EP0773814B1 - Beatmungsgerät - Google Patents

Beatmungsgerät Download PDF

Info

Publication number
EP0773814B1
EP0773814B1 EP95926793A EP95926793A EP0773814B1 EP 0773814 B1 EP0773814 B1 EP 0773814B1 EP 95926793 A EP95926793 A EP 95926793A EP 95926793 A EP95926793 A EP 95926793A EP 0773814 B1 EP0773814 B1 EP 0773814B1
Authority
EP
European Patent Office
Prior art keywords
air
valve
pump unit
pressure
mask
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
EP95926793A
Other languages
English (en)
French (fr)
Other versions
EP0773814A4 (de
EP0773814A1 (de
Inventor
Martinus Oliver Klockseth
Bengt Yngve Roland Jervmo
Goran Bertil Claes Berndtsson
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.)
Safety Equipment Sweden AB
Original Assignee
Safety Equipment Sweden AB
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
Priority claimed from AUPM7190A external-priority patent/AUPM719094A0/en
Priority claimed from AUPN1909A external-priority patent/AUPN190995A0/en
Priority claimed from AUPN1911A external-priority patent/AUPN191195A0/en
Priority claimed from AUPN3106A external-priority patent/AUPN310695A0/en
Application filed by Safety Equipment Sweden AB filed Critical Safety Equipment Sweden AB
Publication of EP0773814A1 publication Critical patent/EP0773814A1/de
Publication of EP0773814A4 publication Critical patent/EP0773814A4/de
Application granted granted Critical
Publication of EP0773814B1 publication Critical patent/EP0773814B1/de
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A62—LIFE-SAVING; FIRE-FIGHTING
    • A62B—DEVICES, APPARATUS OR METHODS FOR LIFE-SAVING
    • A62B18/00—Breathing masks or helmets, e.g. affording protection against chemical agents or for use at high altitudes or incorporating a pump or compressor for reducing the inhalation effort
    • A62B18/006—Breathing masks or helmets, e.g. affording protection against chemical agents or for use at high altitudes or incorporating a pump or compressor for reducing the inhalation effort with pumps for forced ventilation

