[go: up one dir, main page]

US3389698A - Fluidic device for alternately filling and emptying an enclosure - Google Patents

Fluidic device for alternately filling and emptying an enclosure Download PDF

Info

Publication number
US3389698A
US3389698A US47569665A US3389698A US 3389698 A US3389698 A US 3389698A US 47569665 A US47569665 A US 47569665A US 3389698 A US3389698 A US 3389698A
Authority
US
United States
Prior art keywords
duct
enclosure
cavity
valve
fluid
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
Other languages
English (en)
Inventor
Kadosch Marcel
Pavlin Cyrille Francois
Mace Edouard
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.)
Bertin Technologies SAS
Original Assignee
Bertin et Cie SA
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 Bertin et Cie SA filed Critical Bertin et Cie SA
Application granted granted Critical
Publication of US3389698A publication Critical patent/US3389698A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • 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. ventilators; Tracheal tubes
    • A61M16/06—Respiratory or anaesthetic masks
    • 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. ventilators; Tracheal tubes
    • A61M16/0057—Pumps therefor
    • A61M16/0063—Compressors
    • 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. ventilators; Tracheal tubes
    • A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes operated by electrical means
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00—Machines, pumps, or pumping installations having flexible working members
    • F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
    • F04B43/10—Pumps having fluid drive
    • F04B43/113—Pumps having fluid drive the actuating fluid being controlled by at least one valve
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F15—FLUID-PRESSURE ACTUATORS; HYDRAULICS OR PNEUMATICS IN GENERAL
    • F15C—FLUID-CIRCUIT ELEMENTS PREDOMINANTLY USED FOR COMPUTING OR CONTROL PURPOSES
    • F15C1/00—Circuit elements having no moving parts
    • F15C1/22—Oscillators
    • 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
    • A61M2202/00—Special media to be introduced, removed or treated
    • A61M2202/02—Gases
    • A61M2202/0208—Oxygen
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00—Fluid handling
    • Y10T137/206—Flow affected by fluid contact, energy field or coanda effect [e.g., pure fluid device or system]
    • Y10T137/2229—Device including passages having V over T configuration
    • Y10T137/2234—And feedback passage[s] or path[s]

