WO1989011245A1 - Systeme d'interface avec un patient et procede de prevention de la contamination de l'eau - Google Patents

Systeme d'interface avec un patient et procede de prevention de la contamination de l'eau Download PDF

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Publication number
WO1989011245A1
WO1989011245A1 PCT/US1989/001974 US8901974W WO8911245A1 WO 1989011245 A1 WO1989011245 A1 WO 1989011245A1 US 8901974 W US8901974 W US 8901974W WO 8911245 A1 WO8911245 A1 WO 8911245A1
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WO
WIPO (PCT)
Prior art keywords
sample
patient
section
gas
water vapor
Prior art date
Application number
PCT/US1989/001974
Other languages
English (en)
Inventor
Dennis L. Coleman
Charles V. Owen
Noel De Nevers
Original Assignee
Albion Instruments
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 Albion Instruments filed Critical Albion Instruments
Priority to KR1019900700104A priority Critical patent/KR900701352A/ko
Publication of WO1989011245A1 publication Critical patent/WO1989011245A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A61B5/083—Measuring rate of metabolism by using breath test, e.g. measuring rate of oxygen consumption
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/06—Radiation therapy using light

Definitions

  • This invention relates to a system and method of interfacing a patient with monitoring equipment that monitors inspired and expired gases, and more particularly, to a system and method for preventing condensed water or other liquids from entering the detection portion of the monitoring equipment.
  • Respiratory and anesthetic gas monitoring has achieved a high standard of technological advancement with the development of monitoring techniques that enable quick diagnosis and treatment of unfavorable trends in the condition of a patient, improved survival rates, early extubation following surgery and shorter times in intensive care units.
  • Applications of respiratory gas and anesthetic agent monitoring include the measurement of oxygen consumption, carbon dioxide production, anesthetic agent uptake and the detection of anesthesia machine circuit disconnections and introduction of air emboli into the blood.
  • Continuous analysis of patients' respiratory and anesthetic gases is becoming increasingly important in improving patient safety during the course of treatment. For example, breath-by-breath monitoring of the concentrations and identity of the anesthetic agents present in a patient's respiratory gases leads to a more scientific basis for the administration and control of the anesthetic agents.
  • Continuous, breath-by-breath monitoring of a patient's respiratory gases and simultaneous determination of multiple specific respiratory gases and anesthetic agents in the patient's system can often facilitate diagnosis and treatment, anticipate and prevent the development of oncoming problems, and otherwise provide instant data for physicians and other health care personnel to use in therapeutic situations.
  • Measurements of any gas of interest in a patient's breath can be sampled on a continuous basis and monitored by an appropriate type of gas analyzer. For example, when monitoring a patient's carbon dioxide level, a sharp reduction of carbon dioxide in the breath might indicate an imminent failure of respiration. Similarly a sharp increase in the level of carbon dioxide might be an indication of other conditions requiring attention.
  • Respiration monitoring of patients is now available utilizing many types of commercially available gas analyzers including infrared (IR) , polaragraph, mass spectrometer (MS) , Raman spectrometer, etc. Due to the high cost of some of the monitoring equipment, a single monitor may be connected to several patients simultaneously. In many of these situations, the gas analyzer is placed in a remote location and lengthy capillary tubes are used to connect the patients to the analyzer unit. Since it is common practice to humidify inspired gas, and since the expired gas from the patient is often at nearly 100% relative humidity and 37 degrees centigrade, water can easily condense at room temperature in the tubing interfacing the patient with the analyzer.
  • IR infrared
  • MS mass spectrometer
  • Raman spectrometer Raman spectrometer
  • One prior method for removing water vapor from expired gases prior to analysis physically drys the expired gas, for example, by introducing the expired gas into a desiccator.
  • One such system has been developed using a desiccator filled with calcium sulfate (C S ⁇ 4) as the drying agent.
  • C S ⁇ 4 calcium sulfate
  • Such desiccator systems experience at least two significant problems. First, the drying agent must be carefully monitored and replaced on a regular basis when it is depleted. Second, the large desiccator volume required to perform the drying of the gas makes for increased dead space within the system and thus results in longer "washout times" for measuring changes in gaseous composition.
  • the term dead space refers to any space in the system between the point where the sample is tapped from the patient and the point at which the sample enters the gas analyzer. This would include the space within the connecting tubes, filters, desiccants, valves, traps etc.
  • the term "washout time” refers to the amount of time which is needed for a unit of
  • Washout time is an important factor in monitoring changes in the concentrations of oxygen, carbon dioxide, anesthetic agents and other constituents of the patient's inspired and expired gases. Where large total volumes or dead volumes are present within a metabolic gas monitoring system, corresponding large washout times are created, resulting in decreased ability to quickly and accurately measure time dependent changes in the composition of the inspired and expired gases.
  • the long washout times associated with desiccator systems do not allow for the dynamic response necessary to measure time dependent changes in the oxygen and carbon dioxide concentrations in breath-by-breath analysis of expired gas.
  • the large total volumes and dead volumes of desiccator systems have resulted in less sensitivity to changes in the composition of the gases analyzed and less accurate measurements of the oxygen, carbon dioxide and anesthetic agent components of the gases.
