EP0148320B1 - Kreislaufatemschutzgerät für Überdruckbetrieb - Google Patents

Kreislaufatemschutzgerät für Überdruckbetrieb Download PDF

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Publication number
EP0148320B1
EP0148320B1 EP84109870A EP84109870A EP0148320B1 EP 0148320 B1 EP0148320 B1 EP 0148320B1 EP 84109870 A EP84109870 A EP 84109870A EP 84109870 A EP84109870 A EP 84109870A EP 0148320 B1 EP0148320 B1 EP 0148320B1
Authority
EP
European Patent Office
Prior art keywords
respiratory
pressure
closed circuit
breathing
pressure gas
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
Application number
EP84109870A
Other languages
German (de)
English (en)
French (fr)
Other versions
EP0148320A1 (de
Inventor
Pasternack Dr. Adalbert
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.)
Draegerwerk AG and Co KGaA
Original Assignee
Draegerwerk AG and Co KGaA
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 Draegerwerk AG and Co KGaA filed Critical Draegerwerk AG and Co KGaA
Publication of EP0148320A1 publication Critical patent/EP0148320A1/de
Application granted granted Critical
Publication of EP0148320B1 publication Critical patent/EP0148320B1/de
Expired legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A62—LIFE-SAVING; FIRE-FIGHTING
    • A62B—DEVICES, APPARATUS OR METHODS FOR LIFE-SAVING
    • A62B9/00—Component parts for respiratory or breathing apparatus
    • A—HUMAN NECESSITIES
    • A62—LIFE-SAVING; FIRE-FIGHTING
    • A62B—DEVICES, APPARATUS OR METHODS FOR LIFE-SAVING
    • A62B7/00—Respiratory apparatus
    • A62B7/10—Respiratory apparatus with filter elements

