EP0188548A1 - PROCEDE ET APPAREIL POUR AMENER DES MELANGES GAZEUX A UN SYSTEME RESPIRATOIRE $i(IN VIVO) - Google Patents

PROCEDE ET APPAREIL POUR AMENER DES MELANGES GAZEUX A UN SYSTEME RESPIRATOIRE $i(IN VIVO)

Info

Publication number
EP0188548A1
EP0188548A1 EP85903606A EP85903606A EP0188548A1 EP 0188548 A1 EP0188548 A1 EP 0188548A1 EP 85903606 A EP85903606 A EP 85903606A EP 85903606 A EP85903606 A EP 85903606A EP 0188548 A1 EP0188548 A1 EP 0188548A1
Authority
EP
European Patent Office
Prior art keywords
gas
respiratory system
port
vivo respiratory
vivo
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.)
Withdrawn
Application number
EP85903606A
Other languages
German (de)
English (en)
Inventor
Leonard M. Sieracki
Gerald P. Durkan
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.)
Individual
Original Assignee
Individual
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 Individual filed Critical Individual
Publication of EP0188548A1 publication Critical patent/EP0188548A1/fr
Withdrawn legal-status Critical Current

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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
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/104—Preparation of respiratory gases or vapours specially adapted for anaesthetics
    • 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
    • A61M16/0003—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