Definitions

  • the present invention relates to a fan forced positive pressure breathing apparatus of the kind in which filtered air is pumped to a face piece or mask covering at least the nose or mouth of the wearer, the air being pumped by means of a fan driven by an electric motor which is usually battery powered.
  • Breathing apparatus of the kind of which the present invention is concerned is well known and a variety of different constructions have been proposed and the advantages and disadvantages of such apparatus is discussed in many patent specifications.
  • a satisfactory apparatus supplies adequate quantities of air when the user takes a deep breath which, testing shows, necessitates the supply of a substantially higher flow rate than normally anticipated. It is desirable to minimise power consumption by the motor driving the fan consistent with the requirements set out above to increase battery life.
  • DE 4,205,412 describes a gas mask and breathing equipment arrangement with a storage tank for liquefied respiration gas and an air circulation duct intended for transmitting heat of evaporation from the ambient air to the liquefied respiration gas. According to the disclosure of DE 4,205,412, a sufficient flow rate of ambient air will be achieved under all conditions of use by providing a fan for delivering ambient air through the air circulation duct.
  • the present invention consists in a forced air breathing apparatus comprising a face piece or mask covering at least the nose or mouth of a wearer, a pump unit arranged to supply air to a space within the face piece or mask, an electric motor within the pump unit arranged to drive a fan forming part of the pump unit, a filter to filter air entering the face piece or mask and a valve means controlling the flow of air from the pump unit to the face piece or mask during inhalation and from the face piece or mask during exhalation, the valve means including an air inlet valve and an air outlet valve, the air outlet valve being maintained in a closed position during inhalation through the air inlet valve by air pressure from the pump unit and being opened by exhaled air which also acts on the inlet valve to prevent the entry of exhaled air to the pump unit; wherein the apparatus further includes means for maintaining and controlling the speed of the motor so that the fan rotates at a substantially constant speed irrespective of whether air is being inhaled or exhaled by the user.
  • face piece or mask is taken to include any device covering the nose or mouth of a wearer and adapted to engage with the wearer's body or clothing around its edges. It may cover only the mouth or the nose or both of them. If desired, it may comprise a helmet covering the whole of the wearer's head.
  • the term filter is taken to include any device for the removal of particulate and/or gaseous contaminants from the inhaled air.
  • the particulates may be solid, as in smoke, or liquid as in insecticide sprays.
  • the filter may be adapted to remove gaseous contaminants, in which case the filter may be in the form of activated carbon or another gaseous absorbent.
  • the apparatus may include, downstream of the filter, a device for measuring the oxygen content of the inhaled air.
  • This device will preferably provide a warning to a wearer when the oxygen content of the filtered inhaled air falls below a predetermined level.
  • the apparatus includes a source of compressed oxygen or other breathable gas that can be released into the inhaled air at a rate sufficient to maintain the oxygen content of the inhaled air above that predetermined level.
  • a positive air pressure respirator apparatus may comprise a face piece or mask covering at least the mouth or nose of a wearer, a pump unit arranged to supply air to the space within the face piece or mask, an electric motor within the pump unit arranged to drive a fan, wherein the apparatus is provided with actuable control means adapted to cause the apparatus to undergo a calibration phase such that the speed of rotation of the fan is set at a predetermined optimum base value relative to the operating conditions then prevailing in the apparatus.
  • the base value is preferably maintained substantially constant during any one period of operation of the apparatus or until the apparatus is recalibrated.
  • the apparatus includes an electronic data processing means which monitors and controls the speed of the motor so as to ensure adequate air flow at the mask of the apparatus.
  • the actuable control means takes account of the filter type and/or flow resistance within the apparatus to set the optimum value of speed of rotation of the fan.
  • the actuable control means would be manually operated by a user of the apparatus.
  • the actuable control means would include the electronic data processing means with the user entering parameters relevant to the filter type and/or the flow resistance so as to set the optimum speed of the fan prior to use.
  • the actuable control means would automatically set the apparatus to undergo a calibration phase.
  • One means of automatic operation would involve the parameters of the filter type being coded onto the filter such that the details are detected by the electronic data processing means which automatically adjust the flow of air through the apparatus.
  • the transmission of the coded information to the electronic data processing means could be by optical, electrical or magnetic transfer.
  • a second and more desirable means of automatic operation would involve use of a pressure sensor and/or flow measurement apparatus, each under the control of the electronic data processing means.
  • the pressure sensor and/or flow meter would preferably be located proximate, and downstream of, the filter of the apparatus such that flow and pressure drop are automatically measured with detected values of air flow and pressure being fed to the electronic data processing unit.
  • the electronic data processing unit would then automatically calculate the appropriate speed of rotation of the fan given the measured parameters.
  • the pressure sensor comprises a silicone pressure transducer.
  • the pressure sensor comprises a flexible membrane arranged to flex with changes in pressure, an ultrasound transmitter arranged to direct ultrasound at the membrane, an ultrasound receiver arranged to detect ultrasound reflected from the membrane, and an analysing means, the analysing means being capable of determining a parameter based on the transit time of the ultrasound between the transmitter, membrane and receiver and calibrated so as to provide an indication of air pressure to the electronic data processing means.