Definitions

  • a fluidic device for alternately filling and emptying an enclosure comprising a motive fluid supply duct leading from an intake to a zone at opposite sides of which open two control nozzles adapted to deflect the motive fluid from the axis of the duct in either one of two opposite directions, the motive fluid supply duct being extended beyond the zone by two branched ducts, at different angular inclinations with respect to the axis of the duct, namely, an exhaust duct inclined at a relatively small angle and adapted to collect motive fluid deflected in one direction and a load duct inclined at a relatively large angle and adapted to collect motive fluid deflected in the other direction, the load duct leading into the enclosure and being connected to the supply duct along a curved convex wall and being further permanently connected with one of the control nozzles through a feedback passage.
  • This invention relates to a device devoid of moving parts other than valves or cocks for adjusting it, by means of which an enclosure may be alternately filled with and emptied of a pressurized fluid (i.e. set under negative pressure with respect to a reference pressure which is preferably the atmospheric pressure).
  • a pressurized fluid i.e. set under negative pressure with respect to a reference pressure which is preferably the atmospheric pressure.
  • the invention has more particularly for its object to provide a device devoid of moving parts and enabling the above result to be achieved with great reliability.
  • a further object resides in the efficient use of the energy of a pressurized drive jet.
  • the invention lastly encompasses the application of such a device to the pumping of all fluids, and more particularly of biological fluids such as breathing air and blood, by reason of the ability of the device to reproduce the natural functional frequencies of the lungs and the heart.
  • the inventive device may be practiced with advantage as a so-called artificial heart, a blood pump or as an artificial respirator wilh the use of a breathing mask.
  • the device essentially comprises:
  • Opposed control passages substantially perpendicular to the axis of said duct, these passages being adapted to be interconnected and also to be connected individually to any convenient chamber maintained at a reference pressure, such as the atmospheric pressure;
  • An exhaust duct which extends at least to the proximity of the motive fluid supply duct;
  • a load duct which is connected through rounded sections to said supply duct and the axis of which forms with the axis of said supply duct an angle greater than the angle formed by said exhaust duct and the supply duct, said load duct terminating at the enclosure in which the pressure and mass of the fluid is to be varied; and lastly A so-called tumbler or switching duct which connects the enclosure or the load duct to one of said control passages.
  • the entire system may be executed by embodying, by any convenient methoda non-limita ive example being by machining or casting-the nozzles, passages and ducts referred to in at least one flat part made of a material which will withstand abrasion by the fiuid employed.
  • breathers Exhaustive tests carried out with the device have revealed all its functional features and have led to providing for certain alternative constructional forms adapted to specific applications.
  • the present invention consequently includes in its scope all such alternative embodiments taking the form of artificial breathing devices, hereinafter referred to as breathers.
  • breathers are strictly devoid of moving partsincluding valvesand are incorporated in a mask which can be supplied from an air or oxygen bottle, as well known per se, whereby the gas issuing from such a bottle subjects the patients lungs to an assisted periodic ventilation.
  • FIGURES 1 and 2 are respectively a plan view and a schematic fragmental section on the line II-II of FIG- URE 1, of one specific form of embodiment of the invention;
  • FIGURE 3 illustrates schematically in section how the device can be supplemented to provide a diaphragmyp P p;
  • FIGURE 4 is a schematic side elevation view in partial section, on a smaller scale, of an alternative construe tional form utilizing a liquid as the drive fluid;
  • FIGURES 5 and 6 are respectively front and side views of the essential part of a breathing mask according to the invention.
  • FIGURE 7 is a perspective view of the simplest form of embodiment of a breathing mask.
  • FIGURE 8 shows correspondingly on a smaller scale an alternative form of construction thereof.
  • FIGURES 1 and 2 shows a device according to the invention for alternately setting a cavity or enclosure 1 under an overpressure and an underpressure condition with respect to atmospheric pressure.
  • Said cavity may, for example, be a patients or an accident victims lungs.
  • the invention comprises, in the manner well known per se, at least two and in this particular example three juxtaposed plates 2a, 2b, 20 through the bodies of which are formed passages for conveying the drive fluid.
  • the latter is delivered through an intake 3 and is discharged parallel to the plates 2 by a supply duct 4.
