CA1305391C - Breathing apparatus - Google Patents
Breathing apparatusInfo
- Publication number
- CA1305391C CA1305391C CA000599378A CA599378A CA1305391C CA 1305391 C CA1305391 C CA 1305391C CA 000599378 A CA000599378 A CA 000599378A CA 599378 A CA599378 A CA 599378A CA 1305391 C CA1305391 C CA 1305391C
- Authority
- CA
- Canada
- Prior art keywords
- breathing
- pressure
- bag
- breathing bag
- wall
- 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 - Fee Related
Links
Classifications
-
- 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
Abstract
Abstract A circulating breathing apparatus for pressurized operation with a source of compressed gas that discharges the respiration gas and with a breathing bag that is under tension in the inhalation phase, this tension being reduced with the help of a controller that recognizes the phase of respiration, so as to assist respiration in the exhalation phase, is to be improved so as to be a simplified, purely pneumatic-mechanical construction.
according to the present invention, this has been achieved in that it incorporates a pneumatic control valve (3) that can be switched over between the inhalation phase and the exhalation phase and is controlled directly by the pressure differential between exhalation pressure and the pressure within the breathing bag (6), which during the inhalation phase, connects the source of compressed gas with the breathing bag (6) and during the exhalation phase controls a pneumatic adjuster (4) by interrupting the connection below the compressed-gas pressure head from the source of compressed gas (1) in such a manner that the mechanical pretension on the breathing bag is reduced.
according to the present invention, this has been achieved in that it incorporates a pneumatic control valve (3) that can be switched over between the inhalation phase and the exhalation phase and is controlled directly by the pressure differential between exhalation pressure and the pressure within the breathing bag (6), which during the inhalation phase, connects the source of compressed gas with the breathing bag (6) and during the exhalation phase controls a pneumatic adjuster (4) by interrupting the connection below the compressed-gas pressure head from the source of compressed gas (1) in such a manner that the mechanical pretension on the breathing bag is reduced.
Description
~3(~53~1 The present invention relates to a breathing apparatus for pressurized operation with a source of compreesed gas that dispenses the respiration ga~ and, with a breathing bag that is under tension during the inhalation phase, this tension being reduced with the help of a governing element that recognizes the respiration phase, this being done so as to assist respiration during the exhalation phase.
In a circulating breathing apparatus for pressurized operation it is en~ured that there i5 always a higher pressure within the respiration circuit relative to ambient pressure in order that no injurious substances can enter the respiration circuit. This elevated pressure can be generated by elastic pretensioning of the breathing bag by means of a mechanical/pneumatic spring system, as is shown, for example, in DE-PS 31 05 637. In such a system, however, respiration is additionally encumbered by the flow resistances that also have to be overcome during expansion ln the exhalatlon phase, slnce the pretension in the breathing bag, which is generated by the mechanical or pneumatic sprlng, is maintained throughout the exhalation phase. Respiration resistance shifts towards higher pressures.
DE-OS 34 29 345 describes a circulating breathing apparatus for pressurized operation in which the source for the compressed gas also supplies an auxillary system through a compressed-gas feed line, this bringing about mechanical pretensioning of the breathing bag so as to increase the preRsure. A sensor that i8 13C~53~
connected to a measuring circuit distinguishes between the phases of respiration and during the exhalation phase controls the auxiliary system in such a manner that the excess pressure that is applied to the breathing bag is decreased.
It would appear that for specific applications, it would be desirable to arrive at a simplified configuration of the respiratory support system that is based exclusively on pneumatic-mechanical components without an electronic control circuit and without additional sources of electrical energy.
It is the task of the present invention to configure a circulating breathing apparatus of the type described in the introduction hereto in a simple manner, to support respiration in the inhalation and the exhalation phases of the respiratory cycle.
The solution to this task has been found in that a pneumatic control valve has been used; this control valve can be switched over between the inhalation phase and the exhalation phase and is controlled directly from the pressure differential between exhalation pressure and the pressure within the breathing bag.
During the inhalation phase, this control valve connects the source of compressed gas with the breathing bag and during the exhalation phase controls a pneumatic adjuster by interrupting the connection beneath the compressed-gas pressure head from the source of compressed gas in such a manner that the mechanical pretension on the breathing bag is reduced. A mechanical drive element, which can be variously configured, for example a 13(~3~
bellows, a diaphragm, an cylinder unit or the like, can be used as a pneumatic adjuster.
Thus, in the inhalation phase, the pretension on the breathing bag brings about the maintenance of the overpressure in the respiration circuit and a certain respiratory assistance.
~he exhalation phase is recognized by the control valve, so that only then is the compensation for the pretension initiated. The compressed-gas pressure head acts on the pneumatic adjuster, which acts mechanically and directly on a wall section of the breathing bag and causes this to move in a direction that will increase its volume. Thus, the energy in the continuously entering respiration gas is used to reduce or almost eliminate the pretension on the breathing bag during the e~halation phase.