Definitions

  • the invention relates to a circuit breathing apparatus for overpressure operation with a compressed gas source which, in addition to the breathing circuit, feeds an auxiliary device via a compressed gas line, which brings about a pressure increase in the breathing circuit by moving the breathing bag in the inhalation phase.
  • Such a circuit breathing apparatus is known from DE-A-31 05 637.
  • the exhalation line is connected to the inhalation line via a CO 2 absorber and a gas compensation container.
  • a pressurized gas bottle containing predominantly oxygen is connected to the inhalation line.
  • a bellows with rigid end walls is best suited as a gas expansion tank. The bellows is under the constant force of a cylinder-piston unit acting in the sense of its volume reduction, the piston of which is connected to its end wall and pressurized gas from the pressurized gas bottle is acted upon, relaxed to a medium pressure. The movement of the piston creates a sustained pressure increase in the bellows, which is sufficient for the desired overpressure in the entire breathing circuit.
  • the force acting on the bellows can be changed continuously or stepwise by means of measures that are not shown in more detail, as a result of which the excess pressure prevailing in the circuit can be adapted to the prevailing working conditions and the respiratory protection device can optionally be set to negative and positive pressure operation.
  • FR-A-2 323 403 describes a closed-circuit breathing apparatus in which a pressure sensor is connected to the mask and breathing gas source, which releases or blocks the fresh gas flow in accordance with the pressure prevailing in the mask near the mouthpiece.
  • This known auxiliary device is installed in the main breathing circuit and controls the supply of the fresh gas itself, depending on the determined breathing phase based on the pressure in the mask. However, it is not suitable for relieving an excess pressure once built up in the main breathing circuit when changing to the exhalation phase.
  • the object of the present invention is seen in improving a circuit breathing apparatus of the type mentioned above in such a way that an overpressure in the breathing circuit is generated only during the inhalation phase, but not during the exhalation phase.
  • This object is achieved in that a sensor connected to a measuring circuit is provided for determining the breathing phases, and in that the measuring circuit controls the auxiliary device in the exhalation phase for reducing the additional pressure exerted on the breathing bag.
  • the arrangement of the circulatory breathing apparatus according to the invention enables the pressure conditions in the breathing circuit to be controlled as a function of the breathing phases.
  • a sensor provided for determining the breathing phases can be arranged at any point in the breathing circuit if it is only able to determine the change between the inhalation and exhalation phases.
  • Such a sensor is preferably attached to the breathing bag.
  • the compressed gas line is connected to the auxiliary device by a changeover valve only during the inhalation phase, but is shut off during the exhalation phase.
  • the auxiliary device and the breathing bag are connected to one another via a connecting line, so that pressure fluctuations due to the lifting movement of the breathing bag in the feed line to the auxiliary device can be compensated for. It is possible to connect the supply line to the auxiliary device with the compressed gas line shut off via the changeover valve with the free ambient atmosphere. This could blow off the gas from the supply line when pressure fluctuations occur in the exhalation phase. However, this would have the undesirable disadvantage that each time unnecessarily pressurized gas, for. B. oxygen is lost.
  • the sensor for determining the breathing phase can advantageously be designed as an electrical resistance section which is arranged on a guide element connected to the piston end wall. As a result, the determination of the breathing phases can be traced back to a measurement of the direction of movement of the rigid, movable wall part of the breathing bag.
  • the measurement signal to be evaluated by the measurement circuit is supplied by the voltage drop along the measurement section, as received by a measurement sensor.
  • the voltage difference which can be tapped changes in an advantageous manner as a result of the movement of the guide element, namely by a difference ⁇ V f in the inhalation phase and by a difference AV A in the exhalation phase. Both difference amounts decrease to zero at the end of a breath.
  • a change between the inhalation phase and the exhalation phase also means a change between increasing and decreasing the detectable voltage difference ⁇ V ⁇ .
  • the circuit breathing apparatus with positive pressure operation contains the components, which are shown in a functional arrangement and form the breathing circuit, on a carrying frame in an outer protective cover. These are a breathing connection 1, an exhalation line 3, a regeneration cartridge 4 which binds the carbon dioxide present in the exhaled air, a breathing bag 5 and an inhalation line 2.
  • the oxygen consumed during breathing is fed to the breathing circuit from an oxygen cylinder 6, a cylinder valve 7, a pressure reducer 8 via a regulator 9 and via a pipeline 10 with a constant dosage 11 behind the breathing bag 5.
  • a pressure relief valve 12 behind the regeneration cartridge 4 prevents excessive pressure in the breathing circuit.
  • the breathing bag 5 consists of a bellows 13, which is closed by a movable rigid end wall 14.
  • a cylinder-piston unit 15 with a piston 16 in a cylinder 17 forms a pressure chamber 18 above the piston 16, which is connected to the pipeline 10 via a pressure line 19.
  • the pressure line 19 contains a solenoid valve 20, with which the pressure line 19 is closed and a line part 21 is separated in front of the pressure chamber 18 and this can then be connected to the breathing bag 5 via the line part 21 and a connecting line 22.
  • the piston 16 with its lower piston end face 23 opposite the pressure chamber 18, protrudes from the cylinder 17, which is open here and is connected to the end wall 14 of the breathing bag 5 via a movable connection 24.
  • a sensor 26 is axially attached to a guide element 31.
  • the sensor 26 is designed as an electrical resistance path, which is connected on the input side to the amplifier 28.
  • a current impressed by the amplifier produces a voltage drop along the resistance path, which is picked up by a standing sliding contact 27.
  • the voltage differences AV e , AV A and AV o determined in the amplifier 28 with a transmitter 29 result in the switching values for the solenoid valve 20.
  • the breathing phases that is, the inhalation and the subsequent exhalation, each result in repetitive functions and pressure conditions in the breathing circuit.
  • the solenoid valve 20 connects the pressure chamber 18 to the pipeline 10.
  • the excess pressure given in this by the pressure reducer 8 continues into the pressure chamber 18, presses on the piston 16 and moves it and thus its end wall 25 downward.
  • the pressure forms the excess pressure in the breathing circuit.
  • the overpressure exists throughout inhalation phase and prevents the penetration of possibly non-breathable ambient atmosphere into the breathing circuit. Concomitant with the piston 16 movement of the feeler 26 with the thereby changing the length of the resistance path for the sliding contact 27 leads to a decreasing order AV E voltage difference AV e.
  • the breathing circuit becomes severely defective, the overpressure in it completely drops.
  • the oxygen pressure still present in the pressure line 19 with the open solenoid valve 20 presses the breathing bag together widely.
  • the breathing bag 5 remains in the smallest position because it has no inherent elasticity, the solenoid valve 20 remains permanently closed with respect to the pressure line 19, and an alarm device 30 simultaneously occurs Activity.
  • the wearer can now use the breathing apparatus with normal pressure. Its oxygen supply takes place normally via the pipeline 10. When the defect is closed, the breathing circuit automatically switches back to overpressure mode when the breathing bag 5 is refilled.