  • Two opposed control nozzles 5 and 6 open out at the outlet zone of the supply duct 4 and each is directed substantially perpendicularly to said duct. They are interconnected by a connecting duct 7 in which a valve 70, or the like, is effective in progressively varying the crosssection through said duct, and are equipped with valves 5a and 6a respectively whereby the nozzles 5 and 6 may be progressively and independently vented to the atmosphere or connected to any other region in which prevails a reference pressure which is preferably the exhaust pressure, as will be explained hereinbelow.
  • the drive fluid supply duct 4 is extended by an exhaust duct 8 which is slightly inclined with respect to the axis of the supply duct and the flow cross-section of which increases preferably progressively in the downstream direction thereby forming a diffuser in which the drive fluid is susceptible to being recompresscd before exhausting at 9 into the atmosphere.
  • a load duct 10 connected to the cavity 1 joins onto the supply duct 4 and the exhaust duct 8 through smoothly curved convex walls 10a, 10b.
  • Said load duct also has a flow cross-section which increases progressively in the downstream direction in order to assist recompression of the drive fluidwhen the same flows towards the cavity 1, and said duct is markedly more inclined than exhaust duct 8 (again with respect to the axis of the supply duct 4).
  • a feedback passage 11 connects load duct 1t preferably at the downstream end thereof, to one of the control nozzles (the nozzle 6 in the example shown).
  • valve 6a Assuming first of all that the valve 6a is open and the valves a and 7a closed, then delivery of a pressurized drive fluid through the intake 3 and discharge of this fiuid through the supply duct 4 will result in a relative negative pressure prevailing in control nozzle 5 and the portion of duct 7 connected thereto, due to an ejector eltect.
  • a com parable negative pressure can prevail neither in 6 (which is vented to the atmosphere through valve 6a being open), nor in (by reason of the existence of passage 11).
  • the jet of drive fluid hugs the wall 8a and flows in stable fashion through the exhaust duct 8 wherein it is at least partly recompressed before issuing at J.
  • valve 5a is opened and the valve 6a closed, leaving the valve 7a closed, an ejector effect will occur in 6, 10 and 11. If the radius of curvature of the wall 10a is greater than four times the width of the duct 4, then the jet issuing from duct 4 will hug the curved wall 10a and will consequently flow at least momentarily through the load duct 10 wherein it will be recompressed. Thus the drive fluid will distend the cavity 1 and the pressure therein will rise.
  • This pressure rise will be communicated via the feedback passage 11 to the control nozzle 6 and, whilst it may not be correct to speak of a control jet as such, the transverse pressure gradient at the exit of duct 4 will be reversed and will tend to divert the jet of drive fluid towards the wall 8a and the exhaust duct 8.
  • the pressure in the cavity 1 will thus drop, ultimately even to below atmospheric pressure, due to the ejector efiect assisted by the rounded wall 101) and the divergent section of exhaust duct 8. The cycle then recommences.
  • valves 5a and 6a are both vented to the atmosphere, then valve 7a will remain without effect.
  • the jet flows alternately through duct 8 and duct 10.
  • valve 7a When valve 7a is opened, the drive jet flows alternately through duct 8 and duct 10 due to the inertia of the mass of gas contained in cavity 1. As the passageway through valve 7a increases, the frequency increases, as does also the mean value of the pressure in duct 10 and cavity 1.
  • valves 5a and 6a are closed, then when valve 7a is likewise closed the drive jet will remain in duct 8 since the negative pressure induced in control nozzle 5 will be preponderant. Through an ejector effect the jet will produce a negative pressure in cavity 1, the value of which can be exceeded with no other configuration for a given drive jet since it is not attenuated by any entry of gas.
  • valve 7a When valve 7a is opened at least beyond a certain threshold, then the drive jet will pass periodically into duct 8 and into duct 10, the preponderance of the negative pressure at 5 no longer being permanent. As the passageway through valve 7a increases, the oscillation frequency will increase and the maximum negative pressure in cavity 1 will drop in absolute value.
  • valve 5a If valve 5a is vented to the atmosphere and valve 6a is closed, then the drive jet will flow alternatively into duct 8 and duct 10. (Due to an ejector effect, control nozzle 6 and the system 10, 11, I tend to be set under negative pressure, thus tending to cause the drive jet to hug wall 10a and fill cavity 1. The resulting overpressure diverts the jet into exhaust duct 8.)
  • valve 7a As valve 7a is gradually opened, the value of the negative pressure increases in cavity 1, while the overpressure decreases and the frequency increases.