A further advantage can be achieved under some circumstances in that a mechanical pretensioning unit is provided in order to generate the pretension on the breathing bag, this unit incorporating a spring element. The breathing bag can incorporate a moving, loading rockar arm as a section of its wall, this roclcer arm being connected to the spring element. In a further embodiment of the present invention, the transfer of force from the rocker arm to the spring element can be arranged through a cam plate such that the discharge pressure of the breathing bag remains constant, or at least nearly so, regardless of the degree to which it is filled. The control valve, the pneumatic adjuster, the breathing bag, and the selected pre-tension are so matched to each other that no induced breathing 13~S3~1 can occur, even though a preselected overpressure is maintained constantly in the respiration circuit.
In order to render the described pretensioning independent of position, it is expedient to provide the rocker arm which loads the breathing back with a counter-weight at the end that is opposite the pivot point.
The pneumatic control valve is advantageously configured as a double-diaphragm valve in which a control diaphragm passes the force differential between the exhalation pressure and the pressure within the breathing bag to a governor diaphragm that manages the changeover of the flow of compressed gas between the breathing bag in the inhalation phase and the pneumatic adjuster in the exhalation phase.
In an expedient embodiment, provision can be made such that the exhalation pressure is tapped off as a pressure head ahead of a component that generates a considerable exhalation resistance.
The exhalation pressure can thus be tapped off ahead of the absorption bed of the respiratory gas cartridge that binds the carbon dioxide, or ahead of the breathing tubes and the like.
In a further advantageous embodiment the pneumatic adjuster transfers a moment that is opposite the tensile force of the spring element through a mechanical coupler to the rocker arm of the breathing bay. This can take place, for example, in that the coupler has a flexible end and is there connected with the shaft of the rocker arm, so as to pass part way around the shaft. The flexible end can be configured as a cable if the usable travel of 13(~53~1 ~he adjuster is to be in form of a pull, or as a leaf spring if the usable travel is in the form of a push.
A further advantageous configuration is that a diaphragm is provided in the adjuster element, this acting through a toothed rack on a toothed ring that is installed at the point of rotation of the rocker arm.
A smoothing system ensures that any pressure variations in the source of respiration gas that could occur do not lead to inopportune operation of the adjuster. At the same time, an upper limit for the compressed-gas pressure head is established by the high-pressure relief valve. When the control valve is open, the choke releases a constant flow of respiration gas, when at the same time the flow pressure drops to values that unload the adjuster. The quantities of gas discharged at the high-pressure relief valve are preferably passed to the breathing bag.
In summary, according to one broad aspect the present invention provides a closed cycle breathing apparatus, comprising:
a pressurized air source; a bellows-type breathing bag; an inspiration line connected to said breathing bag; an expiration line connected to said breathing bag; prestress means for applying a Eorce to said breathing bag for contracting said breathing bag to urge air out of said breathing bag; control means for counter-acting said prestress means allowing expansion of said breathing bag during expiration including a pneumatic control valve means connected to said exhalation line and connected to said breathing bag for responding to a difference between gas pressure in said exhalation line and gas pressure in said breathing bag for 13~5391 switching between an inspiration phase and an expiration phase based on said difference and for connecting said pressuri~ed b:reathing source with said air bag during the inspiration phase and interrupting the connection between said pressurized air source and the breathing bag during the expiration phase and for actuating a pneumatic adjustment element during the expiration phase for offsetting the force applied by said prestress means.
According to a second broad aspect the present invention provides a pressure operated closed cycle breathing device, comprising a respiratory gas supply under pressure, a bellows member air bag having a fixed wall with inner and outer ends, a rnoveable wall pivotally supported adjacent said inner end of said fixed wall and having a moveable wall outer end, a bellows member connected between said fixed wall outer end and said moveable wall outer end and enclosing a space, an inhalation line connected to said air bag space, an exhalation line connected to said air bag space, control means connected to said respiratory gas supply, said control means including an interior portion a diaphragm means within said interior portion dividing said interior into a Eirst space connected to said air bag space and a second space connected to said exhalation said diaphragm means line for sensing a pressure difference between said exhalation line and said air bag space and Eor connecting said respiratory gas supply to said air bag space in dependence upon the pressure difference sensed, mechanical coupling means having a mechanical adjusting element connected to said moveable wall to move said moveable wall during exhalatlon and connected to said respiratory gas delivery line and , i'r,~
. ,.
i3(~539~
responsive to pressure in said line delivery to aid in moving said moveable wall.
The present invention will be described in greater detail below on the basis of an embodiment shown in the drawing appended hereto, which shows additional features.
A source 1 for compressed gas that dispenses the breathing gas is connected through a branched connector line 2 on the one side to a double-diaphragm valve 3 that serves as a pneumatic control valve, and on the other to a pneumatic adjuster 4. A gas discharge line 5 of the double-diaphragm valve 3 opens out into a breathing bag 6 that is configured as a bellows 9.
Between the source 1 of compressed gas and the connector line 2 there is a choke 35 of a smoothing system. A high-6b r~
. . . _.
13~5391 pressure relief valve 36 branches off ahead of the choke 35 andthe outflow opening of this opens out into the gas discharge line 5 through an outflow line 37.
The breathing bag 6 incorporates a fixed wall section 7 to which the accordeon-fold bellows 9 is attached through a movable rocker arm 8. The end of the rocker arm that is opposite the pivot point 10 is fitted with a balance weight 11.
