EP2445591A1

EP2445591A1 - Artificial lung

Info

Publication number: EP2445591A1
Application number: EP10726109A
Authority: EP
Inventors: Florian Lux; Peter Kadow
Original assignee: MSA Auer GmbH
Current assignee: MSA Europe GmbH
Priority date: 2009-06-26
Filing date: 2010-06-25
Publication date: 2012-05-02
Also published as: DE102009030819A1; US20120115119A1; WO2010149764A1; CN102802734A

Abstract

The invention relates to an artificial lung for simulating the stress by a user when testing a breathing apparatus, particularly a compressed air breathing apparatus, comprising a housing, which surrounds a pulmonary space for the breathing air and has a connection for supplying the breathing air to the breathing apparatus. In order to be able to variably control the volume flow for generating a certain respiration curve, the housing (2) surrounding the pulmonary space for the breathing air is provided with an inlet (5) and with an outlet (6) for the breathing air, a fan (7, 8) is connected to the inlet and outlet (5, 6), respectively, for supplying and removing the breathing air, and a cover (13), which can be actuated by way of a drive (16) and encloses the pulmonary space (3), is disposed in the housing (2), which cover controls the volume flow of the breathing air between the inlet (5) for the breathing air and the connection (4) for the supply of the breathing air to the breathing apparatus, and/or between the connection (4) and the outlet (6) for removing the breathing air, so as to generate the breathing curve.

Description

"ARTIFICIAL LUNG"

description

The invention relates to an artificial lung for simulating the load by a user when testing a respiratory protective device, in particular compressed air respirator, from a housing enclosing a lung space for the respiratory air with a connection for supplying the respiratory air to the respiratory connection of the respiratory protective device.

As artificial lungs piston, bellows and membrane lungs are previously known.

The piston lung consists of a housing enclosing the lung space with a piston and a connection for supplying the respiratory air to the breathing connection of the respiratory protective device. The piston lung displaces air or sucks in air by changing the volume of the lung space. The relationship between spatial change and displaced or drawn in air volume is linear. ("Pressure guard" from Infotec AG)

The Balglunge comes closest to the human lung.

In this case, a bellows enclosing the lung space is compressed and relaxed again so that the lung space changes in volume and breathing air can be supplied to the respiratory connection of the respiratory protective device and can be discharged therefrom. ("Proficheck" by MSA Auer

GmbH; "Quaestor" by Draeger AG)

The membrane lung comprises a housing enclosing the lung space with a piston acting mechanically on a flexible membrane. By means of the movements of the membrane the volume of the lung space is changed. The Membranlunge is a combination of piston and bellows lung. ("Membranlunge" of the MSA Auer GmbH at all testing and licensing offices)

Disadvantageous in all three artificial lungs, which form a closed system with their respectively enclosed lung space, on the one hand is a large space for the lungs and on the other hand the linear relationship between the change in space and displaced or sucked volume flow.

The invention is therefore an object of the invention to provide an artificial lung of the generic type, which requires only a small space for the lung space and the volume flow to produce a specific breathing curve is variably controllable.

To solve this problem, the invention provides that the lung space for the breathing air comprehensive housing is additionally provided with an input and an outlet for the breathing air, that at the entrance and at the output ever a fan for the supply or for the removal of Respiratory air is connected and that in the housing actuatable via a drive, the lung space comprehensive aperture is arranged to generate a breathing curve, the volume flow of air between the inlet for the breathing air and the connection for supplying the breathing air to the breathing port of the respirator or between the Connection and the output to remove the breathing air controls.

The artificial lung forms a Gebläselunge. The principle of the blower lung is based on the generation of a volumetric flow of breathing air by means of at least one blower. In order to make the volume flow variable, the speed of the fan can be controlled and the volume flow be generated depending on the speed of the blower. The faster the blower rotates, the more breathing air is also moved. Technically, however, this solution is poorly executed, since the masses of the moving parts in the fan are permanently accelerated and the inertia is too high, so as to achieve a sinusoidal breathing curve with a certain period by a scheme.

