR SEARCHING FOR UNDERWATER OBJECTS
    • B63C11/00—Equipment for dwelling or working underwater; Means for searching for underwater objects
    • B63C11/02—Divers' equipment
    • B63C11/18—Air supply
    • B63C11/22—Air supply carried by diver
    • B63C11/24—Air supply carried by diver in closed circulation

Definitions

  • a breathing assist device for deep sea divers and the Fleld of Search 1 like including a reversible jet pump powered from a 128/ 14596, breathing gas supply and controlled by a diaphragm 63 R actuated two position poppet valve which operates in response to the pressure differential occurring across [56] Refe e ces Clted the jet pump during a ventilation cycle.
  • This invention relates to ventilation, i.e., breathing apparatus, and more particularly to breathing assist apparatus for supplying breathable gas to a persons lungs, for example a diver working at great depths wherein the high flow resistance pressure drops resulting from the high density of the breathing gas must be overcome in order to receive sufficient quantities of gas in order to function efficiently.
  • the subject invention is directed to breathing assist apparatus for both the inhalation and exhalation phases of a ventilation cycle and which is particularly useful but not restricted to the life support apparatusworn by undersea divers.
  • the breathing assist apparatus comprises a reversible jet pump located between a device inserted in the divers mouth and an input valve and an output check valve, the input valve couples a source of breathing to the jet pump.
  • the output valve acts to conduct the exhaled gas away from the pump.
  • the reversible jet pump includes a unitary converging-diverging throat section with upper and lower supply nozzles respectively located at each end of the throat section.
  • the supply nozzles are alternately supplied from a gas power source during exhalation and inhalation causing a gas pumping action first in one direction and then the other.
  • Control of the nozzles is effected by valving means driven by a diaphragm operable in response to the differential pressure in the region of the supply nozzles.
  • the pressure drop across the jet pump is sensed by the diaphragm which when the pressure drop across the jet pump exceeds a preset value, indicating a decrease in inhalation flow for example, the diaphragm causes the valving means to switch to the opposite position causing the other supply nozzle to become activated,
  • This type of breathing device senses the divers attempt to inhale and exhale and assists his normal breathing and thereby overcome the increase pressure drops due to the relatively high density of the breathing gas at increased depths. If for some reason the diver ceases to breathe on his own power, the present invention will also effect an automatic ventilation of the diver's lungs.
  • anotherjet pump may be included between the gas power source which may comprise a replenish supply in a closed or semi-closed system and the valving means as well as a breathing assist pressure adjustment means. The additional jet pump results in quieter operation while the pressure adjustment is advantageous when a divers work becomes harder and his breathing flow demand increases.
  • FIG. 1 is a vertical cross sectional view illustrative of the preferred embodiment of the subject invention
  • FIG. 2 is a set of performance curves illustrative of the operation of the subject invention
  • FIG. 3 is a side elevational view of the subject invention incorporated in an open circuit or Scuba type of underwater life support apparatus;
  • FIG. 4 is a side elevational view of the subject invention incorporated in a closed circuit life support apparatus
  • FIG. 5 is a side elevational view of the subject invention incorporated in a semi-closed life support apparatus fed from an umbilical tube coupled back to an underwater habitat, not shown;
  • FIG. 6 is illustrative of the subject invention incorporated in a diving helmet fed a helium-oxygen mixture from a habitat, not shown.
  • the breathing assist apparatus of the subject invention comprising, inter alia, a reversible jet pump designated generally by reference numeral 10 coupled between a respirator such as a mouthpiece l2 and a pair of valves 14 and 16.
  • the valve 14 is operable to feed a breathing gas such as air, pure oxygen or helium-oxygen mixture to the mouthpiece 12 for inhalation while the valve 16 is adapted to feed the exhaled gases away from the apparatus either to the outside atmosphere or a breathing bag, not shown.
  • valve 14 which may be referred to as the input valve is located in an input conduit 18 while the valve 16 which may be referred to as the output check valve is located in an output conduit 20.
  • the input and output conduits l8 and 20 join together in a region 22 which is common to one diverging end of a unitary converging-diverging throat section 24, i.e., one having a common constriction or narrow portion between two flared or diverging end portions.
  • a first aspirator type supply nozzle 26 is located in one end portion 27 which also is common to the region 22 and is directed towards the common constriction portion 28.
  • the supply nozzle 26 and the throat portions 27 and 28 act as the first section of a relength of conduit 30 which terminates in a bend at a region 32 which is common to the other diverging end of portion 33 of the converging-diverging throat section 24.
  • a second aspirator type supply nozzle 34 is located in the end portion 33 and is directed toward the common constriction portion 28 and is adapted to pump the exhaled gas to the conduit 20 from the mouthpiece l2 and the conduit 30.