A spring element 12 is provided to load the breathing bag 6, and this generates spring tension through a compression spring 13 and this is passed through a mechanical tension connection 14 to an attachment point 16 on the rocker arm 8 of the breathing bag 6 through an interposed cam plate 15.
An inhalation line 17 leads from the breathing bag 6 to the inhalation connection 18 of the mask (not shown herein).
An exhalation connector 19 on the mask is connected through a supply line 20, which is similarly branched, to a lime bed 21 that is used to absorb CO2. A return line 22 for the breathing gas connects the lims bed 21 with the interior space of the breathing bag 6.
Within the double-diaphragm valve , the branched supply line 20 is connected on one side with a secondary chamber ahead of the control diaphragm 23 that is connected on its other side to a further secondary space that is connected through a pressure-check line 24 to the interior space within the breathing bag 6.
A plunger 25 is connected to the control diaphragm 23 of the double-diaphragm valve 3; this plunger lies against a governor ~3~53~
diaphragm 26 and governs the movement of this towards a valve seat 27 so as to open the connecting line 2 to the gas discharge line 5. The control diaphragm 23 thus acts as a controlling element that recognizes the phase of respiration.
The pneumatic adjuster 4 has an expansion chamber 28 within which there is a diaphragm 29. This is connected through a mechanical coupling 30 with the movable rocker arm 8 so that a Eorce is exerted in the movable rocker arm 8 during the exhalation phase which at least in part relieves this rocker arm 8 of the spring tension that is effective as a result of the compression spri.ng 13.
In thc inhalation phase, respiration gas flows through the connector iine 2, through the valve seat 27 of the double-diaphragm valve 3--which has been opened by the governor diaphragm 26--and into the gas discharge line 5, and from there into the breathing bag 6. The rocker arm 8 is under spring tension from the compres.sion spring 13 and is moved in the direction indicated by the inhalation arrow, so that respiration gas moves from the breathing bag 6 along the inhalation line 17 to the inhalation connector 18 of the mask. The spring tension acting on the breathing bag 6, means that a slight overpressure is achieved during inhalation.
The cam plate 15 that is fixed to the movable rocker arm 8 so as to be unab].e to rotate independently of it is so con--tou:red that regardless of the filled volume of the breathing bag 6 there will be a constant pre-pressure on the inhalation line 17.
13(:~S;~9l In the inhalation phase, the pneumatic adjuster 4 is in the upper position of the membrane 29 (as indicated by the dashed line), so that no add~tional relieving force that opposes the action of ths compression spring 13 occurs.
At the beginning of the exhalation phase, the exhaled gas ls introduced from the exhalation connector 19 into the branched supply line 20. The pressure that builds up ahead of the lime bed 21 when this is done is transferred through the feed line 20 onto one side of the control diaphragm 23, the other side of which is subjected to the pressure from the interior space of the breathing bag 6 along the pressure-check line 24. The control diaphragm 23 with the plunger 25 that is connected to it, and the governor diaphragm 26 move into the closed position depending on the pressure differential that results from the foregoing, so that the supply of respiration gas through the connector line 2 and gas-discharge line 5 ceases. When this happens, the pressure i.n the connector line 2 increases, and the pressure build up moves into the expansion space 28 in front of the diaphragm 29 of the pneumati.c adjuster 4. This means that the mechaniaal coupler 30, which ls in the form of a toothed rack and engages in a toothed ring 38 that is installed around the shaft of the rocker arm 8, is moved so that a counter-action to the mechanical pretension occurs by the compression spring 13 on the tension connection 14. By this means, the expansion of the breathing bag 6 is assisted and exhalation is made easier.
13(;t53~
The corresponding movements are indicated by the exhalation arrows.
In the circulating breathing apparatus, respiration in the inhalation phase is assisted by spring tension of the movable rocker arm 8 and in the exhalation phase by the pneumatic adjuster ~, the mechanical coupler 30 of which acts against the spring action of the compression spring 13.
In each case, however, pains have been taken to ensure that a preset nominal value in the respiration circuit is always reached in both the exhalation phase and in the inhalation phase, so that the ingress o~ injurious substances is always prevented.
In a circulating breathing apparatus for pressurized operation it is en~ured that there i5 always a higher pressure within the respiration circuit relative to ambient pressure in order that no injurious substances can enter the respiration circuit. This elevated pressure can be generated by elastic pretensioning of the breathing bag by means of a mechanical/pneumatic spring system, as is shown, for example, in DE-PS 31 05 637. In such a system, however, respiration is additionally encumbered by the flow resistances that also have to be overcome during expansion ln the exhalatlon phase, slnce the pretension in the breathing bag, which is generated by the mechanical or pneumatic sprlng, is maintained throughout the exhalation phase. Respiration resistance shifts towards higher pressures.
DE-OS 34 29 345 describes a circulating breathing apparatus for pressurized operation in which the source for the compressed gas also supplies an auxillary system through a compressed-gas feed line, this bringing about mechanical pretensioning of the breathing bag so as to increase the preRsure. A sensor that i8 13C~53~
connected to a measuring circuit distinguishes between the phases of respiration and during the exhalation phase controls the auxiliary system in such a manner that the excess pressure that is applied to the breathing bag is decreased.