  • a bladder 12 made of fluidtight, deformable and preferably elastic material, mounted in the cavity 1 and connected to any convenient pipe 14 fitted with two non-return valves 13a, 13b. Variations in the mass of drive fluid contained in cavity 1 cause the volume of bladder 12 to vary and the fluid to be pumped to flow through the line 14 and to be checked alternately by valves 13a and 13b.
  • a device of this type could constitute a blood pump, or artificial heart.
  • FIGURE 4 shows an alternative form of embodiment of the device of FIGURES 1 and 2, in which the drive fluid is a liquid.
  • FIGURE 4 clearly shows, the device 2 proper is submerged in a tank which is almost filled with liquid and into which the valves 5a and 6a open.
  • the supply is effected by a submerged pump 16, of the centrifugal type for instance, which is driven by an electric motor 17 and feeds the intake 3.
  • the latter is fitted with a pressure gauge 18 and a valve-type by-pass 19, for varying the pressure of the drive fluid.
  • the tank 15 may be filled with pressurized air or conversely be maintained at a negative pressure relatively to the atmosphere by means of the pump 16.
  • a number at least of the valves 5a, 6a and 7a may be interconnected whereby to enable them to be controlled by a single lever.
  • FIGURES 5 and 6 like parts (to FIGURES 1 and 2) are used for the most part and are designated by like reference numerals.
  • the interconnecting duct 7 and the valves 6a and 7a are dispensed with, while the valve 5a is replaced by a filter which places the passage in communication with the cavity (including the patients lungs), which cavity is positioned behind the mask 24.
  • the subject device of the invention is mounted for instance on this mask, by simply engaging a peripheral flange formed thereon into a suitable groove in the mask.
  • the latter is preferably made of plastic.
  • the configuration of the device of FIGURES 5 and 6 may be likened to that corresponding to line 3/2 of the table above, in which the control nozzles 5 and 6 both communicate with the cavity 1 due to opening of the valve 7a alone.
  • the chief advantage of dispensing with the duct 7 interconnecting these two control nozzles is that, in the event of its becoming obstructed by food particles or the like, there is no further danger of the patients lungs being set under a permanent negative pressure (see lines 2/1 and 3/ 1 of the table above, which corresponds to closure of valve 7a).
  • the filter 25 prevents such obstruction of nozzle 5.
  • the device shown in FIGURE 7 corresponds similarly to line 4/1 of the table. It will be seen that its oscillation frequency is for all practical purposes lower than that of the device of FIGURES 5 and 6, in which the exhalation period is shorter. Said oscillation frequency can be lowered to some extent by replacing the filter 25 by one having a lower pressure loss, thereby adapting the frequency to the patients natural breathing rate.
  • a fluid amplifier device operable with a source of motive fluid for alternately filling and emptying an enclosure comprising a motive fluid intake to be connected to said source, a motive fluid supply duct leading from said intake and having two opposite sides, two control nozzles opening into said supply duct at said opposite sides thereof and adapted to deflect the motive fluid supplied by said duct away from the axis thereof in either one of two opposite directions, two branched ducts extending said motive fluid supply duct beyond said control nozzles respectively in said opposite directions and at different angular inclinations with respect to said axis, one of said branched ducts being an exhaust duct forming a branch of said supply duct extending the same beyond said control nozzles at a relatively small angle of inclination with respect to the axis of said supply duct, said exhaust duct being adapted to collect said motive fluid when the same is deflected in one of said two opposite directions and to lead said fluid to exhaust, the other of said branched ducts being a load duct leading into said enclosure
  • a device as claimed in claim 4 further comprising filtering means interposed into the communication of said enclosure with that one of said two control nozzles which is opposite to the one permanently connected with said feedback passage.
  • both said control nozzles are isolated from an ambient medium in at least one operative condition of said device.
  • a device as claimed in claim 7 further comprising valve means for selectively and controllably connecting each of said control nozzles to said ambient medium.
  • a device as claimed in claim 1 wherein said enclosure comprises a deformable fluid-tight membrane bounding at least partly a variable-volume, liquid pumping chamber.
  • a device as claimed in claim 12 wherein said liquid pumping chamber is an artificial heart for pumping blood.
  • a device as claimed in claim 1 wherein said enclosure comprises a breathing mask adapted to be fitted on a patients face and to communicate with his respiratory system, whereby said device operates as an artificial respirator.
  • a device as claimed in claim 14 further comprising a balloon fitted on said mask and communicating with the interior thereof.