  • a temperature probe in communication with the analysing means, the analysing means applying a compensation algorithm to the transit time in accordance with the measured temperature.
  • the flow measurement apparatus comprises an air flow restrictor such as an orifice plate or mesh and a pressure sensor adapted to measure the change in pressure across the restrictor.
  • the flow measurement apparatus comprises a pressure sensor adapted to measure the change in pressure between the pump unit and the face piece or mask resulting from one or more air flow restrictors between the pump unit and mask.
  • the air flow restrictor preferably comprises an air transfer hose which allows flow of air between the pump unit and face piece or mask.
  • the flow measurement apparatus comprises an ultrasound transmitter and an ultrasound receiver adapted to respectively transmit and detect ultrasound travelling along a portion of the air transfer hose.
  • the flow rate is directly proportional to the time shift of the ultrasound travelling down the hose.
  • the flow measurement apparatus comprises a thermistor placed in the air flow and heated to a temperature greater than ambient temperature, the flow rate being proportional to the cooling effect of the air flow on the heated thermistor.
  • the mask is preferably washed after each use. For these reasons it is not desirable to have electrical systems, or other apparatus vulnerable to breakage, in the mask.
  • the forced air breathing apparatus preferably operates at a low pressure but at a relatively high flow rate.
  • the apparatus is capable of delivering at least 150 litres of air per minute, preferably 300 litres of air per minute, and more preferably at least 500 litres of air per minute, to a wearer.
  • the supply pressure of air to the air inlet valve admitting air to the face piece or mask is between zero and 10mBar, more preferably no more than 6mBar, above ambient reference pressure-. It is also preferred that the fan in the pump unit produces a pressure in this range. It is possible, however, to provide a regulator between a pump unit producing air at a higher pressure and the value means associated with the face piece or mask.
  • the pump unit will supply air at a pressure of less than 1Bar, preferably less than 100mBar, and more preferably less than 20mBar.
  • hose diameters must be so chosen as to avoid undue How-restrictions that would cause large pressure drops in the system.
  • the apparatus shown in Figures 1 and 2 consists of a pump unit 10 enclosing an air space and an electric motor 11 driving a centrifugal fan 12.
  • a source of power for the motor usually a rechargeable battery, and in addition a motor speed control unit of conventional construction.
  • This unit monitors the speed of rotation of the fan 12 and controls the speed of the motor to cause it to operate at a substantially constant speed irrespective of whether air is being inhaled or exhaled by the user.
  • Air is drawn into the pump unit 10 through a conventional filter 13.
  • the entry of air from the filter is controlled by the valve member 14 associated with the bellows 15 which closes the valve during exhalation of air as shown in Figure 2 and which is lightly biased to the open position by means of the spring 20 as shown in Fig. 1.
  • the valve 14 is displaced by the spring 15 and the depression within the pump unit to allow air to enter the pump unit.
  • Means may be provided for adjusting the pressure at which the valve 14 closes. It is desirable to keep this as low as possible and for the valve to be arranged to open only for a time sufficient to allow the required amount of air to enter after which the valve closes.
  • the system is balanced with the valve acting as a pressure regulator to minimise pressure fluctuations in the pump unit as much as possible to ensure a more or less instantaneous supply of air from the fan to the user as soon as inhalation commences.
  • the pump unit is connected by means of the duct 16 to an exhaust valve shown at 17.
  • the duct 16 splits into two parts, a duct 18 which leads via a valve member 19 to the face piece or mask (20a) and also to an exhaust outlet 21 which during inhalation is closed by the valve member 22 which is lightly biased to the closed position by the spring 23 as shown in Figure 1.
  • the valve 22 could be replaced by a simple spring loaded exhalation valve.
  • the second branch 24 of the duct 16 leads to the rear of the valve member 22 which tends to maintain the valve in a pressure balanced condition.
  • Air is drawn in through the open valve 14 to the fan 12 which generates a pressure to produce an air flow through the ducts 16 and 18 to the face piece or mask worn by the user. It will be seen that the valve 19 is maintained open by the air pressure on it and air flows freely to the user. The pressure of air in the duct 24 acts on the back of valve 22 to reinforce the action of the spring 23 and keep the valve closed.
  • Figures 3 and 4 show in a more realistic manner one form of exhaust valve construction corresponding in function to the exhaust valve 17 shown in Figures 1 and 2.
  • the duct 25 corresponds to the duct 16 in Figures 1 and 2
  • a pair of one way valves 26 correspond to the valve member 19 of Figures 1 and 2
  • a pair of outlet apertures 27 correspond to the duct 18 of Figures 1 and 2 providing a connection to the face piece or mask.
  • air from the pump unit enters the duct 25, passes through the valve 26 and is supplied to the face piece or mask through the outlet 27.
  • a diaphragm valve 28 lightly loaded by a spring 29 onto a seating 31.
  • This valve has a central hollow stem 32 movable with the diaphragm. This has air inlet apertures 33 at its lower end and an air outlet 34 at its upper end.
  • the diaphragm valve 28 corresponds to the valve 22 of Figures 1 and 2.
  • the exhaust valve shown in Figures 3 and 4 has features not shown in Figures 1 and 2 in that when the hollow stem 32 is in the position shown in Figure 3, air under pressure from the pump unit can enter the apertures 33 and exert pressure on the upper surface of the diaphragm valve 28 reinforcing the action of the spring 29 and the situation is similar to that shown in Figures 1 and 2.
  • the diaphragm 28 moves upwardly it carries the member 32 with it. This has the effect of shutting off the air inlets 33 and opening the air outlet 34 thus releasing any air pressure above the diaphragm 28 through the one way valves 35.
  • the valve 40 includes an air inlet duct 41 connected to a source of positive air pressure (not shown), a first valve 42, a face mask 43 covering the mouth and nose of a wearer (as is shown in Fig. 5(a)), a second valve 44, and a discharge aperture 45 for the discharge of exhaled air to atmosphere.