  • drying agents to remove the water vapor often require frequent replacement of the drying agent and often introduce long delay times in the sampling line precluding the acquisition of breath-by- breath data. Additionally, in some applications, the drying agent may absorb the gas being monitored and lead to inaccurate measurements.
  • U.S. Patent No. 4,090,513 entitled "HEAT AND MOISTURE EXCHANGING DEVICE FOR RESPIRATION” discloses a device for removing moisture from a tube carrying respiratory air. The moisture accumulates on an exchange layer and flows out of the device through a drainage tube. As with other condensation moisture removal systems, decreased response time and water removal considerations limit the applications for which this system is suitable.
  • U. S. Patent No. 4,549,553 entitled "APPARATUS AND METHOD FOR USE IN A MEDICAL GAS SAMPLING SYSTEM”, discloses an approach for providing a sample gas flow from an air tube to a patient undergoing automatic ventilation.
  • the air tube includes a gas diffusive membrane disposed in a wall of the air tube.
  • the gas diffusive membrane may be made of water absorbing or water passing materials to eliminate excess water from accumulating and blocking the gas sample flow.
  • a non-wettable gas diffusive membrane is used to prevent or reduce water from entering the sample gas flow; otherwise, water saturates the membrane and water eventually passes through the membrane to enter the gas sample flow.
  • non- wettable it is meant that the membrane resists or cannot be saturated with liquid and its surfaces resist or cannot be covered with liquid.
  • a Teflon ® mesh membrane is a suitable non-wettable membrane for this application. Teflon ® is a registered trademark of E.I. Du Pont de Nemours & Company, Inc in Wilmington, Delaware. This approach, while perhaps reducing the frequency of sample flow blockage, does nothing to remove the moisture from the system and is still susceptible to occlusion in long term usage. Additionally, the embodiment shown in Figure 1A incorporates a large volume funnel 20 which increases the dead space volume in the gas transport system and results in poor response time characteristics.
  • a more recent approach for preventing water from condensing in the gas transport circuitry uses interface tubing comprising a polymer that is highly permeable to water vapor, but simultaneously has a very low permeability for the respiratory and anesthetic gases being analyzed.
  • Nafion ® is a registered trademark of E.I. Du Pont de Nemours S Company,
  • the present invention is a method and apparatus for interfacing a patient with gas analysis equipment that monitors inspired and expired gases of a patient.
  • the invention utilizes a vaporization technique to inhibit or prevent moisture contained in the inspired and expired gases from obstructing the sample line or from reaching the detector portion of the gas analyzer. More specifically, the invention relates to a method and system for interfacing a patient with a gas monitoring apparatus for analysis of a patient's respiratory gases.
  • One embodiment of the invention includes a patient link which receives a sample of exhaled gases from the patient's airway.
  • the patient link comprises a tubing section which is attached to a vaporization section.
  • the vaporization section comprises a coil of tubing formed by wrapping the tubing around a cylindrical spool in a plurality of proximate turns.
  • the vaporization section is encased by a heated element which advantageously facilitates the vaporization of any condensed moisture which is typically contained in the respiratory gases.
  • Attached to the output of the vaporization section is a hydrophobic filter which is permeable to the vaporized moisture but inhibits the passage of particulates and liquids.
  • the gases After passing through the filter, the gases enter a separator section comprising a tubing material that is highly permeable to water vapor but has a very low permeability for respiratory gases, anesthetic agent gases and other gases being analyzed.
  • the vaporized moisture which passes through the filter diffuses out of the system through the separator section of water vapor permeable tubing substantially reducing the amount of moisture which enters the detector portion of the gas analyzer.
  • the invention comprises an apparatus for sampling the respiratory gases of a patient through an airway circuit and delivering the gas sample to a gas analysis cell.
  • a patient link comprising a first length of tubing connects to the airway circuit, receives the sample of respiratory gases and transports the sample toward the gas analysis cell.
  • a vaporization section receives the sample from the patient link and vaporizes moisture contained in the sample.
  • the vaporization section comprises a vaporization coil which comprises a spool having a cylindrical body portion. The body portion has a first end and a second end.
  • a second length of tubing wraps around the body portion to form a coil having a plurality of proximate turns and a coil output.
  • a disc-shaped filter having an input and an output is located at the second end of the cylindrical body wherein the input to the filter connects to the output from the coil.
  • the vaporization section is surrounded by a heating block having a means for heating the block to a predetermined temperature and a chamber within the block for receiving the vaporization coil.
  • a separator section having an input and an output is connected to the output of the disc filter, wherein the separator receives the gas sample from the filter and removes the water vapor portion from said gas sample to form a dried gas sample. The separator section then delivers the dried gas sample to the gas analysis cell.
  • the separator section comprises a water vapor permeable section.
  • the water vapor permeable section may be a section of Nafion ® tubing.
  • Another embodiment of the invention comprises an apparatus for sampling gases in the airway of a patient and delivering the sample to a gas monitor wherein the apparatus comprises: a patient link for obtaining the gas sample from the patient airway and a vaporization section which receives the gas sample from the patient link and vaporizes condensed moisture contained in the sample before delivering the sample to the gas monitor.