Landscapes

  • Health & Medical Sciences (AREA)
  • Pulmonology (AREA)
  • General Health & Medical Sciences (AREA)
  • Business, Economics & Management (AREA)
  • Emergency Management (AREA)
  • Respiratory Apparatuses And Protective Means (AREA)
EP84109870A 1983-12-09 1984-08-18 Kreislaufatemschutzgerät für Überdruckbetrieb Expired EP0148320B1 (de)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
DE3344567 1983-12-09
DE3344567 1983-12-09
DE19843429345 DE3429345A1 (de) 1983-12-09 1984-08-09 Kreislaufatemschutzgeraet fuer ueberdruckbetrieb
DE3429345 1984-08-09

Publications (2)

Publication Number Publication Date
EP0148320A1 EP0148320A1 (de) 1985-07-17
EP0148320B1 true EP0148320B1 (de) 1987-09-30

Family

ID=25816309

Family Applications (1)

Application Number Title Priority Date Filing Date
EP84109870A Expired EP0148320B1 (de) 1983-12-09 1984-08-18 Kreislaufatemschutzgerät für Überdruckbetrieb

Country Status (3)

Country Link
US (1) US4667669A (enrdf_load_stackoverflow)
EP (1) EP0148320B1 (enrdf_load_stackoverflow)
DE (2) DE3429345A1 (enrdf_load_stackoverflow)