  • the first valve 42 serves to admit air from the inlet duct 41 into the face mask 43 when the system pressure in the inlet duct 41 exceeds the pressure in the face mask 43. When the pressures are equal the valve 42 closes.
  • the second valve 44 serves to permit the passage of exhaled air from the face mask 43 through the discharge aperture 45 to atmosphere.
  • the valve 44 comprises a diaphragm which is exposed on a first face 46 to the inlet duct 41 and the air pressure therein.
  • a second face 47 of the diaphragm of valve 44 is arranged to bear against a valve seat 48 for the second valve 44.
  • the area of the second face 47 of the diaphragm within the area defined by value seat 48 is exposed, when the valve is closed, to the pressure within the face mask 43.
  • the remainder of the second face 47 of the diaphragm will be exposed to atmospheric pressure through discharge aperture 45 when the valve 44 is closed.
  • air will flow from inlet duct 41 through valve 42 into the face mask 43 is equal to that in the inlet duct 41.
  • the valve 42 will then close. If the wearer now exhales the pressure in the face mask 43 will rise. Once the rise is sufficient to overcome the force holding valve 44 in a closed position that valve will open and air will discharge from the face mask 43 through valve 44 and discharge aperture 45 to atmosphere.
  • the force holding the valve 44 in a closed position is the difference between the pressure on the first face 46 and the second face 47.
  • the force holding the valve 44 closed is the difference between atmospheric pressure on that part of the second face that lies outside the valve seat 48 and the inlet duct pressure over a similar area.
  • this area is small relative to the area of the diaphragm which lies within the area defined by valve seat 48 even a small rise in pressure within the face mask is sufficient to open the outlet valve 44.
  • the area is small even a substantial increase in system pressure within the inlet duct will not raise greatly the exhalation pressure required to open the second valve 44.
  • Figs. 6(a) to 6(c) The arrangement shown in Figs. 6(a) to 6(c) is essentially similar to that described with reference to Figs. 5(a) to 5(c) and similar parts are given the same numeric designation.
  • the first valve 42 is disposed within the membrane of the second valve 44. The valve works in the manner described with reference to Figs. 5(a) to 5(c).
  • Figs. 7(a) and 7(b) The arrangement shown in Figs. 7(a) and 7(b) is similar to the arrangement described with reference to Figs. 1 and 2 with two major exceptions.
  • the first exception that the valve 40 of Figs. 6(a) to 6(c) has been substituted for valve 17 of Figs. 1 and 2.
  • the second exception is that the filter 13 is moved from in front of the fan 12 to behind the fan 12.
  • the pressure controlling the valve 14 is drawn from a duct 60 linking the filter 13 with the valve 40. In this way the opening and closing of the valve 14 more closely reflects the changes in pressure due to the breathing by a wearer due to inclusion of the pressure drop over the filter in the regulation.
  • FIGs 8(a) and 8(b) show fan forced positive air pressure breathing apparatus according to this invention.
  • the arrangement is similar to the arrangement described with reference to Figures 7(a) and 7(b) and similar parts are given the same numeric designation.
  • the fan operates at a high pressure and feeds high pressure air to a regulator 51. Air from the regulator 51 flows through hose 53 to valve 40.
  • a positive air pressure respirator is generally shown as 110 in Fig. 9.
  • the apparatus includes a pump unit in which is situated an electric motor 111 driving a centrifugal fan 112.
  • a source of power for the motor 111 usually a rechargeable battery (not depicted), and a motor speed control unit under microprocessor control 115.
  • Air is drawn into the respirator 110 through a filter 113, passes through the fan 112 and exits the apparatus 110 via the mask 114.
  • the mask 114 is adapted to completely cover the mouth and nose of a wearer and is adjustable so as to fit snugly to the contours of the face of the wearer.
  • the microprocessor control 115 in the embodiment depicted monitors input from a pressure transducer 116 and a flow meter 117 and is thereby able to ascertain the flow resistance of the filter 113 being employed. In those cases where flow resistance is high, the microprocessor control 115 will note this and set the speed of rotation of the fan 112 at-a higher level to compensate thereby ensuring that adequate flow of air is available at the mask 114 on inhalation by the wearer.
  • the microprocessor control 115 will automatically undertake a measure of flow resistance and automatically adjust the speed of the fan 112 to the necessary level.
  • a positive air Purifying respirator is generally shown as 210 in Fig. 10.
  • the apparatus includes a pump unit in which is situated an electric motor driving a centrifugal fan, a power source, usually a rechargeable battery, and a motor speed control unit under microprocessor control (all not depicted). Air is drawn into the respirator 210 through a filter, passes through the fan and exits the apparatus 210 through an air hose 211 and mask 212.
  • the mask 212 is adapted to completely cover the mouth and nose of a wearer and is adjustable so as to fit snugly to the contours of the face of the wearer.
  • Performance of the apparatus 210 is monitored by a performance monitor located within the pump unit.
  • the performance monitor controls a pressure transducer located proximate the fan, a flow meter located proximate the filter, a voltmeter monitoring the charge of the battery and a pressure.
  • transducer 213 located in the apparatus 210 which measures the pressure in the space within the mask 212.
  • the pressure transducer 213 is in communication with the space within the mask 212 via a flexible hose 214.
  • the hose 214 is preferably connected to the mask 212 with a fitting which allows ready removal of the hose 214 after use of the apparatus 210.
  • the performance monitor issues a warning signal to the wearer.
  • the warning signal comprises-both an audible tone and an indicator light.
  • the audible tone is generated by a speaker 215 within the apparatus 210, with the tone transmitted through the air transfer hose 211 to the mask 212.
  • the light source is generated by a light emitting diode (LED) 216 with the light transmitted to the field of view of the wearer-in the mask 212 by an optical fibre 217.
  • LED light emitting diode
  • Both the optical fibre 217 and air hose 211 are connected to the mask 212 by fittings which allow ready removal of these items from the mask 212 prior to it being cleaned.