With the Gebläselunge invention, which is an open system for the breathing air, in contrast, a constant volume flow is generated and arbitrarily limited by the adjustable or rotatable diaphragm. The two blowers run with a quasi-constant speed and the shutter is moved or rotated with a drive motor. For inhalation and exhalation to be carried out, one fan must inject breathing air into the lung space and the other fan must suck breathing air out of the lung space. The breathing curve is designed by regulating the angular velocity of the diaphragm. The maximum flow rate is determined by the power of the fans. Due to the variable control of the angular velocity of the diaphragm, each respiratory curve can be realized.

An advantage of the Gebläselunge invention is the small space for the lung room. The respiratory curve is not limited by the maximum lung volume of the artificial lung, but by controlling the volume flow via a variable resistance by the dependence of overlap areas between the respective tube connection and the aperture. Thus, the space for the artificial lung can be made relatively small. Another advantage is the ability to integrate the examination of the suction and the blow-off in the function of the artificial lung, since a constant volume flow can be generated. As a result, no further equipment is required for these tests.

The artificial lung or Gebläselunge invention consists of a diaphragm system, which can be designed as a rotatable diaphragm or as a linear slide, the diaphragm system reduces the air currents of the pressure and suction side fan or fan and directs the air flows to the outlet of the lung body of the Gebläselunge. The orifices of the respective fans or blowers can be controlled individually or jointly. A complete iris cycle simulates the respiratory rate. The aperture controls the breath flow. With complete opening of the aperture of one fan and simultaneous closing of the aperture of the other fan, the maximum breathing air flow prevails. The flow measurement is carried out by means of a flowmeter.

The aperture can either be rotated by 360 ° or oscillated by 180 ° from + 90 ° to - 90 ° and rotated from - 90 ° back to + 90 °. With the shutter designed as a shutter, an oscillating back and forth movement can be performed.

Further advantageous embodiments of the artificial lung according to the invention will become apparent from the dependent claims.

Advantageously, the housing is formed tubular, whereby a small space for the lung space is made possible, and the aperture is rotatably formed in the housing.

According to the invention, the inlets and outlets for the breathing air are furthermore arranged opposite to the tubular housing and the panel is designed as a hollow cylinder with an intermediate see the inlet and the outlet for the breathing air rotatable aperture formed.

In a second embodiment according to the invention, the inputs and outputs for the breathing air at the tubular

Housing arranged offset axially and the aperture is designed as a hollow cylinder with two axially staggered, rotatable between the input and the outlet for the breathing air apertures.

Finally, the two blowers can be provided with a common, speed-controllable drive motor.

In a third embodiment, two housings are arranged parallel next to each other and each provided with a rotatable aperture, each with a diaphragm opening and the two housing provided with the panels are connected to each other by a housing cover with a connection channel connecting the terminals.

In further fourth to sixth embodiments, the two apertures in the panel are Z-shaped connected to each other. It is also possible to arrange two Z-shaped apertures one above the other in the rotatable aperture. Also, the two Z-shaped apertures can be arranged offset by 90 ° to each other in the aperture, wherein the aperture is driven by 180 ° oscillating.

In yet another seventh embodiment, the diaphragm is formed as a disc with an aperture arranged at a radial distance from the horizontal axis of rotation, and the disc is rotatable about the horizontal axis within a slot formed in the housing. Finally, in the eighth embodiment, the diaphragm is designed as a slide which can be pushed back and forth in a slot in the housing and is provided with two aperture apertures arranged at a distance, which are aligned with the respective inlet or outlet of the housing in the respective end positions of the slide.