  • the bi-directional jet pump 10 is contained in a body 38 which additionally includes a chamber 40 located adjacent the converging-diverging throat section 24 in which is located a diaphragm 42 which separates the chamber into two parts.
  • One part of the chamber 40 is coupled to the region 22 by means of a channel 44 while the other part of the chamber 40 is coupled to the region 32 at the opposite end of the nozzle 34 by means of the channel 46.
  • the pressure on one side of the diaphragm 42 is at the pressure in the vicinity of the region 22 while the pressure on the other side of the diaphragm is at the pressure in the vicinity of the region 32.
  • the diaphragm 42 is connected to a double acting poppet valve 48 by means of a stem 50.
  • the valve 48 is located in a valve chamber 52, having an input orifice in one side thereof.
  • the chamber 52 In a first position of the valve 48, the chamber 52 is coupled to the supply nozzle 26 by means of a fluid passage 54 while in the second position of the valve 48, the chamber 52 is coupled to the supply nozzle 34 by means of the fluid passage 56.
  • the valve chamber 52 isfed a breathable gas for powering the jet pump 10 from a conduit 57 coupled to a suitable source, not shown, which may be for example a replen- .ish supply in a closed or semi-closed system.
  • the gas applied to the conduit 57 is adapted to supply the pumping power alternately to the supply nozzles 26 and 34 during inhalation and exhalation respectively, and is fed to the valve chamber 52 by means of a first stage uni-directional jet pump 58 including a supply nozzle 60 and a throat portion 62.
  • the incoming gas supplied by means of conduit 57 is adapted to provide a pumping action of gas coupled thereto from the region 32 by means of the passage 64.
  • a by-pass air passage 66 which couples back to the air passage 64.
  • the amount of by-pass or bleed flow is controlled by means of a manually operated screw 68 mounted in the outer wall of the body portion 38.
  • the breathing assist apparatus shown in FIG. 1 constitutes a bi-stable device which senses the attempt to inhale and exhale by reason of the pressure differentials between the regions 22 and 32 to trigger the necessary pumping action to assist normal breathing.
  • the apparatus shown in FIG. 1 operates in the following manner. Assume for purposes of illustration that exhalation has ceased and inhalation starts. At that moment the pressure in the region 32 begins to drop with respect to the pressure in region 22. The pressure differential in the passages 46 and 44 causes the diaphragm 42 to move to the position shown inFIG. 1, shutting off passage 56 from the chamber 52 while opening passage 54.
  • the incoming gas applied to the first stage jet pump 58 by means of the conduit 57 is coupled to the passage 54 and to the supply nozzle 26, causing a pumping action from the check valve 14 and the conduit 18 by means of the venturi effect.
  • a positive feedback action occurs via the gas flow in passage 64 causing still further pumping action due to the venturi effect and pumping action of the first stage jet pump 58.
  • the pressure in region 32 increases, due to the back pressure provided by the gas in the lungs.
  • This phase of a ventilation cycle is shown for example by reference to curve 70 shown in FIG. 2 which depicts the pumping pressure existing at the mouthpiece 12 shown in FIG. 1.
  • the pressure at the mouthpiece 12 now exhibits a characteristic as shown by the curve 76 in FIG. 2 while the flow out of the lungs appears as shown by the curve 78 shown in FIG: 2, until, where for example at the end of the three second period exhalation flow ceases and the inhalation action again is triggered.
  • the apparatus as shown in FIG. 1 is particularly adapted to overcome the pressure drop increase with depth experienced with relatively high density breathing gases (helium-oxygen) utilized in underwater life support apparatus.
  • relatively high density breathing gases helium-oxygen
  • the configuration as disclosed in FIG. 1 is operable to sense a divers attempt to inhale and exhale and assist his normal breathing of these relatively high density breathing gases. If for some reason the diver ceases to breathe on his own power, the present invention will cause automatic ventilation of the divers lungs. In this sense it also becomes a life sensing device.
  • the first stage jet pump 58 shown in FIG. 1 acts to convert high pressure low flow gas in the conduit 57 into a medium pressure medium flow output into the valve chamber 52 and the by-pass or bleed passage 66.
  • the first stage jet pump results in a quieter operating device.
  • Adjustment of the screw 68 adjusts the pressure occurring at the output of the supply nozzles 26 and 34, which is advantageous, for example, when a diver increases his work output requiring a greater breath flow demand.
  • a second reason for the desirability of the first stage jet pump 58 is to reduce the length of the converging-diverging nozzle 24 of the reversible jet pump 10.
  • the first stage jet pump results in larger areas and lower velocities in the supply nozzles 26 and 34. This in turn results in a shorter dis tance for the velocity to become reasonably uniform in the throat section 24 of the reversible jet pump 10.
  • FIGS. 3 through 6, inclusively disclose various combinations of life support systems which the subject invention can be used in conjunction therewith.