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)
  • External Artificial Organs (AREA)
  • Orthopedics, Nursing, And Contraception (AREA)
  • Duct Arrangements (AREA)

Claims (10)

  1. Beatmungsgerät, welches ein Gesichtsteil oder eine Gesichtsmaske (20a), welche/s zumindest die Nase oder den Mund des Trägers bedeckt, eine Pumpeinheit (10), um Luft in einen Raum innerhalb des Gesichtsteils oder der Gesichtsmaske (20a) zuzuführen, einen Elektromotor (11) innerhalb der Pumpeinheit (10), einen Ventilator (12) anzutreiben, welcher Teil der Pumpeinheit (10) ist, einen Filter (13) zum Filtern der Luft, welche in das Gesichtsteil oder die Gesichtsmaske (20a) eintritt, sowie eine Ventileinheit (40), welche den Luftstrom von der Pumpeinheit (10) zum Gesichtsteil oder der Gesichtsmaske (20a) während der Inhalation und vom Gesichtsteil oder der Gesichtsmaske (20a) weg während der Exhalation steuert, aufweist, wobei die Ventileinheit (40) ein Lufteinlassventil (42) und ein Luftauslassventil (44) aufweist, wobei das Luftauslassventil (44) während der Inhalation durch das Lufteinlassventil (42) durch Luftdruck von der Pumpeinheit (10) in einer geschlossenen Position gehalten und durch die ausgeatmete Luft geöffnet wird, welche außerdem auf das Einlassventil (42) wirkt, um das Eintreten ausgeatmeter Luft in die Pumpeinheit (10) zu verhindern;
       wobei das Gerät ferner Mittel zum Beibehalten und Steuern der Geschwindigkeit des Motors (11) beinhaltet, so dass sich der Ventilator (12) mit einer im Wesentlichen konstanten Geschwindigkeit dreht, ungeachtet dessen, ob vom Benutzer Luft eingeatmet oder ausgeatmet wird.
  2. Beatmungsgerät nach Anspruch 1, bei dem der Ventilator (12) ein Radialventilator ist.
  3. Beatmungsgerät nach Anspruch 1, bei dem das Gerät ein Ventil (14) aufweist, welches den Luftstrom durch die Pumpeinheit (11) steuert, wobei das Ventil (14) so angeordnet ist, dass es sich schließt, wenn der im Beatmungsgerät vorherrschende Druck stromabwärts des Ventilators auf ein vorbestimmtes Niveau ansteigt.
  4. Beatmungsgerät nach Anspruch 1, bei dem das Gerät ferner mit einem Drucksensor (116) und/oder Durchflussmessgerät (117), welcher/s so eingestellt ist, dass er/es den Luftdruck im Gerät und der Luftstrom durch das Gerät, bevorzugt an einem Punkt in der Nähe und stromabwärts des Filters, misst; sowie mit einer Mikroprozessorsteuereinheit (115) zum Überwachen der empfangenen Daten vom Drucksensor (116) und/oder Messgerät (117) und somit zur Sicherstellung des Strömungswiderstandes des Filters ausgestattet ist.
  5. Beatmungsgerät nach Anspruch 4, bei dem der Drucksensor (116) eine flexible Membran, die so angeordnet ist, dass sie sich bei Druckänderungen biegt, einen Ultraschall-Transmitter, der so angeordnet ist, dass er den Ultraschall auf die Membran richtet, einen Ultraschall-Empfänger zum Erkennen des von der Membran reflektierten Ultraschalls und ein Analysegerät aufweist, wobei das Analysegerät zur Bestimmung eines Parameters basierend auf der Übertragungszeit des Ultraschalls zwischen dem Transmitter, der Membran und dem Empfänger in der Lage und so kalibriert ist, dass es eine Angabe des Luftdrucks zur Mikroprozessorsteuereinheit (115) liefert.
  6. Beatmungsgerät nach Anspruch 5, bei dem sich eine Temperatursonde in der Nähe des Drucksensors befindet, wobei die Temperatursonde ein Signal an das Analysegerät liefert, welches die gemessene Temperatur anzeigt, um es dem Analysegerät zu ermöglichen, einen Ausgleichsalgorithmus auf den Parameter basierend auf der Übertragungszeit in Übereinstimmung mit der gemessenen Temperatur anzuwenden.
  7. Beatmungsgerät nach Anspruch 1, bei dem das Gerät so eingestellt ist, dass es an den Träger mindestens 150 Liter Luft pro Minute, bevorzugt mindestens 300 Liter Luft pro Minute, bevorzugter mindestens 500 Liter Luft pro Minute, abgibt.
  8. Beatmungsgerät nach Anspruch 1, bei dem das Gerät so ausgebildet ist, dass es Luft an das Einlassventil (42) abgibt, welches die Luft mit einem Druck zwischen null und 10 mBar, bevorzugter nicht mehr als 6 mBar über dem umgebenden Referenzdruck, an das Gesichtsteil oder der Gesichtsmaske abgibt.
  9. Beatmungsgerät nach Anspruch 1, bei dem der Filter (13) zwischen der Pumpeinheit (10) und dem Gesichtsteil oder der Gesichtsmaske (20a) positioniert ist.
  10. Beatmungsgerät nach Anspruch 9, bei dem das Gerät ein Ventil (14)aufweist, welches den Luftstrom durch die Pumpeinheit (10) steuert, wobei das Ventil (14) so angeordnet ist, dass es sich schließt, wenn der innerhalb des Beatmungsgerätes zwischen dem Filter (13) und dem Gesichtsteil oder der Gesichtsmaske (20a) vorherrschende Druck auf ein vorbestimmtes Niveau ansteigt.
EP95926793A 1994-08-01 1995-08-01 Beatmungsgerät Expired - Lifetime EP0773814B1 (de)