It would appear that for specific applications, it would be desirable to arrive at a simplified configuration of the respiratory support system that is based exclusively on pneumatic-mechanical components without an electronic control circuit and without additional sources of electrical energy.
It is the task of the present invention to configure a circulating breathing apparatus of the type described in the introduction hereto in a simple manner, to support respiration in the inhalation and the exhalation phases of the respiratory cycle.
The solution to this task has been found in that a pneumatic control valve has been used; this control valve can be switched over between the inhalation phase and the exhalation phase and is controlled directly from the pressure differential between exhalation pressure and the pressure within the breathing bag.
During the inhalation phase, this control valve connects the source of compressed gas with the breathing bag and during the exhalation phase controls a pneumatic adjuster by interrupting the connection beneath the compressed-gas pressure head from the source of compressed gas in such a manner that the mechanical pretension on the breathing bag is reduced. A mechanical drive element, which can be variously configured, for example a 13(~3~
bellows, a diaphragm, an cylinder unit or the like, can be used as a pneumatic adjuster.
Thus, in the inhalation phase, the pretension on the breathing bag brings about the maintenance of the overpressure in the respiration circuit and a certain respiratory assistance.
~he exhalation phase is recognized by the control valve, so that only then is the compensation for the pretension initiated. The compressed-gas pressure head acts on the pneumatic adjuster, which acts mechanically and directly on a wall section of the breathing bag and causes this to move in a direction that will increase its volume. Thus, the energy in the continuously entering respiration gas is used to reduce or almost eliminate the pretension on the breathing bag during the e~halation phase.
A further advantage can be achieved under some circumstances in that a mechanical pretensioning unit is provided in order to generate the pretension on the breathing bag, this unit incorporating a spring element. The breathing bag can incorporate a moving, loading rockar arm as a section of its wall, this roclcer arm being connected to the spring element. In a further embodiment of the present invention, the transfer of force from the rocker arm to the spring element can be arranged through a cam plate such that the discharge pressure of the breathing bag remains constant, or at least nearly so, regardless of the degree to which it is filled. The control valve, the pneumatic adjuster, the breathing bag, and the selected pre-tension are so matched to each other that no induced breathing 13~S3~1 can occur, even though a preselected overpressure is maintained constantly in the respiration circuit.
In order to render the described pretensioning independent of position, it is expedient to provide the rocker arm which loads the breathing back with a counter-weight at the end that is opposite the pivot point.
The pneumatic control valve is advantageously configured as a double-diaphragm valve in which a control diaphragm passes the force differential between the exhalation pressure and the pressure within the breathing bag to a governor diaphragm that manages the changeover of the flow of compressed gas between the breathing bag in the inhalation phase and the pneumatic adjuster in the exhalation phase.
In an expedient embodiment, provision can be made such that the exhalation pressure is tapped off as a pressure head ahead of a component that generates a considerable exhalation resistance.
The exhalation pressure can thus be tapped off ahead of the absorption bed of the respiratory gas cartridge that binds the carbon dioxide, or ahead of the breathing tubes and the like.
In a further advantageous embodiment the pneumatic adjuster transfers a moment that is opposite the tensile force of the spring element through a mechanical coupler to the rocker arm of the breathing bay. This can take place, for example, in that the coupler has a flexible end and is there connected with the shaft of the rocker arm, so as to pass part way around the shaft. The flexible end can be configured as a cable if the usable travel of 13(~53~1 ~he adjuster is to be in form of a pull, or as a leaf spring if the usable travel is in the form of a push.
A further advantageous configuration is that a diaphragm is provided in the adjuster element, this acting through a toothed rack on a toothed ring that is installed at the point of rotation of the rocker arm.
A smoothing system ensures that any pressure variations in the source of respiration gas that could occur do not lead to inopportune operation of the adjuster. At the same time, an upper limit for the compressed-gas pressure head is established by the high-pressure relief valve. When the control valve is open, the choke releases a constant flow of respiration gas, when at the same time the flow pressure drops to values that unload the adjuster. The quantities of gas discharged at the high-pressure relief valve are preferably passed to the breathing bag.
In summary, according to one broad aspect the present invention provides a closed cycle breathing apparatus, comprising:
a pressurized air source; a bellows-type breathing bag; an inspiration line connected to said breathing bag; an expiration line connected to said breathing bag; prestress means for applying a Eorce to said breathing bag for contracting said breathing bag to urge air out of said breathing bag; control means for counter-acting said prestress means allowing expansion of said breathing bag during expiration including a pneumatic control valve means connected to said exhalation line and connected to said breathing bag for responding to a difference between gas pressure in said exhalation line and gas pressure in said breathing bag for 13~5391 switching between an inspiration phase and an expiration phase based on said difference and for connecting said pressuri~ed b:reathing source with said air bag during the inspiration phase and interrupting the connection between said pressurized air source and the breathing bag during the expiration phase and for actuating a pneumatic adjustment element during the expiration phase for offsetting the force applied by said prestress means.