  • the invention further comprises a method of monitoring patient gases comprising the steps of: 1) extracting a sample portion of the gases from the patient; 2) vaporizing moisture contained in the sample portion; 3) removing the vaporized moisture from the sample; and 4) delivering the sample to a monitoring apparatus.
  • the interfacing system of the present invention has several significant advantages over alternate systems and methods. It reduces filter occlusion as a result of condensed water by utilizing vaporization techniques. It eliminates or reduces the risk of water vapor condensing inside the analyzer and contaminating the gas analysis cell inside the instrument.
  • the present invention overcomes many of the limitations of prior art devices in a device which offers superior performance in a cost effective manner.
  • Figure 1 is a perspective view illustrating a patient interfacing system in accordance with the present invention.
  • Figure 2 is a cross section view illustrating details of the vaporization section of the invention.
  • Figure 3 is a cross section taken along the line 3-3 of Figure 2.
  • Figure 4 is a perspective view illustrating the patient link and vaporization coil of the invention.
  • Figure 5 is a plan view of the patient interfacing system of Figure 1.
  • the interfacing system 10 is a device for connecting a patient via a patient circuit 11 with gas monitoring equipment 12 that samples and monitors inspired and expired gases of the patient.
  • the patient interfacing system 10 may be used with most commercially available gas analyzers including but not limited to infrared (IR) , polaragraph, mass spectrometer (MS) , Raman spectrometer, etc.
  • gas analyzers including but not limited to infrared (IR) , polaragraph, mass spectrometer (MS) , Raman spectrometer, etc.
  • IR infrared
  • MS mass spectrometer
  • Raman spectrometer Raman spectrometer
  • the interface system 10 comprises a patient link 20, a vaporization section 30 and a separator section 40.
  • the patient link 20 comprises a length of flexible tube or hose 42 having an input end 44 and an output end 46.
  • the input end 44 is connected to the patient's airway passage and the output end 46 is connected to an input of the vaporization section 30.
  • An output of the vaporization section 30 is connected to an input of the separator section 40 which has an output 47 connected to a gas input of the gas monitor 12.
  • the patient link 20 taps into the patient's airway passage and receives a sample of the patient's inspired and expired gases.
  • the tubing 42 delivers the sample to the vaporization section 30. since the gas sample may have a high moisture content, it is possible that some of the moisture will condense before it reaches the vaporization section 30.
  • the vaporization section 30 may have a high moisture content, it is possible that some of the moisture will condense before it reaches the vaporization section 30.
  • the vaporization section 30 since the gas sample may have a high moisture content, it is possible that some of the moisture will condense before it reaches the vaporization section 30.
  • the vaporization section 30 may have a high moisture content
  • an air or vacuum pump which is a component of the gas analyzer, pumps or draws air from the patient's airway through the interface system 10 into the gas analyzer.
  • the patient link 20 comprises a connector 48 at the input end 44.
  • the connector 48 has a tube 50 extending therefrom which enters a facial orifice of the patient and terminates within the patient's airway at a point from which the sample of respiratory or anesthetic gases is to be extracted.
  • the connector 48 may be attached to an endotracheal conduit, a nasal cannula, or a facial mask device to facilitate entrance into the patient's airway via a tracheal incision, the nose and/or the mouth, respectively.
  • U.S. Patent 4,485,822 A more detailed description of various means for entering the patient's airway may be found in U.S. Patent 4,485,822.
  • the flexible tube 42 delivers the samples of the inspired and expired gases to the vaporization section 30 of the interface 10.
  • the tubing 42 is preferably a cylindrical shape tubing made from a resilient and flexible material. It is preferable that the tubing have a small diameter to facilitate continuous and rapid transportation of samples of inspired and expired gases to the monitoring instrument. The small diameter reduces the dead space volume of the interface 10, which as explained previously, gives the system a fast response time which is particularly advantageous in breath-by-breath analysis procedures. It is preferable that the inside diameter (ID) of the tubing 42 be selected to be in the range of from approximately 0.020 inches to approximately 0.060 inches and the tubing wall thickness be in the range of from approximately 0.010 inches to approximately 0.040 inches.
  • tubing dimensions will facilitate a gas flow rate in the range of from approximately 30 ml/min to approximately 400 ml/min.
  • ID of tubing section 42 is approximately 0.040 inches and the wall thickness is approximately 0.032 inches.
  • length of the tubing section 42 included between the input end 44 and the output end 46 is approximately ten feet. It will be understood, however, that these dimensions are by way of example only and that other dimensions could be selected for practicing the present invention.
  • the vaporization section 30 comprises a coil of flexible tubing 52 which is positioned within a heating block 54.
  • the coil 52 and tube 42 may comprise a single length of tubing with the coil formed at the distal end of the length of tubing 42.
  • the length of tubing comprising the coil is selected to effectuate the desired degree of vaporization of moisture passing through the coil. Several factors influence the selection of this length including the temperature of the heating block, the distance separating the surface of the coil from the inside walls of the heater, the amount of moisture in the sample, the flow rate of gas through the coil, the wall thickness of the tubing and the total exposed surface area of the coil.