  • FIG. 3 for example, is illustrative of an open circuit system which might, for example, comprise a Scuba diving rig wherein a tank 80 containing oxygen or air is coupled to an input demand valve 14 by means of a flexible hose 82 and to the conduit 57 by means of another hose 84 branching off of the hose 82.
  • the gas supplied through the hose 84 acts simply as a power source for operating the apparatus.
  • gas is drawn from the bottle 80 through the demand valve 14' and out of the mouthpiece 12.
  • the exhaled gases including carbon dioxide CO is fed back through the mouthpiece 12 where it is pumped out of the output check valve 16 to the surrounding water environment.
  • FIG. 4 discloses a closed circuit breathing apparatus whereupon the oxygen bottle 80 is coupled by means of a flow regulating valve 81 to the conduit 57 by means of a flexible tube 86 to act as a make up or replenish source and power the supply nozzles 26 and 34.
  • the exhaled gases are fed from the output check valve 16 into a first breathing bag 88 which feeds into a canister 90, which removes the carbon dioxide from the exhaled air.
  • the output of the canister 90 comprises CO -free breathing gas which is fed to a second breathing bag 92 where it can then be fed back to the input valve 14 so that the breathing gas is recirculated. Oxygen consumed by breathing is replenished by gas from the oxygen bottle 80.
  • FIG. 5 constitutes a semiclosed system which is adapted to replenish and power the breathing assist mechanism shown in FIG. 1 and is particularly useful in connection with deep diving apparatus where a helium-oxygen mixture is coupled to the apparatus shown in FIG. I from a habitat not shown, by means of an umbilical line 94.
  • a system using a He-O mixture normally requires a relief valve such as shown by reference numeral 96 at the input to the exhalation breathing bag 88.
  • Such a relief valve feeds to the surrounding atmosphere and acts to relieve the pressure build up in the exhalation breathing bag 88.
  • FIG. 6 is intended to illustrate, for example, the apparatus as depicted in FIG. 1, incorporated in a diving helmet shown in phantom section by reference numeral 98. Also instead of a single umbilical line 94 feeding the breathing assist apparatus, a second umbilical line 100 6 is utilized to feed the exhaust gases, including helium, oxygen and carbon dioxide back to an underwater habitat, not shown.
  • the curves shown in FIG. 2 and the values associated therewith are based on calculations provided in an analysis for a diver at the depth of 1,000 feet of sea water, breathing 4% O -96%He gas mixture with the breathing assist pressure adjusted to a maximum value of 15cm H O for no flow.
  • the peak instantaneous breathing flow is assumed to be 2.5 meters per second.
  • the value of 15cm H O is shown as the maximum pumping pressure because values greater than this could result in air being forced into a diver's stomach.
  • Breathing assist apparatus in a system having a breathing input/output device coupling the respiratory system to a source of breathing gas, comprising in combination:
  • a reversible jet pump having a pair of opposed aspirators each including a supply nozzle, said supply nozzles being directed toward one another and respectively located at either end of a convergingdiverging throat section including a common relatively narrow intermediate portion, and flared end portions;
  • output means also coupled to said other end portion of said jet pump for removing exhaled gases therefrom;
  • valve means having bi-stable operating states being operable to alternately couple each of said supply nozzles to said gas power source whereby in a first operating state the supply nozzle located at said other end of said jet pump operates to pump breathing gas toward said input/output device through said thraot section and in a second operating state said supply nozzle located at said one end of said jet pump operates to pump exhaled gas to said output means through said throat section;
  • valve means responsive to the pressure differential between each end portion of said jet pump in the region of said supply nozzles for actuating said valve means and comprising a pressure chamber including a diaphragm, in parallel relationship to said reversible jet pump, dividing said pressure chamber into two parts and additionally including a first channel coupling the region at said one end of said jet pump to one part of said chamber and a second channel coupling the region of the other end of said jet pump to said second part of said chamber; and
  • said another jet pump comprises a uni-directional device including a nozzle and a throat section
  • said source of breathing gas and said gas power source comprise a single breathable gas supply including first and second coupling means respectively coupling said supply tosaid input means and said valve means.
  • said system additionally includes a first breathing bag coupled to said output means for receiving exhaled gases, exhaled gas reconditioning means coupled to said first breathing bag, and a second breathing bag coupled between said gas reconditioning means and said input means, and
  • said gas power source comprises a replenish breathing gas supply coupled to said valve means.
  • said gas power source is comprised of a remote supply and additionally including an umbilical line coupling said remote supply to said valve means.
  • said source of breathing gas and said gas power source comprise a common breathing gas supply situated at a remote location and additionally including a first umbilical line means coupling said common supply to said input means and said valve means, and a second umbilical line coupling said output means to said remote location for returning exhaled gases.