According to a second broad aspect the present invention provides a pressure operated closed cycle breathing device, comprising a respiratory gas supply under pressure, a bellows member air bag having a fixed wall with inner and outer ends, a rnoveable wall pivotally supported adjacent said inner end of said fixed wall and having a moveable wall outer end, a bellows member connected between said fixed wall outer end and said moveable wall outer end and enclosing a space, an inhalation line connected to said air bag space, an exhalation line connected to said air bag space, control means connected to said respiratory gas supply, said control means including an interior portion a diaphragm means within said interior portion dividing said interior into a Eirst space connected to said air bag space and a second space connected to said exhalation said diaphragm means line for sensing a pressure difference between said exhalation line and said air bag space and Eor connecting said respiratory gas supply to said air bag space in dependence upon the pressure difference sensed, mechanical coupling means having a mechanical adjusting element connected to said moveable wall to move said moveable wall during exhalatlon and connected to said respiratory gas delivery line and , i'r,~
. ,.
i3(~539~
responsive to pressure in said line delivery to aid in moving said moveable wall.
The present invention will be described in greater detail below on the basis of an embodiment shown in the drawing appended hereto, which shows additional features.
A source 1 for compressed gas that dispenses the breathing gas is connected through a branched connector line 2 on the one side to a double-diaphragm valve 3 that serves as a pneumatic control valve, and on the other to a pneumatic adjuster 4. A gas discharge line 5 of the double-diaphragm valve 3 opens out into a breathing bag 6 that is configured as a bellows 9.
Between the source 1 of compressed gas and the connector line 2 there is a choke 35 of a smoothing system. A high-6b r~
. . . _.
13~5391 pressure relief valve 36 branches off ahead of the choke 35 andthe outflow opening of this opens out into the gas discharge line 5 through an outflow line 37.
The breathing bag 6 incorporates a fixed wall section 7 to which the accordeon-fold bellows 9 is attached through a movable rocker arm 8. The end of the rocker arm that is opposite the pivot point 10 is fitted with a balance weight 11.
A spring element 12 is provided to load the breathing bag 6, and this generates spring tension through a compression spring 13 and this is passed through a mechanical tension connection 14 to an attachment point 16 on the rocker arm 8 of the breathing bag 6 through an interposed cam plate 15.
An inhalation line 17 leads from the breathing bag 6 to the inhalation connection 18 of the mask (not shown herein).
An exhalation connector 19 on the mask is connected through a supply line 20, which is similarly branched, to a lime bed 21 that is used to absorb CO2. A return line 22 for the breathing gas connects the lims bed 21 with the interior space of the breathing bag 6.
Within the double-diaphragm valve , the branched supply line 20 is connected on one side with a secondary chamber ahead of the control diaphragm 23 that is connected on its other side to a further secondary space that is connected through a pressure-check line 24 to the interior space within the breathing bag 6.
A plunger 25 is connected to the control diaphragm 23 of the double-diaphragm valve 3; this plunger lies against a governor ~3~53~
diaphragm 26 and governs the movement of this towards a valve seat 27 so as to open the connecting line 2 to the gas discharge line 5. The control diaphragm 23 thus acts as a controlling element that recognizes the phase of respiration.
The pneumatic adjuster 4 has an expansion chamber 28 within which there is a diaphragm 29. This is connected through a mechanical coupling 30 with the movable rocker arm 8 so that a Eorce is exerted in the movable rocker arm 8 during the exhalation phase which at least in part relieves this rocker arm 8 of the spring tension that is effective as a result of the compression spri.ng 13.
In thc inhalation phase, respiration gas flows through the connector iine 2, through the valve seat 27 of the double-diaphragm valve 3--which has been opened by the governor diaphragm 26--and into the gas discharge line 5, and from there into the breathing bag 6. The rocker arm 8 is under spring tension from the compres.sion spring 13 and is moved in the direction indicated by the inhalation arrow, so that respiration gas moves from the breathing bag 6 along the inhalation line 17 to the inhalation connector 18 of the mask. The spring tension acting on the breathing bag 6, means that a slight overpressure is achieved during inhalation.
The cam plate 15 that is fixed to the movable rocker arm 8 so as to be unab].e to rotate independently of it is so con--tou:red that regardless of the filled volume of the breathing bag 6 there will be a constant pre-pressure on the inhalation line 17.
13(:~S;~9l In the inhalation phase, the pneumatic adjuster 4 is in the upper position of the membrane 29 (as indicated by the dashed line), so that no add~tional relieving force that opposes the action of ths compression spring 13 occurs.
At the beginning of the exhalation phase, the exhaled gas ls introduced from the exhalation connector 19 into the branched supply line 20. The pressure that builds up ahead of the lime bed 21 when this is done is transferred through the feed line 20 onto one side of the control diaphragm 23, the other side of which is subjected to the pressure from the interior space of the breathing bag 6 along the pressure-check line 24. The control diaphragm 23 with the plunger 25 that is connected to it, and the governor diaphragm 26 move into the closed position depending on the pressure differential that results from the foregoing, so that the supply of respiration gas through the connector line 2 and gas-discharge line 5 ceases. When this happens, the pressure i.n the connector line 2 increases, and the pressure build up moves into the expansion space 28 in front of the diaphragm 29 of the pneumati.c adjuster 4. This means that the mechaniaal coupler 30, which ls in the form of a toothed rack and engages in a toothed ring 38 that is installed around the shaft of the rocker arm 8, is moved so that a counter-action to the mechanical pretension occurs by the compression spring 13 on the tension connection 14. By this means, the expansion of the breathing bag 6 is assisted and exhalation is made easier.