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US5199424A (en) 1987-06-26 1993-04-06 Sullivan Colin E Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled
US5522382A (en) 1987-06-26 1996-06-04 Rescare Limited Device and method for treating obstructed breathing having a delay/ramp feature
DE3823381A1 (de) * 1987-11-03 1989-05-24 Draegerwerk Ag Kreislaufatemschutzgeraet
DE3823383A1 (de) * 1988-07-09 1990-01-18 Draegerwerk Ag Kreislauf-atemschutzgeraet fuer ueberdruckbetrieb mit einer sperre im geraeteanschlussstueck
DE3823382C1 (enrdf_load_stackoverflow) * 1988-07-09 1990-01-11 Draegerwerk Ag, 2400 Luebeck, De
DE3900276A1 (de) * 1989-01-07 1990-07-12 Draegerwerk Ag Beatmungsgeraet mit atemkreislauf und gesteuerter frischgaszufuhr
ATE283085T1 (de) * 1989-05-19 2004-12-15 Puritan Bennett Corp Drucksystem für atmungswege
US5134995A (en) * 1989-05-19 1992-08-04 Puritan-Bennett Corporation Inspiratory airway pressure system with admittance determining apparatus and method
DE3930362A1 (de) * 1989-09-12 1991-03-21 Draegerwerk Ag Kreislaufatemschutzgeraet
US5148802B1 (en) * 1989-09-22 1997-08-12 Respironics Inc Method and apparatus for maintaining airway patency to treat sleep apnea and other disorders
US5239995A (en) * 1989-09-22 1993-08-31 Respironics, Inc. Sleep apnea treatment apparatus
US5632269A (en) * 1989-09-22 1997-05-27 Respironics Inc. Breathing gas delivery method and apparatus
US5537995A (en) * 1990-04-03 1996-07-23 Den Norske Stats Oljeselskap A.S. Breathing system having breathing bag and supplemental gas dosing controls
US5057822A (en) * 1990-09-07 1991-10-15 Puritan-Bennett Corporation Medical gas alarm system
US6629527B1 (en) 1991-10-17 2003-10-07 Respironics, Inc. Sleep apnea treatment apparatus
US7013892B2 (en) 1991-11-01 2006-03-21 Ric Investments, Llc Sleep apnea treatment apparatus
US5520192A (en) * 1991-12-23 1996-05-28 Imperial College Of Science, Technology And Medicine Apparatus for the monitoring and control of respiration
US6675797B1 (en) 1993-11-05 2004-01-13 Resmed Limited Determination of patency of the airway
DE4342310C2 (de) * 1993-12-11 1998-11-05 Draegerwerk Ag Atemsystem mit gesteuertem Atemgasfluß
WO1997010868A1 (en) 1995-09-18 1997-03-27 Resmed Limited Pressure control in cpap treatment or assisted respiration
AUPN616795A0 (en) * 1995-10-23 1995-11-16 Rescare Limited Ipap duration in bilevel cpap or assisted respiration treatment
AUPO247496A0 (en) 1996-09-23 1996-10-17 Resmed Limited Assisted ventilation to match patient respiratory need
AUPO511397A0 (en) * 1997-02-14 1997-04-11 Resmed Limited An apparatus for varying the flow area of a conduit
DE19725632C1 (de) 1997-06-17 1998-10-01 Weinmann G Geraete Med Sauerstoffkonzentrator
ATE339233T1 (de) * 2001-04-12 2006-10-15 Lifevent Ltd Kontinuierliches positiv-atemwegsdruckgerät
US20060290525A1 (en) * 2002-09-12 2006-12-28 Andersen Donald P Gas alert for medical gas system
NO20044074D0 (no) * 2004-09-27 2004-09-27 Ottestad Breathing Syst As Funksjonsmate for et baerbart, halvlukket pustesystem som far pusteluften resirkulert via en pustebelg og en CO2 absorbator
RU2297257C2 (ru) * 2005-06-28 2007-04-20 Открытое акционерное общество "Корпорация "Росхимзащита" (ОАО "Корпорация "Росхимзащита") Изолирующий дыхательный аппарат
US9107606B2 (en) 2010-01-08 2015-08-18 Pulmonx Corporation Measuring lung function and lung disease progression at a lobar/segmental level
US20110284002A1 (en) * 2010-05-18 2011-11-24 Mindray Medical Sweden Ab Pneumatic transient handler and method
CN102309802B (zh) * 2011-01-26 2014-08-06 德州学院 一种呼吸器
US8770194B2 (en) * 2011-01-28 2014-07-08 Dive Cobalt Blue, Llc Gas assisted re-breathing device
DE102014017634B4 (de) * 2014-11-27 2018-02-08 Dräger Safety AG & Co. KGaA Kreislaufatemgerät mit einer Messeinrichtung zur Bestimmung von Gasmengen in dem Kreislaufatemgerät
CN107875488A (zh) * 2017-12-06 2018-04-06 樊树荣 一种呼吸内科用氧气袋辅助箱
DE102023101813A1 (de) 2023-01-25 2024-07-25 Dräger Safety AG & Co. KGaA Kreislaufatemgerät und Verfahren zu einer Überprüfung der Funktionsbereitschaft eines Kreislaufatemgerätes
CN118807065A (zh) * 2024-08-16 2024-10-22 益生瑞(上海)生物科技有限公司 家用氢氧治疗机

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Also Published As

Publication number Publication date
EP0148320A1 (de) 1985-07-17
DE3429345C2 (enrdf_load_stackoverflow) 1989-06-01
DE3429345A1 (de) 1985-06-13
DE3466479D1 (en) 1987-11-05
US4667669A (en) 1987-05-26

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