Landscapes

  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Pulmonology (AREA)
  • Engineering & Computer Science (AREA)
  • Mechanical Engineering (AREA)
  • Ocean & Marine Engineering (AREA)
  • Respiratory Apparatuses And Protective Means (AREA)
US376003A 1973-07-02 1973-07-02 Breathing assist apparatus Expired - Lifetime US3859995A (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
US376003A US3859995A (en) 1973-07-02 1973-07-02 Breathing assist apparatus
CA201,437A CA990611A (en) 1973-07-02 1974-06-03 Breathing assist apparatus
DE2430096A DE2430096A1 (de) 1973-07-02 1974-06-22 Atemhilfsgeraet
JP49075073A JPS5038397A (enrdf_load_stackoverflow) 1973-07-02 1974-07-02

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US376003A US3859995A (en) 1973-07-02 1973-07-02 Breathing assist apparatus

Publications (1)

Publication Number Publication Date
US3859995A true US3859995A (en) 1975-01-14

Family

ID=23483291

Family Applications (1)

Application Number Title Priority Date Filing Date
US376003A Expired - Lifetime US3859995A (en) 1973-07-02 1973-07-02 Breathing assist apparatus

Country Status (4)

Country Link
US (1) US3859995A (enrdf_load_stackoverflow)
JP (1) JPS5038397A (enrdf_load_stackoverflow)
CA (1) CA990611A (enrdf_load_stackoverflow)
DE (1) DE2430096A1 (enrdf_load_stackoverflow)

Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4289126A (en) * 1979-05-02 1981-09-15 Wisconsin Alumni Research Foundation Pressure regulator for breathing apparatus
US4417573A (en) * 1981-07-02 1983-11-29 Bear Medical Systems, Inc. Patient adaptor for medical ventilator
US4612929A (en) * 1984-01-20 1986-09-23 Dragerwerk Ag Attachment for the supply of breathing gas for high-frequency artificial respiration
US5036847A (en) * 1989-03-31 1991-08-06 Georges Boussignac Breathing aid
US5452715A (en) * 1993-08-26 1995-09-26 Boussignac; Georges Tube for assisting breathing
US5538002A (en) * 1994-09-14 1996-07-23 Boussignac; Georges Device for respiratory assistance
US6119723A (en) * 1997-02-14 2000-09-19 Resmed Limited, Apparatus for varying the flow area of a conduit
US6253764B1 (en) 1996-05-08 2001-07-03 Resmed, Ltd. Control of delivery pressure in CPAP treatment or assisted respiration
US6260550B1 (en) * 1998-11-04 2001-07-17 DRäGER MEDIZINTECHNIK GMBH Device and process for controlling a respirator
US20020162553A1 (en) * 2001-05-07 2002-11-07 Hamilton Robert M. Portable gas powered positive pressure breathing apparatus and method
US6532957B2 (en) 1996-09-23 2003-03-18 Resmed Limited Assisted ventilation to match patient respiratory need
US20030106554A1 (en) * 2001-11-30 2003-06-12 De Silva Adrian D. Gas identification system and volumetric ally correct gas delivery system
US20070119454A1 (en) * 1991-12-20 2007-05-31 Resmed Limited Patient interface assembly for CPAP respiratory apparatus
US20140305436A1 (en) * 2011-12-08 2014-10-16 Metran Co., Ltd. Pump unit and respiratory assistance device
WO2015004229A1 (en) * 2013-07-10 2015-01-15 Ventinova Technologies B.V. Gas flow reversing element with bypass and method for controlling expiration of a patient
US20150202473A1 (en) * 2012-08-31 2015-07-23 3M Innovative Properties Company Powered Exhaust Apparatus For A Personal Protection Respiratory Device
US20150250977A1 (en) * 2012-08-21 2015-09-10 Dräger Safety AG & Co. KGaA Respirator
US20150290478A1 (en) * 2012-11-22 2015-10-15 3M Innovative Properties Company Powered Exhaust Apparatus For A Personal Protection Respiratory Device
US10307552B2 (en) 2013-09-06 2019-06-04 Breathe Technologies, Inc. Jet pump adaptor for ventilation system

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5092255A (enrdf_load_stackoverflow) * 1973-12-19 1975-07-23
JPS52100795A (en) * 1976-02-20 1977-08-24 Kazumasa Okamura Portable refuge respirator
US4186735A (en) * 1977-04-21 1980-02-05 Flood Michael G Breathing apparatus
JPS55109543U (enrdf_load_stackoverflow) * 1979-01-29 1980-07-31
JPH087923Y2 (ja) * 1991-03-15 1996-03-06 新日本製鐵株式会社 ロール保護装置を設けた多段圧延機
US5577498A (en) * 1993-07-07 1996-11-26 Zexel Corporation Semi-closed type breathing apparatus for removing carbon dioxide from breathing air circuit having triangularly shaped bellows

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2483698A (en) * 1947-10-24 1949-10-04 Stephenson Corp Resuscitator
US2547458A (en) * 1947-06-25 1951-04-03 Stephenson Corp Resuscitator

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2547458A (en) * 1947-06-25 1951-04-03 Stephenson Corp Resuscitator
US2483698A (en) * 1947-10-24 1949-10-04 Stephenson Corp Resuscitator