  • the length of tubing comprising the coil segment may vary from 2 inches to 50 inches depending upon the specific application.
  • the length of the tubing section which comprises the coil 52 is approximately two feet.
  • the coil 52 is formed by wrapping the tubing 42 around a spool 56 having a head portion 58.
  • the head 58 has an aperture 60 formed in the center through which the tubing 42 is inserted.
  • the spool 56 comprises two semi-circular wall sections 62,64.
  • the semi-circular wall sections 62,64 of the spool 56 define two slots 66,68 which extend longitudinally along the length of the spool 56.
  • the tubing 42 enters the interior region of the spool 56 through the aperture 60 in the head 58.
  • the tubing 42 then exits the interior of the spool through one of the slots 66,68 and is wrapped around the exterior of the spool to form the coil 52.
  • the end of the tubing then reenters the interior of the spool through one of the slots 66,68 and attaches to an input of a disc filter 70.
  • the disc filter 70 also forms the base of the spool 56 opposite the head portion 58.
  • the diameter of the vaporization coil 52 is approximately 1.15 inches.
  • the heating block 54 shown in Figures 2, 3 and 5, comprises a main portion 72 and an extending portion 74 projecting therefrom.
  • the main portion 72 has an cylindrical opening 76 suitably shaped and sized to accommodate the vaporization coil 52.
  • the extending portion 74 has a channel 78 extending therethrough for receiving a heater 80.
  • the heating block 54 may be fabricated from any suitable thermally conductive material such as aluminum or copper.
  • the cylindrical opening 76 has an interior wall 77 which completely surrounds the vaporization coil 52. This facilitates a uniform transfer of heat from the heating block 54 to the coil 52.
  • the coil 52 is placed in close proximity to the interior wall 77 so as to allow effective heat transfer from the block 54 to the coils 52 so as to heat the gases flowing through the coil and vaporize any moisture contained therein.
  • the outer exposed surface of the coil 52 is positioned such that the distance between the exposed surface of the coil and the wall 77 of the heater is in the range of from approximately 0.010 inches to approximately 0.100 inches.
  • the heater 80 may comprise an electrically resistive heating rod or other device capable of supplying heat to the block 54.
  • the heater 80 raises the temperature of the block 54 to a predetermined temperature sufficient to vaporize moisture travelling through the coil 52.
  • the heater 80 is regulated by a thermostat 82 mounted on the heater block 54 so that it senses the temperature of the block.
  • the thermostat is selected to maintain the temperature of the block 54 at the predetermined temperature.
  • One such thermostat which may be used is a bi- etallic switch which turns the heater on when the temperature of the block falls below a lower limit threshold and turns the heater off when the temperature of the block is above an upper limit threshold.
  • the predetermined temperature of the block 54 is typically within the range of from approximately 37* C to approximately 75* C.
  • the thermostat 82 has a control temperature of approximately 50* C.
  • the cylindrical opening 76 of the heater block 78 terminates in a smaller concentric opening 84 in which is positioned a female portion 85 of a two piece tubing connector.
  • a male portion 86 of the two piece connector forms the output of the filter 70 which is connected to the output of the vaporization coil 52 and also forms the base of the vaporization coil.
  • the filter 70 is disc-shaped and has a diameter in the range of from approximately 4 mm to approximately 50 mm.
  • the filter 70 has a large surface area as compared to its volume and a small pore size.
  • the pore size may range from approximately 0.2 microns to approximately 1.2 microns. This configuration limits penetration of the filter by non-gaseous components present in the sample, such as particulates or liquids. These non-gaseous components are trapped at the surface of the filter.
  • the filter 70 prevents secretions from the patient and other liquids from being delivered to the monitoring apparatus while allowing the gas sample to freely pass to the gas monitor.
  • the filter 70 is beneficial for the filter 70 to be constructed from hydrophobic filter materials, such as PTFE (Gortex) and hydrophobic grade acrylic copolymer membranes (Versapor) .
  • the disc filter 70 has an output which is connected to the input of the separator section 40.
  • the separator section 40 comprises a section of water vapor permeable tubing 88.
  • the tubing 88 has a length in the range of from approximately 6 inches to approximately 48 inches, an inside diameter (ID) in the range of from approximately 0.020 inches to approximately 0.085 inches and a wall thickness in the range of from about 0.004 inches to about 0.008 inches.
  • the tubing 88 comprises a polymer that is highly permeable to water vapor but has a very low permeability for the respiratory and anesthetic gases being analyzed. Thus, water vapor rapidly diffuses out of the gas sample when the sample passes through the separator section 40.
  • Nafion® tubing One commercially available product having these characteristics is a polymer which was developed by Du Pont scientists and is marketed in tubing form as Nafion® tubing.
  • a section of Nafion ® tubing having a length of approximately 24 inches, an ID of approximately 0.040 inches and a wall thickness of approximately 0.006 inches is used.
  • the Nafion ® tubing 88 is attached directly to the outflow side of the disc membrane filter 70, thus allowing a majority of the water vapor contained in the sample and vaporized in the vaporization coil 52 to diffuse out of the gas transport system through the Nafion ® tubing before the sample reaches the gas analysis cell.
  • the output end of the tubing 88 is attached to the connector 47 which connects to the gas analysis cell.
  • the Nafion ® tubing 88 is near the end of the gas transport system and thus can be permanently attached to the gas analyzer at its input. In this position, the Nafion ® tubing 88 does not require cleaning and sterilization after each patient use.