The invention will be explained in more detail below with reference to several embodiments of an artificial lung illustrated in the attached drawings. It shows:

1 is an axial longitudinal section through the first embodiment,

2 shows an axial longitudinal section through the second embodiment,

3 is an axial longitudinal section through the third embodiment,

4 shows an axial longitudinal section through the fourth embodiment,

5 shows an axial longitudinal section through the fifth embodiment,

6 is an axial longitudinal section through the sixth embodiment,

7 is an axial longitudinal section through the seventh embodiment,

8 shows the view of the diaphragm in Fig. 7,

Fig. 9 is an axial longitudinal section through the eighth embodiment and 10 shows the view of the diaphragm in FIG. 9.

The illustrated in Fig. 1 in an axial longitudinal section of the first embodiment of the artificial lung 1 is used to simulate the burden of a user when testing a respiratory protective device, in particular a Druckluftatemschutzgerätes. For the purpose of testing, the manufacturer sets target values which must be complied with in accordance with the compressed air respirator to be tested, so that the compressed air respirator, which is provided in particular with an automatic regulator, passes the test.

The artificial lung 1 comprises a tubular housing 2, which encloses a lung space 3 for the breathing air. The tubular housing 2 comprises on the upper side 19 a connection 4 for supplying the respiratory air located in the lung space 3 to the respiratory connection, not shown, in particular of the respiratory machine of a breathing apparatus also not shown. The housing 2 is additionally provided with an inlet 5 and with an outlet 6 for the breathing air. The input 5 and the output 6 are arranged opposite one another in the first embodiment according to FIG.

To the input 5 and to the output 6 of the housing 2 are connected via pipe connections 9, 10 blower 7 and 8 for supply and discharge of the breathing air. For this purpose, the blower 7 in the blowing direction (arrow 11) and the fan 8 in the suction direction (arrow 12) are connected. The inputs and outputs 5 and 6 of the housing 2 are connected to the blower 7 or 8 provided with their own drives via the pipe connections 9, 10.

The two fans 7, 8 are formed in a specific embodiment as a radial fan, are with a operated speed adjustable, which is kept constant by a Drivecontrol, and make a maximum flow of at least 600 l / min.

A diaphragm 13 enclosing the lung space 3 is rotatably arranged in the tubular housing 2 and is rotationally driven about the axis 16 by means of a shaft 15 adjoining the bottom 14 of the diaphragm 13 and a drive (not shown) about the axis 16 (double arrow 16). The diaphragm 13 is formed as a tubular hollow cylinder 17 with an aperture 18 which is arranged in the plane between the inlet 5 and the outlet 6 for the breathing air. The inner surface of the hollow cylinder 17 forms the lung space 3. The free, open upper side 19 of the hollow cylinder 17 forms the connection 4 for supplying the breathing air to the breathing connection of the respiratory protection device, not shown , The closed bottom 14 is provided with the shaft 15 leading to the drive, not shown. In a specific embodiment, the drive for the diaphragm 13 is designed as a stepper motor.

The speed of the two fans 7, 8 is set independently in the embodiment according to FIG. 1, so that the maximum volume flow of both fans 7, 8 is equal in magnitude. This is necessary because the two fans 7, 8 are used in different directions of action. The blower 7 blows air (arrow 11) for exhalation into the lung space 3, which via the connection 4 to

Breathing connection of the respirator is performed. The blower 8 operates in the suction direction (arrow 12) and sucks in the air via the port 4 of the breathing connection of the respiratory protective device through the outlet 6 for inhalation. To simulate a breathing cycle is a complete rotation of the aperture 13 by 360 °. In the zero position, the aperture 13 is aligned so that no overlap of the aperture 18 with the inputs and outputs 5, 6 of the housing 2 to the fans 7, 8 is present and thus also at the terminal 4 no volume flow is present. By turning the diaphragm 13 by means of the drive (double arrow 16), the diaphragm opening 18 is covered with the inlet 5 of the housing 2 and with the pipe connection 9 of the blast-side fan 7. The volume flow increases from the angular position 0 ° of the diaphragm 13 up to the angular position 90 ° of the diaphragm 13 continuously. At the angular position 90 ° of the diaphragm 13, the overlap of the input 5 with the diaphragm opening 18 is maximum and the volume flow of the respiratory air is maximum at port 4 to the respirator. From the angular position 90 ° to the angular position 180 °, the overlap and thus the volume flow again decrease continuously, until in the angular position 180 ° both values have dropped to zero and no volume flow is available. The complete phase of exhalation runs at the angular position of the diaphragm 13 from 0 ° to 180 °. The inhalation phase runs between the angular position of 180 ° and 360 ° or 0 °. By further rotation of the diaphragm 13, there is an overlap of the aperture opening 18 with the output 6 of the housing 2 and with the