Applications Claiming Priority (13)

Application Number Priority Date Filing Date Title
AUPM719094 1994-08-01
AUPM7190A AUPM719094A0 (en) 1994-08-01 1994-08-01 Fan forced positive pressure breathing apparatus
AUPM7190/94 1994-08-01
AUPN1911/95 1995-03-23
AUPN1909A AUPN190995A0 (en) 1995-03-23 1995-03-23 Positive air-purifying respirator
AUPN1911A AUPN191195A0 (en) 1995-03-23 1995-03-23 Positive air-purifying respirator user interface
AUPN1909/95 1995-03-23
AUPN190995 1995-03-23
AUPN191195 1995-03-23
AUPN3106A AUPN310695A0 (en) 1995-05-22 1995-05-22 Improved breathing apparatus
AUPN3106/95 1995-05-22
AUPN310695 1995-05-22
PCT/AU1995/000468 WO1996004043A1 (en) 1994-08-01 1995-08-01 Breathing apparatus

Publications (3)

Publication Number Publication Date
EP0773814A1 EP0773814A1 (de) 1997-05-21
EP0773814A4 EP0773814A4 (de) 1999-07-07
EP0773814B1 true EP0773814B1 (de) 2004-12-22

Family

ID=27424376

Family Applications (1)

Application Number Title Priority Date Filing Date
EP95926793A Expired - Lifetime EP0773814B1 (de) 1994-08-01 1995-08-01 Beatmungsgerät

Country Status (6)

Country Link
EP (1) EP0773814B1 (de)
AT (1) ATE285271T1 (de)
CA (1) CA2196166C (de)
DE (1) DE69533874T2 (de)
ES (1) ES2233946T3 (de)
WO (1) WO1996004043A1 (de)