  • This invention pertains to apparatus and methods for providing gas mixtures to an in vivo respiratory system.
  • a second gas such as a sedation agent
  • a first gas or respirating gas such as oxygen
  • the amount of the supplied gas should generally be in controlled relation to the amount of respirating gas.
  • U.S. patent application S.N. 446,542 filed 3 December 1982 by the Applicants herein, now U.S. patent 4,462,393 discloses an embodiment wherein both respirating gas and a second gas are supplied to an in vivo respiratory system.
  • the same circuit controls a rirst or respirating gas valve means and a second gas valve means- through which the respective gases are supplied to the in vivo respiratory system.
  • examples of the types of gases which can be supplied along with respirating gas to a patient to achieve a sedative effect include anesthetic gases and analgesic gases.
  • Analgesic gases include anesthetic gases and analgesic gases.
  • a typical prior art analgesic gas delivery system employed in such a setting includes the mixing of the- analgesic gas (such as nitrous oxide) and oxygen
  • prior art analgesic gas delivery systems comprise sources for each gas and respective associated flowmeters.
  • the flowmeter associated with the nitrous oxide source is generally
  • the mixing valve has an output port connected to a nasal mask worn by the patient.
  • prior art sedative gas delivery systems operate in a continuous flow mode to provide gases to the patient throughout the respiratory cycle.
  • the typical concentration of nitrous oxide is about 25% to 50% of
  • the total gas mixture is a function inter alia of the patient's state of anxiety and physiological characteristics.
  • the application of the analgesic normally starts with a supply of essentially 100% oxygen.
  • the supply of oxygen is then gradually decreased while the supply of nitrous oxide is increased until the desired sedation effect has- taken place.
  • the supply of oxygen must not cease, and in any event the sedative gas should certainly not be supplied absent the essentially simultaneous supply of an appropriate volume of oxygen. If the oxygen level in the oxygen nitrous oxide mixture is insufficient, brain damage can occur.
  • practioners In view of the serious problems which develop when oxygen is not being properly supplied to a patient receiving a sedating gas in a total tidal volume system, practioners must continuously monitor the condition of the patient's respiratory system and the supply of oxygen to the patient. To some extent prior art devices have endeavored to help the practioner monitor the patient and the oxygen supply. For example, many prior art sedative gas delivery system include a safety mechanism to shut off the supply of nitrous oxide, when an oxygen valve is closed. In addition, some vendors of bottled oxygen and bottled nitrous oxide have an audible alarm associated with the bottles to indicate low pressure and thus hopefully avoid the unexpected interruption of gas supply. Another device, disclosed by SCURLOCK in U.S.
  • sedative gas delivery systems A further concern regarding sedative gas delivery systems is that sedative gas not be wasted and that only minimal amounts of the sedative gas be leaked to the atmosphere. Sedative gases are rather expensive and their presence in the atmosphere is not desirable. Recent studies have shown increases in spontaneous abortion and congenital abnormalities in children of workers exposed to nitrous oxide. The potential risks of hepatic and renal disease, cancer, and central nervous system disorders among exposed personnel have also apparently increased.
  • An advantage of the present invention is the provision of method and apparatus for automatically terminating the supply of a sedative gas if the application of a respirating gas ceases.
  • a further advantage of the present invention is the provision of method and apparatus for providing a sedative gas to an in vivo respiratory system in accordance with inspiratory demand.
  • Yet a further advantage of the invention is the provision of a demand respirating gas supply method and apparatus which employs a single line, thereby allowing pressure sensing and gas supply to be accomplished through the same line.
  • a homogenous mixture of a sedative gas and a respirating gas is supplied upon inspiratory demand to an in vivo respiratory system.
  • the sedative gas is included in the mixture supplied to the in vivo respiratory system upon inspiratory demand essentially only if the respirating gas is simultaneously being supplied to the in vivo respiratory system.
  • a sensor detects an occurrence of negative pressure as an indication of inspiration in the in vivo respiratory system.
  • a respirating gas supply valve responsive to the sensor communicates the respirating gas to the in vivo respiratory system.
  • a second sensor detects the
  • a sedative gas supply valve operating in response with the second sensor allows sedative gas to be transmitted to the in vivo system along with the respirating gas in accordance with the detected supply of the respirating gas.
  • the second sensor comprises a pressure to electric sensor which upon detecting pressure associated with the supply of respirating gas actuates an electrically- operated sedative gas supply valve.
  • the second sensor comprises fluidic circuitry wherein the supplied respirating gas is utilized to actuate a pneumatically-operated sedative gas supply valve.