Landscapes

  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Veterinary Medicine (AREA)
  • General Engineering & Computer Science (AREA)
  • Mechanical Engineering (AREA)
  • Theoretical Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Fluid Mechanics (AREA)
  • Percussion Or Vibration Massage (AREA)
  • Respiratory Apparatuses And Protective Means (AREA)
US47569665 1964-08-05 1965-07-29 Fluidic device for alternately filling and emptying an enclosure Expired - Lifetime US3389698A (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
FR984284A FR1415619A (fr) 1964-08-05 1964-08-05 Dispositif permettant de remplir et vider alternativement une cavité avec un fluide
FR8535A FR87533E (fr) 1964-08-05 1965-03-09 Dispositif permettant de remplir et vider alternativement une cavité avec un fluide

Publications (1)

Publication Number Publication Date
US3389698A true US3389698A (en) 1968-06-25

Family

ID=26162326

Family Applications (1)

Application Number Title Priority Date Filing Date
US47569665 Expired - Lifetime US3389698A (en) 1964-08-05 1965-07-29 Fluidic device for alternately filling and emptying an enclosure

Country Status (5)

Country Link
US (1) US3389698A (fr)
BE (1) BE667721A (fr)
DE (1) DE1503678B2 (fr)
FR (2) FR1415619A (fr)
GB (1) GB1112365A (fr)

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3435822A (en) * 1965-06-29 1969-04-01 United Aircraft Corp Breathing apparatus with fluid diode valve
US3586021A (en) * 1968-11-26 1971-06-22 Bowles Fluidics Corp Fluidic breathing assistor
US4120300A (en) * 1976-11-29 1978-10-17 City Of Hope National Medical Center Breathing apparatus
US4151843A (en) * 1976-06-28 1979-05-01 Brekke John H Apparatus for administration of a gas to a human and the exhausting thereof
WO1982001815A1 (fr) * 1980-11-26 1982-06-10 Ind Inc Tritec Procede et appareil de masque respiratoire
NL1040590C2 (nl) * 2014-01-07 2015-07-08 Alcmair Partners B V Leidingsysteem voor een inrichting voor het beademen van patiënten.
WO2021191820A1 (fr) * 2020-03-24 2021-09-30 Jfd Ltd Collecteur et système de ventilation

Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3122165A (en) * 1960-09-19 1964-02-25 Billy M Horton Fluid-operated system
US3176920A (en) * 1961-05-26 1965-04-06 Honeywell Inc Fluid operated pump
US3196866A (en) * 1962-10-31 1965-07-27 Commw Ind Gases Resuscitator
US3208448A (en) * 1962-02-02 1965-09-28 Kenneth E Woodward Artificial heart pump circulation system
US3217727A (en) * 1963-09-10 1965-11-16 Chris E Spyropoulos Pneumatic relaxation oscillator
US3238961A (en) * 1963-10-10 1966-03-08 Foxboro Co Fluid switch
US3244189A (en) * 1963-10-04 1966-04-05 Feedback Systems Inc Fluid valve device
US3267948A (en) * 1963-08-15 1966-08-23 Sperry Rand Corp Fluid logic apparatus
US3267947A (en) * 1963-06-17 1966-08-23 Romald E Bowles Pressure recovery from bistable element
US3280832A (en) * 1963-11-18 1966-10-25 Retec Inc Cycling valve
US3285265A (en) * 1964-04-17 1966-11-15 Gen Electric Fluid amplifier devices
US3292623A (en) * 1964-02-24 1966-12-20 Raymond W Warren Respirator
US3295543A (en) * 1959-12-15 1967-01-03 Pneumo Hydraulic Automatic Con Method of automatically controlling pneumatic or hydraulic elements of instruments and other devices