Cited By (46)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4289126A (en) * 1979-05-02 1981-09-15 Wisconsin Alumni Research Foundation Pressure regulator for breathing apparatus
US4417573A (en) * 1981-07-02 1983-11-29 Bear Medical Systems, Inc. Patient adaptor for medical ventilator
US4612929A (en) * 1984-01-20 1986-09-23 Dragerwerk Ag Attachment for the supply of breathing gas for high-frequency artificial respiration
US5036847A (en) * 1989-03-31 1991-08-06 Georges Boussignac Breathing aid
US7931023B2 (en) 1991-12-20 2011-04-26 Resmed Limited Patient interface assembly for CPAP respiratory apparatus
US20070119454A1 (en) * 1991-12-20 2007-05-31 Resmed Limited Patient interface assembly for CPAP respiratory apparatus
US7302950B2 (en) 1991-12-20 2007-12-04 Resmed Limited Patient interface for respiratory apparatus
US5452715A (en) * 1993-08-26 1995-09-26 Boussignac; Georges Tube for assisting breathing
US5538002A (en) * 1994-09-14 1996-07-23 Boussignac; Georges Device for respiratory assistance
US6253764B1 (en) 1996-05-08 2001-07-03 Resmed, Ltd. Control of delivery pressure in CPAP treatment or assisted respiration
US7644713B2 (en) 1996-09-23 2010-01-12 Resmed Limited Method and apparatus for determining instantaneous leak during ventilatory assistance
US6532957B2 (en) 1996-09-23 2003-03-18 Resmed Limited Assisted ventilation to match patient respiratory need
US8051853B2 (en) 1996-09-23 2011-11-08 Resmed Limited Method and apparatus for providing ventilatory assistance
US8733351B2 (en) 1996-09-23 2014-05-27 Resmed Limited Method and apparatus for providing ventilatory assistance
US6688307B2 (en) 1996-09-23 2004-02-10 Resmed Limited Methods and apparatus for determining instantaneous elastic recoil and assistance pressure during ventilatory support
US6810876B2 (en) 1996-09-23 2004-11-02 Resmed Ltd. Assisted ventilation to match patient respiratory need
US9974911B2 (en) 1996-09-23 2018-05-22 Resmed Limited Method and apparatus for providing ventilatory assistance
US7137389B2 (en) 1996-09-23 2006-11-21 Resmed Limited Method and apparatus for determining instantaneous inspired volume of a subject during ventilatory assistance
US6119723A (en) * 1997-02-14 2000-09-19 Resmed Limited, Apparatus for varying the flow area of a conduit
US6260550B1 (en) * 1998-11-04 2001-07-17 DRäGER MEDIZINTECHNIK GMBH Device and process for controlling a respirator
US20060243278A1 (en) * 2001-05-07 2006-11-02 Hamilton Robert M Portable gas powered positive pressure breathing apparatus and method
US7066175B2 (en) 2001-05-07 2006-06-27 Emergent Respiratory Products, Inc. Portable gas powered positive pressure breathing apparatus and method
WO2002089873A3 (en) * 2001-05-07 2003-12-04 Life Support Technology Inc Pressure regulating valve and positive pressure ventilation system
US20020162553A1 (en) * 2001-05-07 2002-11-07 Hamilton Robert M. Portable gas powered positive pressure breathing apparatus and method
US7721735B2 (en) 2001-05-07 2010-05-25 Emergent Respiratory Products, Inc. Portable gas powered positive pressure breathing apparatus and method
US20100199985A1 (en) * 2001-05-07 2010-08-12 Hamilton Robert M Portable gas powered positive pressure breathing apparatus and method
US8365728B2 (en) 2001-05-07 2013-02-05 Emergent Respiratory Llc Portable gas powered positive pressure breathing apparatus and method
US20030106554A1 (en) * 2001-11-30 2003-06-12 De Silva Adrian D. Gas identification system and volumetric ally correct gas delivery system
US20080105259A1 (en) * 2001-11-30 2008-05-08 Viasys Healthcare, Critical Care Division Gas identification system and respiratory technologies volumetrically corrected gas delivery system
US9205219B2 (en) 2001-11-30 2015-12-08 Carefusion 202, Inc. Gas identification system and respiratory technologies volumetrically corrected gas delivery system
US7387123B2 (en) 2001-11-30 2008-06-17 Viasys Manufacturing, Inc. Gas identification system and volumetrically correct gas delivery system
US20140305436A1 (en) * 2011-12-08 2014-10-16 Metran Co., Ltd. Pump unit and respiratory assistance device
US10036377B2 (en) * 2011-12-08 2018-07-31 Metran Co., Ltd. Pump unit and respiratory assistance device
US10369322B2 (en) * 2012-08-21 2019-08-06 Dräger Safety AG & Co. KGaA Respirator
US20150250977A1 (en) * 2012-08-21 2015-09-10 Dräger Safety AG & Co. KGaA Respirator
US20150202473A1 (en) * 2012-08-31 2015-07-23 3M Innovative Properties Company Powered Exhaust Apparatus For A Personal Protection Respiratory Device
US20150290478A1 (en) * 2012-11-22 2015-10-15 3M Innovative Properties Company Powered Exhaust Apparatus For A Personal Protection Respiratory Device
JP2016523674A (ja) * 2013-07-10 2016-08-12 ヴェンティノーヴァ テクノロジーズ ベスローテン ヴェンノーツハップＶｅｎｔｉｎｏｖａ Ｔｅｃｈｎｏｌｏｇｉｅｓ Ｂ．Ｖ． バイパスを有するガス流転換要素および患者の呼気を制御するための方法
CN105392515A (zh) * 2013-07-10 2016-03-09 万提诺瓦技术有限责任公司 带旁通管的气流换向元件和控制患者呼气的方法
RU2663787C2 (ru) * 2013-07-10 2018-08-09 Вентинова Технолоджиз Б.В. Реверсирующий поток газа элемент с байпасом и способ управления экспирацией пациента
WO2015004229A1 (en) * 2013-07-10 2015-01-15 Ventinova Technologies B.V. Gas flow reversing element with bypass and method for controlling expiration of a patient
US10857318B2 (en) 2013-07-10 2020-12-08 Ventinova Technologies B.V. Gas flow reversing element with bypass and method for controlling expiration of a patient
US11969550B2 (en) 2013-07-10 2024-04-30 Ventinova Technologies B.V. Gas flow reversing element with bypass and method for controlling expiration of a patient
US10307552B2 (en) 2013-09-06 2019-06-04 Breathe Technologies, Inc. Jet pump adaptor for ventilation system
US11654255B2 (en) 2013-09-06 2023-05-23 Breathe Technologies, Inc. Jet pump adaptor for ventilation system
US12005188B2 (en) 2013-09-06 2024-06-11 Breathe Technologies, Inc. Jet pump adaptor for ventilation system