  • Various ones of the embodiments described above employ a three-way valve as the respirating gas supply valve.
  • the three-way valve has ports connected to the first sensor, the source of the -respirating gas, and to a single line used to communicate gas to an interface.or application means worn by, attached to, or inserted in the in vivo respiratory system.
  • FIG. 1 is a schematic diagram showing apparatus for supplying gas mixtures according to a first embodiment of the invention
  • Fig. 2 is a schematic diagram showing apparatus for supplying gas mixtures according to a second embodiment of the invention. and, -7-
  • Fig. 3. is a schematic diagram of a fluidic control circuit -of the embodiment of Fig. 2.
  • Fig. 1 shows a hybrid electrical/fluidic apparatus for supplying two gases mixed in such a manner as to supply a homogenous mixture of gases to an in vivo respiratory system.
  • the apparatus of the embodiment of Fig. 1 comprises a source 20 of a first or respirating gas (such as oxygen); a source 22 of a second or sedative gas (such as nitrous oxide, for example); first sensor means 24; second sensor means 26; a first flowmeter 28; a second flowmeter 30; first valve means 32; second valve means 34; and, application or interface means for supplying the mixture to the in vivo respiratory system (such as a nasal mask 36).
  • a source 20 of a first or respirating gas such as oxygen
  • a source 22 of a second or sedative gas such as nitrous oxide, for example
  • first sensor means 24 such as oxygen
  • second sensor means 26 such as a first flowmeter 28
  • a second flowmeter 30 such as a second flowmeter 30
  • first valve means 32 such as a nasal mask 36
  • a master switch 40 functions as a three-way contact switch for selecting whether the apparatus is to function in a continuous supply mode of operation; in a demand dose supply mode of operation; or, whether the supply of gases is to be turned off.
  • two further 3-way switches 42 and 44 are slaved to the master switch 40.
  • Switch 42 is on a line 46 which is connected to the first source 20.
  • Switch 44 is on a line 48 which is connected to the second source 22.
  • In its "continuous" position switch 42 enables the source 20 to communicate with a line 50 during the continuous supply mode of operation.
  • In its "dose" position switch 42 enables the source 20 to communicate with a line 52 during the demand dose supply mode of operation.
  • the "continuous" position switch 44 enables the source 22 to communicate with a line 54 during the continuous supply mode of operation, while in its "dose” position switch 44 enables the source 22 to communicate with a line 56 during a demand dose supply mode of -8- operation.
  • the second gas supplied by source 22 is a sedative gas such as an • anesthesia or an analgesic.
  • the first sensor means 24 comprises a fluidic logic element such as a fluid amplifier 60 and a pressure-to-electric conversion means such as P/E switch 62.
  • the fluid logic element 60 has an input or power port 60a; control ports 60b and 60c; and, output ports 60d and 60e.
  • the input or power port 60a is connected to fluidic line 52 by a fluidic line 61 having a variable flow restrictor thereon.
  • the output port 60d is connected by a fluidic line 64 to a pressure sensitive input port 62a of the P/E switch 62.
  • An output port 62b of the P/E switch 62 is connected by electrical conductor 66 to an input terminal 68a of a control circuit 68.
  • the first valve means 32 is a two-position three-port solenoid spool valve having ports 32a, 32b, and 32c. In a first position of the valve means 32 the port 32a is communicable with port 32c. In a second position of the valve means port 32a is communicable with port 32b. Port 32a is connected to the in vivo respiratory system through fluidic line 72. Port 32b is selectively communicable through lines 52 and 46 to the source 20 of the- first gas. The port 32c is selectively communicable with the control port 60b of sensor 60 through fluidic line 74.
  • the continuous mode supply line 50 connects with line 72 at a point 76. Downstream from point 76 at a point 78 a fluidic ine 80 connects with fluidic line 72. The end of fluidic line 80 which is not connected to line 72 is connected to a pressure -9- sensitive input port 26a of the second sensor means such as P/E switch 26. The electrical output terminal 26b of the P/E switch 26 is connected by electrical conductor 82 to the electrical terminal of the second valve means 34.
  • the second valve means 34 is, in the illustrated embodiment of Fig. 1, a two-position, two- port solenoid spool valve having ports 34a and 34b. In a first position of the valve means 34 port 34a does not communicate with port 34b; in a second position the ports 3.4a and 34b do communicate. Port 34a communicates with the in vivo respiratory system through a fluidic line 84. The port 34b selectively communicates through lines 56 and 48 to the source 22 of the second or sedative gas.
  • the continuous mode supply line 54 connects with line 84 at a point 85. Downstream from point 85 at a point 86 a fluidic line 87 connects with fluidic line 84. The end of fluidic line 87 which is not connected to line 84 is connected to a pressure sensitive input port 88a of a P/E switch 88. The electrical output terminal of 88b of the P/E switch 88 is connected by electrical conductor 89 to an LED as hereinafter described. Fluidic lines 90 and 91 are connected to output ports 28b and 30b of flowmeters 28 and 30, respectively. Flowmeters 28 and 30 are both of a type having an orifice-type selector valve.