13(;t53~
The corresponding movements are indicated by the exhalation arrows.
In the circulating breathing apparatus, respiration in the inhalation phase is assisted by spring tension of the movable rocker arm 8 and in the exhalation phase by the pneumatic adjuster ~, the mechanical coupler 30 of which acts against the spring action of the compression spring 13.
In each case, however, pains have been taken to ensure that a preset nominal value in the respiration circuit is always reached in both the exhalation phase and in the inhalation phase, so that the ingress o~ injurious substances is always prevented.
Claims (11)
1. A closed cycle breathing apparatus, comprising: a pressurized air source; a bellows-type breathing bag; an inspiration line connected to said breathing bag; an expiration line connected to said breathing bag; prestress means for applying a force to said breathing bag for contracting said breathing bag to urge air out of said breathing bag; control means for counter-acting said prestress means allowing expansion of said breathing bag during expiration including a pneumatic control valve means connected to said exhalation line and connected to said breathing bag for responding to a difference between gas pressure in said exhalation line and gas pressure in said breathing bag for switching between an inspiration phase and an expiration phase based on said difference and for connecting said pressurized breathing source with said air bag during the inspiration phase and interrupting the connection between said pressurized air source and the breathing bag during the expiration phase and for actuating a pneumatic adjustment element during the expiration phase for offsetting the force applied by said prestress means.
2. A closed cycle breathing apparatus according to claim 1 wherein said prestress means includes a spring element for the generation of a prestress force on said breathing bag.
3. A closed cycle breathing apparatus according to claim 2, wherein said breathing bag has a moveable pivoting wall connected to said spring element.
4. A closed cycle breathing apparatus according to claim 3, wherein said prestress means includes transmission means for transmission of force from said wall to said spring element including a curved plate with a connection element extending around said curve plate, said connection element acting on said wall so as to insure that said supply pressure of said breathing bag is at least approximately constant independently of its filling volume.
5. A closed cycle breathing device and gas mask according to claim 4, wherein said wall is connected to a counterbalance weight.
6. A closed cycle breathing apparatus according to claim 1, wherein said pneumatic control valve comprises a double membrane valve including a control membrane transmitting a differential pressure between pressure in said exhalation line and pressure in said breathing bag, and a switch membrane means operatively connected to said control membranes for switching pressurized air flow between the breathing bag and said pneumatic adjustment element based on the position of said control membrane.
7. A closed cycle breathing apparatus according to claim 3, wherein said expiration line is in fluid communication with said breathing bag such that an exhalation pressure acts as dynamic pressure on an interior surface of said moveable pivoting wall.
8. A closed cycle breathing apparatus according to claim 3, wherein said pneumatic adjustment element is provided for transferring a moment to the pivoting wall by means of a mechanical coupling element to oppose the force applied by said spring element.
9. A closed cycle breathing apparatus according to claim 8, wherein said pneumatic adjustment element has an expansion chamber which is closed on one side by an adjustment membrane, said moveable pivoting wall having a pivot point, a tooth wheel carried at said pivot point and being rotatable with said wall, a tooth rod engaged with said toothed wheel and engaging said adjustment membrane and being actuatable thereby to rotate said tooth wheel to change the position of said wall.
10. A closed cycle breathing apparatus according to claim 1 wherein said air source includes smoothing means for smoothing pressure peaks comprising a throttle in a main flow line and a pressure release valve branching off from said throttle.