Families Citing this family (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0862474A4 (de) * 1995-09-18 2000-05-03 Resmed Ltd Druckregelung bei cpap-behandlung oder bei assistierte beatmung
AUPN973596A0 (en) * 1996-05-08 1996-05-30 Resmed Limited Control of delivery pressure in cpap treatment or assisted respiration
EP1197244A3 (de) * 2000-10-11 2002-10-23 Micronel AG Atemschutzeinrichtung für eine Schutzeinrichtung beispielsweise Schutzmaske, Schutzhaube oder Schutzanzug
JP2004536779A (ja) 2000-11-20 2004-12-09 サイオス インコーポレイテッド ｐ３８キナーゼのインドール型阻害剤
NZ576965A (en) 2006-10-24 2011-12-22 Resmed Motor Technologies Inc Brushless DC motor wherein the magnet and rotor are located in the bearing tube
EP2496297B1 (de) 2009-11-03 2020-09-16 ResMed Pty Ltd Cpap-systeme
CN102892451B (zh) 2010-03-25 2017-03-08 瑞思迈巴黎股份有限公司 用于呼吸治疗装置的可呼吸气体进气口控制设备
CN102763917B (zh) * 2011-05-03 2014-10-22 周瓴 口罩
JP2013192746A (ja) * 2012-03-21 2013-09-30 Shigematsu Works Co Ltd 呼吸装置
EP3669946A1 (de) * 2018-12-18 2020-06-24 Koninklijke Philips N.V. Leckerkennung von gesichtsmasken
WO2019243141A1 (en) * 2018-06-19 2019-12-26 Koninklijke Philips N.V. Leakage detection of face masks
SE545681C2 (en) * 2020-09-30 2023-12-05 Tiki Safety Ab Automatic fan control

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4237877A (en) * 1979-01-22 1980-12-09 Boehler Gabriel D Protective environmental mask with thermoelectric air conditioning system
GB8523331D0 (en) * 1985-09-20 1985-10-23 Devilbiss Co Respiratory protection system
US4827964A (en) * 1987-04-23 1989-05-09 Mine Safety Appliances Company System for metering of breathing gas for accommodation of breathing demand
US4957107A (en) * 1988-05-10 1990-09-18 Sipin Anatole J Gas delivery means
GB8815179D0 (en) * 1988-06-25 1988-08-03 Racal Safety Ltd Differential pressure sensor
US5245994A (en) * 1991-01-08 1993-09-21 National Science Council Air cleaning and supplying system equipped to a helmet for a motorcyclist
GB2264646A (en) * 1992-02-12 1993-09-08 Sabre Safety Ltd Breathing apparatus
DE4205412C2 (de) * 1992-02-22 1994-04-14 Draegerwerk Ag Atemschutzgerät mit verflüssigtem Atemgas
SE9203931L (sv) * 1992-12-29 1994-06-30 Interspiro Ab Optisk varningsanordning

Also Published As

Publication number Publication date
WO1996004043A1 (en) 1996-02-15
CA2196166C (en) 2004-04-06
ES2233946T3 (es) 2005-06-16
EP0773814A4 (de) 1999-07-07
CA2196166A1 (en) 1996-02-15
DE69533874T2 (de) 2005-12-29
EP0773814A1 (de) 1997-05-21
ATE285271T1 (de) 2005-01-15
DE69533874D1 (de) 2005-01-27

Similar Documents

Publication Publication Date Title
US5906203A (en) Breathing apparatus
JP3782823B2 (ja) 呼吸装置の作用を検査する方法
EP0773814B1 (de) Beatmungsgerät
US20020139368A1 (en) Oxygen sensor mounting in medical or flight crew masks for direct indication of blood level oxygen
AU2014340355B2 (en) Heating for powered air unit
EP0200737B1 (de) Künstliches beatmungssystem
US4765325A (en) Method and apparatus for determining respirator face mask fit
US4928684A (en) Apparatus for assisting the spontaneous respiration of a patient
US5074299A (en) Monitor for controlling the flow of gases for breathing during inhalation
EP1064041B1 (de) Automatisches tragbares beatmungsgerät mit überwachungs- und warnungsvorrichtung
US20170296094A1 (en) Breathing apparatus with system-integrated breathing sensor system
EP1038553B1 (de) Strömungsanzeiger für Beatmungsgeräte
US6401714B1 (en) Self contained breathing apparatus
KR960701673A (ko) 수면장애 호흡 제어방법 및 제어장치(method add apparatus for controlling sleep disorder breathing)
JPS6222637B2 (de)
JP3276536B2 (ja) ガス供給装置における同調制御装置及び呼吸センサ
CN101454040A (zh) 呼吸装置测量系统
CN113729338B (zh) 一种智能工矿头盔及其监测方法
US8453646B2 (en) Sensor apparatus and method to regulate air flow in a powered air purifying respirator
AU699492B2 (en) Breathing apparatus
EP0602847A1 (de) Strömungsanzeiger
WO2017198238A1 (en) Automatic wearable powered air purifying system and method
AU729528B2 (en) Breathing apparatus
KR20190029266A (ko) 수동식 인공호흡기의 소리를 이용한 공기공급량 측정장치
CN111529980B (zh) 一次性空气过滤呼吸机的控制系统