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  • Sampling And Sample Adjustment (AREA)
  • Percussion Or Vibration Massage (AREA)
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Abstract

Système d'interface (10) avec un patient permettant d'échantillonner les gaz inspirés et expirés d'un patient et d'éliminer l'humidité contenue dans l'échantillon. Dans un mode de réalisation de la présente invention, une liaison (20) avec le patient reçoit les gaz provenant du circuit d'air (11) du patient et une section de vaporisation (30) vaporise l'humidité condensée dans l'échantillon. Une section de séparation (40) permet à la composante humidité vaporisée de l'échantillon de sortir du système d'interface (10) avant que l'échantillon de gaz n'atteigne l'instrument de contrôle (12). Un filtre (70) peut également être utilisé pour empêcher l'humidité condensée, des particules et des liquides d'entrer dans l'instrument de contrôle (12). Ainsi, le système d'interface (10) avec un patient, décrit par la présente invention, constitue un moyen fiable économique et efficace pour fournir des échantillons de gaz à un instrument de contrôle (12) qui réduit ou empêche la condensation de l'eau à l'intérieur de la partie d'analyse des gaz de l'instrument de contrôle (12).
PCT/US1989/001974 1988-05-20 1989-05-09 Systeme d'interface avec un patient et procede de prevention de la contamination de l'eau WO1989011245A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
KR1019900700104A KR900701352A (ko) 1988-05-20 1989-05-09 물 오염을 방지하기 위한 환자 인터페이싱 시스템 및 방법