Also Published As

Publication number Publication date
JPS5038397A (enrdf_load_stackoverflow) 1975-04-09
CA990611A (en) 1976-06-08
DE2430096A1 (de) 1975-01-23

Similar Documents

Publication Publication Date Title
US3859995A (en) Breathing assist apparatus
US4127123A (en) Ventilator and method
US3730180A (en) Pneumatically operated ventilator
US4273120A (en) Underwater breathing apparatus
US11291785B2 (en) Portable light-weight ventilator system
US4045835A (en) Power deflator mechanism for scuba buoyancy vests
US4459982A (en) Servo-controlled demand regulator for respiratory ventilator
US4905688A (en) Portable light weight completely self-contained emergency single patient ventilator/resuscitator
US3485243A (en) Respirator with improved exhalation valve and control means
US4637386A (en) Ventilation system having true valve control for controlling ventilation pressures
US3319627A (en) Intermittent positive pressure breathing apparatus
GB2139099A (en) Resuscitator
GB1212528A (en) Improvements in or relating to anesthesia apparatus and resuscitators
ATE158952T1 (de) Beatmungsgerät mit strahldüse
US20090228018A1 (en) Anti-Choking Device
US9352115B1 (en) Respiratory ventilation system with gas sparing valve having optional CPAP mode and mask for use with same
US2268172A (en) Resuscitator
JP2002509005A (ja) ピストン換気装置酸素混合
WO1981002677A1 (en) Volume ventilator
US3581742A (en) Intermittent positive pressure breathing device
GB1212529A (en) Improvements in or relating to mechanical ventilators for the lungs
EP0429528B1 (en) Resuscitator valve
US2364626A (en) Resuscitator
US5195516A (en) Breathing gas recirculation apparatus with reduced work of breathing
US4340045A (en) Lung ventilator