  • a single line 93 connects the "T" coupling 92 to the application or interface means such as the nasal mask 36. It should be understood that various types of interface or application means other than a nasal cannula are used in differing embodiments, such as a nasal cannula.
  • An apnea alarm circuit 95 is connected by electrical conductor 96 to an output terminal 68c of the control cirucit 68.
  • the circuit details of both the control circuit 68 and the apnea event detection/alarm circuit 95 are basically disclosed in U.S. patent application S.N. 446,542 filed 3 December 1982 and incorporated herein by reference.
  • P/E switch 62 of the presently described embodiment closes a switch in control circuit 68 in the manner in which switch 36 is closed in circuit 32 of the incorporated application.
  • conductor 70 of the present invention basically corresponds to line L3 of the incorporated application for controlling the solenoid valve 32.
  • a difference between the circuit 32 shown in the incorporated application and the circuits 68 and 95 of the* present invention is the value of the 100K variable potential resistor R2 of the circuit 32 of the incorporated application.
  • the value of the resistor R2 should be set so that a dose sufficient to last at least for the duration of normal inspiration is supplied, such as a dose lasting about 1.5 seconds, for example.
  • the apparatus of Fig. 1 also includes a control pannel 97 having various diagnostic indicators thereon.
  • a. first indicator device such as light-emitting diode (LED) 98, is connected by electrical conductors 99 and 82 to the output terminal 26b of P/E switch 26.
  • LED 96 When LED 96 is lit an indication is provided that the first gas or respiratory gas is being supplied on line 72.
  • a second LED 100. is connected by electrical conductor 110 to an output
  • LED 100 essentially corresponds to LED 94 of the incorporated application Serial Number 446,542.
  • LED 94 provides an indication that the in vivo respiratory system has not attempted an inspiration within a predetermined interval of time from the previous inspiration.
  • a third LED 112 is connected by electrical conductor 89 to the output terminal 88b of the P/E switch 88 as described above. When lit, the LED 112 provides an indication that ports 34a and 34b of valve means 34 are communicating with one another to thus permit the supply of the second or sedative gas on line 84.
  • the embodiment of Fig. 2 resembles the embodiment of Fig. 1 but is a primarily fluidic rather than a hybrid electric fluidic system.
  • the output port 60d of the fluidic logic element 60 is connected to an input terminal 150a of a fluidic control circuit 150.
  • the structural details of the fluidic control circuit 150 are seen hereinafter with reference to Fig. 3.
  • a output terminal 150b of the fluidic control circuit is connected by fluidic line 152 to an input port 154a of a pilot valve 154.
  • An output port 154b of the pilot valve 154 is connected by fluidic line 156 to the control terminal of a pressure-activated solenoid valve 32'.
  • the port connections of fluidic valve 32' are similar to the port connection of the valve 32 of Fig. 1 as described hereinbefore, it being understood that valve 32'. is a pressure-activated solenoid spool valve while the valve 32 is an electrically-activated solenoid spool valve.
  • a second output terminal 154c of the pilot valve 154 is connected by a fluidic line 164 to an apnea event detection/alarm circuit 95'.
  • the circuit 95' is not considered a part of the present invention -12- but is in one embodiment a fluidic timing circuit such as circuit 10 shown in U.S. patent 4,414,982 which is incorporated herein by reference.
  • the fluidic line 80 of the embodiment of Fig. 2 connects line 72 to a pressure input port 26a' of a fluidic pilot valve 26'.
  • An output port 26b' of the pilot valve 26' is connected by fluidic line 166 to the fluidic control terminal of second valve means 34'.
  • the second valve means 34' comprises a fluidic pressure-activated, two-stage, two- port solenoid spool valve having ports 34a' and 34b* selectively communicable in the fashion of the second valve means 34 of the embodiment of Fig. 1.
  • the second terminal 26b' of the pilot valve 26' is also connected by a line 167 to a pressure sensitive input terminal 168a of a P/E switch 168.
  • the output terminal 168b of the switch 168 is connected by electrical conductor 170 to the LED 96.
  • Fig. 2 is shown in detail in Fig. 3.
  • the control circuit 150 has an input port 150a connected to line 64' and an output port 150b connected to line 152.
  • the control circuit 150 comprises a fluidic one shot 180 and a substantially closed-loop fluidic path 182 having one or more timing means thereon.
  • the fluidic one shot element 180 of control circuit 150 has a power input 180a; control ports 180b and 180c; and, output ports 180d and 180e.
  • Power input port 180a is ultimately connected through appropriate conventional flow restrictor devices to a fluidic source such as source 20, for example.
  • Control port 180b is connected to input port 150a.
  • Output port 180d is formed whereby the power stream is discharged therefrom to atmosphere when pressure is equalized at control ports 180b and 180c.