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

17P Request for examination filed

Effective date: 19970204

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LI LU MC NL PT SE

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: SAFETY EQUIPMENT SWEDEN AB

A4 Supplementary search report drawn up and despatched

Effective date: 19990526

AK Designated contracting states

Kind code of ref document: A4

Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LI LU MC NL PT SE

RIC1 Information provided on ipc code assigned before grant

Free format text: 6A 62B 7/00 A, 6A 62B 18/00 B, 6A 62B 18/04 B

17Q First examination report despatched

Effective date: 20030314

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LI LU MC NL PT SE

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: CH

Ref legal event code: EP

REG Reference to a national code

Ref country code: IE

Ref legal event code: FG4D

REF Corresponds to:

Ref document number: 69533874

Country of ref document: DE

Date of ref document: 20050127

Kind code of ref document: P

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20050322

REG Reference to a national code

Ref country code: CH

Ref legal event code: NV

Representative=s name: ISLER & PEDRAZZINI AG

REG Reference to a national code

Ref country code: SE

Ref legal event code: TRGR

REG Reference to a national code

Ref country code: GR

Ref legal event code: EP

Ref document number: 20050400948

Country of ref document: GR

REG Reference to a national code

Ref country code: ES

Ref legal event code: FG2A

Ref document number: 2233946

Country of ref document: ES

Kind code of ref document: T3

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: MC

Payment date: 20050725

Year of fee payment: 11

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: LU

Payment date: 20051005

Year of fee payment: 11

PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

26N No opposition filed

Effective date: 20050923

ET Fr: translation filed
PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20060831

REG Reference to a national code

Ref country code: CH

Ref legal event code: PCAR

Free format text: ISLER & PEDRAZZINI AG;POSTFACH 1772;8027 ZUERICH (CH)

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: PT

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20050522

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LU

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20060801

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: ES

Payment date: 20080922

Year of fee payment: 14

Ref country code: CH

Payment date: 20080815

Year of fee payment: 14

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: IT

Payment date: 20080827

Year of fee payment: 14

Ref country code: IE

Payment date: 20080818

Year of fee payment: 14

Ref country code: FR

Payment date: 20080818

Year of fee payment: 14

Ref country code: AT

Payment date: 20080814

Year of fee payment: 14

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GR

Payment date: 20080716

Year of fee payment: 14

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: BE

Payment date: 20090119

Year of fee payment: 14

BERE Be: lapsed

Owner name: *SAFETY EQUIPMENT SWEDEN A.B.

Effective date: 20090831

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LI

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090831

Ref country code: CH

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090831

REG Reference to a national code

Ref country code: FR

Ref legal event code: ST

Effective date: 20100430

REG Reference to a national code

Ref country code: IE

Ref legal event code: MM4A

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: BE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090831

Ref country code: AT

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090801

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090803

Ref country code: FR

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090831

REG Reference to a national code

Ref country code: ES

Ref legal event code: FD2A

Effective date: 20090803

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: GR

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20100303

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IT

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090801

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: ES

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090802

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 20130724

Year of fee payment: 19

Ref country code: SE

Payment date: 20130813

Year of fee payment: 19

Ref country code: NL

Payment date: 20130810

Year of fee payment: 19

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 20130731

Year of fee payment: 19

REG Reference to a national code

Ref country code: DE

Ref legal event code: R119

Ref document number: 69533874

Country of ref document: DE

REG Reference to a national code

Ref country code: NL

Ref legal event code: V1

Effective date: 20150301

REG Reference to a national code

Ref country code: SE

Ref legal event code: EUG

GBPC Gb: european patent ceased through non-payment of renewal fee

Effective date: 20140801

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: NL

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20150301

REG Reference to a national code

Ref country code: DE

Ref legal event code: R119

Ref document number: 69533874

Country of ref document: DE

Effective date: 20150303

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20140802

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20150303

Ref country code: GB

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20140801