11. A pressure operated closed cycle breathing device, comprising a respiratory gas supply under pressure, a bellows member air bag having a fixed wall with inner and outer ends, a moveable wall pivotally supported adjacent said inner end of said fixed wall and having a moveable wall outer end, a bellows member connected between said fixed wall outer end and said moveable wall outer end and enclosing a space, an inhalation line connected to said air bag space, an exhalation line connected to said air bag space, control means connected to said respiratory gas supply, said control means including an interior portion a diaphragm means within said interior portion dividing said interior into a first space connected to said air bag space and a second space connected to said exhalation said diaphragm means line for sensing a pressure difference between said exhalation line and said air bag space and for connecting said respiratory gas supply to said air bag space in dependence upon the pressure difference sensed, mechanical coupling means having a mechanical adjusting element connected to said moveable wall to move said moveable wall during exhalation and connected to said respiratory gas delivery line and responsive to pressure in said line delivery to aid in moving said moveable wall.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE3823382A DE3823382C1 (en) | 1988-07-09 | 1988-07-09 | |
| DEP3823382.7-22 | 1988-07-09 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1305391C true CA1305391C (en) | 1992-07-21 |
Family
ID=6358381
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000599378A Expired - Fee Related CA1305391C (en) | 1988-07-09 | 1989-05-11 | Breathing apparatus |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US5038772A (en) |
| JP (1) | JPH0265871A (en) |
| AU (1) | AU625576B2 (en) |
| CA (1) | CA1305391C (en) |
| DE (1) | DE3823382C1 (en) |
| GB (1) | GB2220362B (en) |
| ZA (1) | ZA894456B (en) |
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| SE465497B (en) * | 1989-11-24 | 1991-09-23 | Minco Ab | DEVICE FOR STUDYING A PERSON'S LUNG FUNCTION |
| SE504376C2 (en) * | 1995-07-05 | 1997-01-20 | Comasec International Sa | Respiratory Equipment |
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| US6595215B2 (en) | 2000-03-13 | 2003-07-22 | Innomed Technologies, Inc. | Ventilation interface for sleep apnea therapy |
| US6478026B1 (en) | 1999-03-13 | 2002-11-12 | Thomas J. Wood | Nasal ventilation interface |
| US20060150982A1 (en) * | 2003-08-05 | 2006-07-13 | Wood Thomas J | Nasal ventilation interface and system |
| US7059328B2 (en) * | 2000-03-13 | 2006-06-13 | Innomed Technologies, Inc. | Ventilation interface for sleep apnea therapy |
| US6679265B2 (en) * | 2001-10-25 | 2004-01-20 | Worldwide Medical Technologies | Nasal cannula |
| EP2913079B1 (en) | 2002-09-06 | 2017-10-25 | ResMed Limited | Cushion for respiratory mask assembly |
| NZ553302A (en) | 2002-11-06 | 2008-10-31 | Resmed Ltd | Mask assembly with frame that can be flexed about longitudinal axis |
| US20040182397A1 (en) * | 2003-03-21 | 2004-09-23 | Innomed Technologies, Inc. | Nasal interface including ventilation insert |
| US7191781B2 (en) | 2003-08-05 | 2007-03-20 | Innomed Technologies, Inc. | Nasal ventilation interface and system |
| US20050235999A1 (en) * | 2004-04-23 | 2005-10-27 | Wood Thomas J | Nasal ventilation interface and system |
| US7472707B2 (en) * | 2003-08-06 | 2009-01-06 | Innomed Technologies, Inc. | Nasal interface and system including ventilation insert |
| US7000613B2 (en) * | 2003-08-06 | 2006-02-21 | Innomed Technologies, Inc. | Nasal interface and system including ventilation insert |
| US6997187B2 (en) * | 2003-09-10 | 2006-02-14 | Innomed Technologies, Inc. | Nasal interface and system including ventilation insert |
| EP2510968B1 (en) | 2003-12-31 | 2017-02-08 | ResMed Limited | Compact oronasal patient interface |
| JP4787243B2 (en) | 2004-06-03 | 2011-10-05 | レスメド・リミテッド | Cushion for patient intermediate attachment |
| US8261745B2 (en) | 2004-12-10 | 2012-09-11 | Respcare, Inc. | Ventilation interface |
| US8042539B2 (en) * | 2004-12-10 | 2011-10-25 | Respcare, Inc. | Hybrid ventilation mask with nasal interface and method for configuring such a mask |
| DE202006021258U1 (en) | 2005-01-12 | 2014-05-05 | Resmed Limited | Upholstery for patient interface |
| US7559327B2 (en) | 2005-05-31 | 2009-07-14 | Respcare, Inc. | Ventilation interface |
| CN101237902B (en) | 2005-06-06 | 2012-02-29 | 雷斯梅德有限公司 | Mask system |
| NZ591992A (en) | 2005-10-14 | 2012-11-30 | Resmed Ltd | Breathing mask with cushion attached to frame via lip of cushion engaging within recess between frame outer and inner walls, and guided in via angled protrusion of frame inner wall |
| US20090126739A1 (en) | 2005-10-25 | 2009-05-21 | Resmed Limited | Interchangeable Mask Assembly |