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US19672588A 1988-05-20 1988-05-20
US196,725 1994-02-15

Publications (1)

Publication Number Publication Date
WO1989011245A1 true WO1989011245A1 (fr) 1989-11-30

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PCT/US1989/001974 WO1989011245A1 (fr) 1988-05-20 1989-05-09 Systeme d'interface avec un patient et procede de prevention de la contamination de l'eau

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EP (1) EP0418267A4 (fr)
JP (1) JPH03504206A (fr)
KR (1) KR900701352A (fr)
AU (1) AU3571789A (fr)
CA (1) CA1325115C (fr)
WO (1) WO1989011245A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1992005738A1 (fr) * 1990-10-06 1992-04-16 Lion Laboratories Plc Embouchure
EP0577053A1 (fr) * 1992-06-30 1994-01-05 Hideo Ueda Procédé et tube collecteur destinés à la prise de gaz expirés
WO2015186122A1 (fr) * 2014-06-02 2015-12-10 Oridion Medical 1987 Ltd. Tube d'échantillonnage de gaz respiratoire et dispositif associé
EP3548129B1 (fr) * 2016-12-05 2022-03-23 Servei Central d'Anestesiologia SLP Dispositifs d'échantillonnage de l'air expiré

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080027344A1 (en) * 2006-07-27 2008-01-31 Ric Investments, Llc Modular sidestream gas sampling assembly

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US3507146A (en) * 1968-02-09 1970-04-21 Webb James E Method and system for respiration analysis
US4425804A (en) * 1981-10-29 1984-01-17 The Perkin-Elmer Corp. Ultrasonic air flow transducer for high humidity environments
US4727871A (en) * 1985-10-28 1988-03-01 Infrasonics, Inc. Ventilator exhalation system

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Publication number Priority date Publication date Assignee Title
US3649199A (en) * 1970-03-26 1972-03-14 Varian Associates Method for detecting trace quantities of an organic drug material in a living animal
US4167667A (en) * 1978-06-12 1979-09-11 The Perkin-Elmer Corporation Respiratory gas moisture separator system for mass spectrometer monitoring systems
US4549553A (en) * 1983-11-07 1985-10-29 Spacelabs, Inc. Apparatus and method for use in a medical gas sampling system

Patent Citations (3)

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Publication number Priority date Publication date Assignee Title
US3507146A (en) * 1968-02-09 1970-04-21 Webb James E Method and system for respiration analysis
US4425804A (en) * 1981-10-29 1984-01-17 The Perkin-Elmer Corp. Ultrasonic air flow transducer for high humidity environments
US4727871A (en) * 1985-10-28 1988-03-01 Infrasonics, Inc. Ventilator exhalation system

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP0418267A4 *

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1992005738A1 (fr) * 1990-10-06 1992-04-16 Lion Laboratories Plc Embouchure
EP0577053A1 (fr) * 1992-06-30 1994-01-05 Hideo Ueda Procédé et tube collecteur destinés à la prise de gaz expirés
WO2015186122A1 (fr) * 2014-06-02 2015-12-10 Oridion Medical 1987 Ltd. Tube d'échantillonnage de gaz respiratoire et dispositif associé
EP3548129B1 (fr) * 2016-12-05 2022-03-23 Servei Central d'Anestesiologia SLP Dispositifs d'échantillonnage de l'air expiré

Also Published As

Publication number Publication date
CA1325115C (fr) 1993-12-14
EP0418267A1 (fr) 1991-03-27
JPH03504206A (ja) 1991-09-19
AU3571789A (en) 1989-12-12
KR900701352A (ko) 1990-12-01
EP0418267A4 (en) 1991-08-07

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