  • Output port 180e is formed whereby the power stream is discharged to create a fluidic signal on line 152 when the pressure at control port 180b exceeds the pressure at control port 180c.
  • the closed-loop fluidic path 182 has a first end connected to the input port 150a and a second end connected to control port 180c of the one shot 180.
  • the timing means shown in Fig. 3 on the fluidic path 182 comprise a fluid restrictive device 184 and a capacitance device 186.
  • the restrictor 184 is a variable resistor and the capacitance 186 is a variable capacitance, such as an elastomeric balloon.
  • the values of the restrictive device 184 and capacitance 186 are chosen whereby the time delay for the equilization of pressures at control ports 180b and 180c is at least as great as the duration of normal inspiration such as about 1.5 seconds, for example.
  • an operator first manipulates the master switch 40 to select the desired mode. If a continuous supply mode is selected, switch 40 controls switches 42 and 44 whereby line 50 communicates with line 46 and line 54 communicates with line 48. If a demand dose supply mode is selected, switch 40 controls switches 42 and 44 whereby line 52 communicates with line 46 and line 56 communicates with line 48. The operation of the demand dose supply mode is discussed hereinafter under the assumption that master switch 44 is manipulated to be in the "dose" position.
  • the operator then sets the flowmeters 28 and 30 to establish desired flow rates for the respective gases.
  • the first flowmeter 28 is adjustable through a range from approximately three to
  • the first flowmeter 28 is used to control the flow of oxygen.
  • the second flowmeter 30 is adjustable through a range of from approximately zero to approximately eight liters per minute and, in the illustrated example., is used to control the flow of a sedative gas such as nitrous oxide.
  • the operator is then ready to install the interface or application device so that the homogenous mixture of gases. can be supplied to the in vivo respiratory system.
  • nasal mask 36 is inserted over the nose.
  • control circuit 68 uses the electrical signal on conductor 66 to generate an electrical signal on conductor 70 for actuating the • electrical solenoid valve means 32. . Actuation of the
  • valve means 32 by the application of a signal on conductor 70 causes the spool valve to slide to a position whereat port 32a is connected to port 32b.
  • the first gas is supplied from the source 20 along lines 46 and 52, through the valve 32, along line 72, through flowmeter 28, and along lines 90 and 93 for application to the in vivo respiratory system.
  • the control circuit 68 actuates valve means 32 to supply gas from source 20 for a duration at least as long as the duration of normal inspiration.
  • the second sensor means 26 senses the supply of the first gas on line 72.
  • supply of the first gas on line 72 also creates a pressure on line 80 which activates the pressure sensitive input port 26a of the P/E switch 26.
  • Pressure at the input port 26a of switch 26 causes the P/E switch 26 to generate an electrical signal at its output port 26b.
  • the electrical signal at output port 26b is transmitted on electrical conductor 82 to the electrical terminal of the electrical solenoid spool valve 34.
  • the application of electrical signal at the electrical terminal of the valve 34 actuates the valve 34 whereby valve 34 moves to a position where port 34a communicates with port 34b.
  • Fig. 2 basically resembles the operation of Fig. 1. It should be understood,
  • the fluidic output signal for port 60d is applied to the input port 150a of the fluidic control circuit 150.
  • An output signal is generated by control circuit 150 on line 152 for a time duration determined by the timing means on the closed-loop path 182 of circuit 150..
  • the values of the timing means 184 and 186 on path 182 are so chosen whereby the time delay before pressures equilize at control ports 180b and 180c is at least as great as the duration of normal inspiration.
  • circuit 150 ceases generation of the output signal on line 152.
  • the output signal of the fluidic control circuit 150 is applied on fluidic line 152 to the input terminal 154a of the pilot valve 154.
  • a fluidic signal at the output port 154d causes the solenoid spool valve 32' to move to the position whereat port 32a' is connected to port 32b' , thereby causing the first gas to be supplied to the in vivo respiratory system in substantially the aforedescribed manner.
  • the pressure on line 72 created by the supply of first gas is incident upon the input port 26a' of pilot valve 26', causing the pilot valve 26' to generate a fluidic output signal on line 166.
  • the signal on line 166 actuates the solenoid valve 34' whereby port 34a' is connected to port 34b' for permitting the second gas to be supplied and mixed homogeneously in substantially the aforedescribed manner.
  • master switch 44 ' When master switch 44 ' is manipulated to be in the "continuous" position the first gas from source 20 is continually supplied on lines 46, 50, 72, and 90 from source 22 and the second from source 22 on lines 48, 54, and 91 to point 92 whereat the first and second gases are homogeneously mixed for continuous application on line 93 and via mask 36 to the in vivo respiratory system.