| US20070163591A1 (en) * | 2006-01-13 | 2007-07-19 | Ross Julian T | Method and system for providing breathable air in a closed circuit |
| US8789532B2 (en) | 2006-03-10 | 2014-07-29 | Respcare, Inc. | Ventilation mask |
| USD597199S1 (en) | 2006-04-28 | 2009-07-28 | Resmed Limited | Respiratory mask frame |
| USD623288S1 (en) | 2006-04-28 | 2010-09-07 | Resmed Limited | Patient interface |
| US8887725B2 (en) * | 2006-05-10 | 2014-11-18 | Respcare, Inc. | Ventilation interface |
| US9937312B2 (en) | 2006-07-28 | 2018-04-10 | Resmed Limited | Delivery of respiratory therapy with foam interface |
| CN101516427B (en) | 2006-07-28 | 2012-08-08 | 雷斯梅德有限公司 | Delivery of respiratory therapy |
| JP5911189B2 (en) | 2006-12-15 | 2016-04-27 | レスメド・リミテッドＲｅｓＭｅｄ Ｌｉｍｉｔｅｄ | Respiratory therapy |
| US8517023B2 (en) | 2007-01-30 | 2013-08-27 | Resmed Limited | Mask system with interchangeable headgear connectors |
| NZ578334A (en) | 2007-04-19 | 2011-01-28 | Resmed Ltd | Mask frame connected to face cushion via intervening clip |
| NZ570059A (en) | 2007-07-30 | 2010-08-27 | Resmed Ltd | Nostril prong elastic support for gas breathing mask |
| WO2009108994A1 (en) | 2008-03-04 | 2009-09-11 | Resmed Ltd | A foam respiratory mask |
| DE202009018972U1 (en) | 2008-03-04 | 2014-12-09 | Resmed Limited | mask system |
| US11331447B2 (en) | 2008-03-04 | 2022-05-17 | ResMed Pty Ltd | Mask system with snap-fit shroud |
| NZ608162A (en) | 2008-03-04 | 2014-11-28 | Resmed Ltd | An interface including a foam cushioning element |
| NZ589634A (en) | 2008-06-04 | 2012-09-28 | Resmed Ltd | A mask to apply positive airway pressure (PAP) for the treatment of a sleep disorder that attaches to the face |
| US8905031B2 (en) | 2008-06-04 | 2014-12-09 | Resmed Limited | Patient interface systems |
| US20100037896A1 (en) * | 2008-08-18 | 2010-02-18 | General Electric Company | Automatic ventilator system and method |
| CN104771821B (en) | 2008-09-12 | 2018-10-16 | 瑞思迈有限公司 | The interface structure method and apparatus of foam-based |
| EP2213324B1 (en) | 2009-01-30 | 2016-07-27 | ResMed R&D Germany GmbH | Patient interface structure and method/tool for manufacturing same |
| CN101820559A (en) * | 2009-02-26 | 2010-09-01 | 鸿富锦精密工业（深圳）有限公司 | Speaker and wireless charging device with same |
| US20160228670A1 (en) * | 2013-09-11 | 2016-08-11 | Advanced Inhalation Therapies (Ait) Ltd. | System for nitric oxide inhalation |
| CN108131957A (en) * | 2018-01-18 | 2018-06-08 | 佛山市恒学科技服务有限公司 | A kind of foundry machinery pernicious gas collection device |
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| GB900866A (en) * | 1960-07-19 | 1962-07-11 | Biease Anaesthetic Equipment L | Improvements in respiration machines |
| FR1393311A (en) * | 1963-12-17 | 1965-03-26 | Blease Anaesthetic Equip Ltd | Ventilation machine for feeding a breathing mask |
| GB1328087A (en) * | 1969-09-15 | 1973-08-30 | Pye Ltd | Pneumatically controlled medical respirators |
| FR2323403A1 (en) * | 1975-09-15 | 1977-04-08 | Spirotech Ind Commerc | CLOSED-CIRCUIT RESPIRATORY SYSTEM |
| US4060077A (en) * | 1975-11-12 | 1977-11-29 | Diana W. Friedman | Respirator |
| FR2344278A1 (en) * | 1976-03-19 | 1977-10-14 | Air Liquide | RESPIRATOR |
| GB1592548A (en) * | 1977-09-30 | 1981-07-08 | Nat Res Dev | Medical ventilation apparatus |
| DE3105637C2 (en) * | 1981-02-17 | 1986-09-18 | Interspiro GmbH, 7529 Forst | Circulatory breathing apparatus |
| DE3202638A1 (en) * | 1982-01-28 | 1983-08-18 | Drägerwerk AG, 2400 Lübeck | RESPIRATORY DEVICE WITH BREATHING AIR CIRCUIT |
| DE3429345A1 (en) * | 1983-12-09 | 1985-06-13 | Drägerwerk AG, 2400 Lübeck | CIRCUIT BREATHING PROTECTOR FOR OVERPRESSURE OPERATION |
| US4793340A (en) * | 1985-09-18 | 1988-12-27 | Den Norske Stats Oljeselskap A.S. | Breathing system for divers |
| US4928685A (en) * | 1988-10-05 | 1990-05-29 | Cairns & Brother Inc. | Closed-circuit positive pressure breathing apparatus with pneumatically operated storage chamber |
-
1988
- 1988-07-09 DE DE3823382A patent/DE3823382C1/de not_active Expired - Fee Related
-
1989
- 1989-05-11 CA CA000599378A patent/CA1305391C/en not_active Expired - Fee Related
- 1989-06-13 ZA ZA894456A patent/ZA894456B/en unknown
- 1989-06-20 US US07/368,870 patent/US5038772A/en not_active Expired - Fee Related
- 1989-06-26 GB GB8914617A patent/GB2220362B/en not_active Expired - Fee Related
- 1989-07-05 JP JP1172086A patent/JPH0265871A/en active Granted
- 1989-07-07 AU AU37936/89A patent/AU625576B2/en not_active Ceased
Also Published As
| Publication number | Publication date |
|---|---|
| GB8914617D0 (en) | 1989-08-16 |
| JPH0265871A (en) | 1990-03-06 |
| US5038772A (en) | 1991-08-13 |
| AU3793689A (en) | 1990-01-11 |
| GB2220362B (en) | 1992-05-27 |
| DE3823382C1 (en) | 1990-01-11 |
| AU625576B2 (en) | 1992-07-16 |
| JPH0448464B2 (en) | 1992-08-06 |
| ZA894456B (en) | 1990-02-28 |
| GB2220362A (en) | 1990-01-10 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKLA | Lapsed |