Patent Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3295543A (en) * 1959-12-15 1967-01-03 Pneumo Hydraulic Automatic Con Method of automatically controlling pneumatic or hydraulic elements of instruments and other devices
US3122165A (en) * 1960-09-19 1964-02-25 Billy M Horton Fluid-operated system
US3176920A (en) * 1961-05-26 1965-04-06 Honeywell Inc Fluid operated pump
US3208448A (en) * 1962-02-02 1965-09-28 Kenneth E Woodward Artificial heart pump circulation system
US3196866A (en) * 1962-10-31 1965-07-27 Commw Ind Gases Resuscitator
US3267947A (en) * 1963-06-17 1966-08-23 Romald E Bowles Pressure recovery from bistable element
US3267948A (en) * 1963-08-15 1966-08-23 Sperry Rand Corp Fluid logic apparatus
US3217727A (en) * 1963-09-10 1965-11-16 Chris E Spyropoulos Pneumatic relaxation oscillator
US3244189A (en) * 1963-10-04 1966-04-05 Feedback Systems Inc Fluid valve device
US3238961A (en) * 1963-10-10 1966-03-08 Foxboro Co Fluid switch
US3280832A (en) * 1963-11-18 1966-10-25 Retec Inc Cycling valve
US3292623A (en) * 1964-02-24 1966-12-20 Raymond W Warren Respirator
US3285265A (en) * 1964-04-17 1966-11-15 Gen Electric Fluid amplifier devices

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3435822A (en) * 1965-06-29 1969-04-01 United Aircraft Corp Breathing apparatus with fluid diode valve
US3586021A (en) * 1968-11-26 1971-06-22 Bowles Fluidics Corp Fluidic breathing assistor
US4151843A (en) * 1976-06-28 1979-05-01 Brekke John H Apparatus for administration of a gas to a human and the exhausting thereof
US4120300A (en) * 1976-11-29 1978-10-17 City Of Hope National Medical Center Breathing apparatus
WO1982001815A1 (fr) * 1980-11-26 1982-06-10 Ind Inc Tritec Procede et appareil de masque respiratoire
NL1040590C2 (nl) * 2014-01-07 2015-07-08 Alcmair Partners B V Leidingsysteem voor een inrichting voor het beademen van patiënten.
WO2015105415A1 (fr) * 2014-01-07 2015-07-16 Alcmair Partners Bv Système de ligne pour un appareil pour la respiration de patients
US11389613B2 (en) 2014-01-07 2022-07-19 Löwenstein Medical Technology Sa Line system for an apparatus for the respirating of patients
WO2021191820A1 (fr) * 2020-03-24 2021-09-30 Jfd Ltd Collecteur et système de ventilation

Also Published As

Publication number Publication date
DE1503678A1 (de) 1969-10-30
FR87533E (fr) 1966-06-24
DE1503678B2 (de) 1971-04-15
GB1112365A (en) 1968-05-01
BE667721A (fr) 1966-01-31
FR1415619A (fr) 1965-10-29

Similar Documents

Publication Publication Date Title
US4657160A (en) Pressure infusion control
US3700000A (en) Valve arrangement,especially for use in anaesthetic gas supply systems
US4278110A (en) Demand responsive flow controller
US5411472A (en) Low trauma blood recovery system
US4575042A (en) Pneumatically amplified conservation valve
CA1073303A (fr) Systeme pressostatique de collection de fluides
US3389698A (en) Fluidic device for alternately filling and emptying an enclosure
US3730180A (en) Pneumatically operated ventilator
WO1999049216A8 (fr) Pompe a vide a ejecteur
GB2137887A (en) Respiratory apparatus
EP0273714A3 (fr) Ensemble de pompe péristaltique
AU696318B2 (en) A device for the pulsed pumping of liquids, particularly blood
US3379194A (en) Fluid amplifier controlled respirator
US2268172A (en) Resuscitator
GB1378701A (en) Pressure modulator for and artificial bloodcircuit
US3465752A (en) Apparatus for the control of pressure respirator
DE69006982D1 (de) Ventil und mit diesem Ventil ausgerüstete Vorrichtung.
US4632107A (en) High-frequency jet ventilator
US2364626A (en) Resuscitator
US3292623A (en) Respirator
US5261897A (en) Portable suction system
US3522816A (en) Fluid system for filling and emptying an enclosure
JPH01148129A (ja) 潅漑液の自動律動供給装置
US3565091A (en) Fluid pump and regulator
US3435822A (en) Breathing apparatus with fluid diode valve