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  • Health & Medical Sciences (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Respiratory Apparatuses And Protective Means (AREA)

Abstract

Un mélange homogène d'un gaz sédatif et d'un gaz de respiration est fourni sur demande inspiratoire à un système respiratoire in vivo. Le gaz sédatif est inclus dans le mélange fourni au système respiratoire in vivo après demande inspiratoire seulement en cas d'alimentation simultanée du gaz de respiration au système respiratoire in vivo. Un capteur (24) détecte l'apparition d'une pression négative indicatrice d'une inspiration dans le système respiratoire in vivo. Une soupape d'alimentation de gaz de respiration (32) répondant au capteur (24) communique le gaz de respiration au système respiratoire in vivo. Un second capteur détecte la communication du gaz de respiration au système in vivo. Une soupape d'alimentation de gaz de sédatif fonctionnant en réponse au second capteur permet la transmission du gaz sédatif au système in vivo de concert avec le gaz de respiration en conformité avec l'alimentation détectée du gaz de respiration. Dans un mode de réalisation, le second capteur comporte une pression pour le capteur électrique (26) qui, après détection de la pression associée à l'alimentation du gaz de respiration, actionne une soupape d'alimentation de gaz sédatif à actionnement électrique (34). Dans un autre mode de réalisation, le second capteur comporte un ensemble de circuits de fluide où le gaz de respiration fourni est utilisé pour actionner une soupape d'alimentation de gaz sédatif à actionnement pneumatique (34').
EP85903606A 1984-07-09 1985-07-09 PROCEDE ET APPAREIL POUR AMENER DES MELANGES GAZEUX A UN SYSTEME RESPIRATOIRE $i(IN VIVO) Withdrawn EP0188548A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US62913584A 1984-07-09 1984-07-09
US629135 1984-07-09

Publications (1)

Publication Number Publication Date
EP0188548A1 true EP0188548A1 (fr) 1986-07-30

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EP85903606A Withdrawn EP0188548A1 (fr) 1984-07-09 1985-07-09 PROCEDE ET APPAREIL POUR AMENER DES MELANGES GAZEUX A UN SYSTEME RESPIRATOIRE $i(IN VIVO)

Country Status (3)

Country Link
EP (1) EP0188548A1 (fr)
AU (1) AU4634385A (fr)
WO (1) WO1986000537A1 (fr)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ES2122656T3 (es) * 1994-06-07 1998-12-16 United Parcel Service Inc Procedimiento y aparato para descodificar simbolos bidimensionales en el dominio espacial.

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Publication number Priority date Publication date Assignee Title
US2830580A (en) * 1952-10-21 1958-04-15 Saklad Meyer Electronically controlled respiratory apparatus
US3357428A (en) * 1963-12-23 1967-12-12 David L Carlson Respiratory augmentor with electronic monitor and control
US3831596A (en) * 1971-11-10 1974-08-27 Synthelabo Control device for a respiratory apparatus
US4003372A (en) * 1975-10-06 1977-01-18 The Raymond Lee Organization, Inc. Foot washing and massaging device
GB1576118A (en) * 1976-06-02 1980-10-01 Boc Ltd Lung ventilators
US4215409A (en) * 1978-03-13 1980-07-29 Mckesson Company Flow control system for anesthesia apparatus
US4328823A (en) * 1980-05-14 1982-05-11 N.A.D. Inc. Oxygen flow ratio controller for anesthesia apparatus
US4461293A (en) * 1982-12-03 1984-07-24 Kircaldie, Randall, And Mcnab Respirating gas supply method and apparatus therefor

Non-Patent Citations (1)

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Title
See references of WO8600537A1 *

Also Published As

Publication number Publication date
AU4634385A (en) 1986-02-10
WO1986000537A1 (fr) 1986-01-30

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