Pipe connection of the suction-side blower 8. The suctioning volume flow increases continuously from the angular position 180 ° of the diaphragm 13 to the angular position 270 ° of the diaphragm 13. At the angular position of 270 ° of the diaphragm 13, the coverage of the output 6 with the aperture 18 is maximum and the extracted volume flow of the inhaled air at the terminal 4 of the respirator maximum, and then again drop to the angular position 360 ° or 0 ° continuously. The breathing cycle is performed by a complete rotation of the aperture 13 by 360 °. The respiratory rate is determined by the rotational speed of the diaphragm 13. The tidal volume is determined by integration of the resulting volume flow.

In the illustrated in Fig. 2 the second embodiment of the artificial lung 1, in contrast to the first embodiment of FIG. 1, the inputs and outputs 5, 6 for the breathing air on the tubular housing 2 ¹¹ arranged axially offset, the input 5 with the pressure side Fan 7 is arranged below the outlet 6 with the suction-side fan 8. The aperture 13 is arranged as a hollow cylinder 17 with two axially offset, rotatable in the plane of the input 5 and in the plane of the output 6 for the breathing air aperture openings 18 ¹¹ . The function of this second embodiment corresponds to that of the first embodiment, but the exhaled air only through the input 5 to the terminal 4 and the inhaled air only from the terminal 4 through the output 6 out.

The illustrated in Fig. 3 third embodiment of the artificial lung 1 comprises two juxtaposed housing 2 ¹¹¹ , each with a diaphragm 13 ^111th In the housing 13 ¹¹¹ shown on the left in FIG. 3, the inlet 5 is arranged, which is connected via the pipe connection 9 to the pressure-side blower 7. In the housing 2 ¹¹¹ shown on the right in FIG. 3, the outlet 6 is arranged, which is connected via the pipe connection 10 to the suction-side fan 8. The each provided with a lung 3 apertures 13 ¹¹¹ have the respective apertures 18 ¹¹¹ , of which in the illustrated angular position, the left aperture 18 ^{111 is} aligned with the associated input 5 to generate the maximum volume flow of air, whereas the other aperture 18 ¹¹¹ of right aperture 13 ¹¹¹ illustrated is situated opposite the wall of the housing 2 ^111, and is thus closed. Both housings 2 ¹¹¹ are connected on their upper sides 19 by a connecting channel 22, which is formed twice in a housing cover 21 and leads to connection 4 ¹¹¹ . With synchronous rotation of both drives according to the double arrows 16, a breathing cycle is simulated in a similar manner to the first embodiment of FIG. 1 described above.

In the illustrated in Fig. 4 the fourth embodiment of the artificial lung 1 are in a similar manner as in the second embodiment shown in Fig. 2 on the left side of the housing 2 ^IV, the inputs and outputs 5, 6 via the pipe connections 9, 10th connected to the blowers 7, 8. In contrast to the first to third embodiments, the top 19 are closed and the terminal 4 ^{IV arranged} on the inputs and outputs 5, 6 opposite side of the housing 2 ^IV and formed as a slot. The arranged in the vertical axis 20 lung 3 is provided at the lower end in the plane of the entrance 5 with a lower aperture 18 ^IV and at the upper end in the plane of the output 6 with an upper aperture 18 ^IV , which during the rotation of the aperture 13th ^IV each oscillating with the terminal 4 ^IV for supplying the breathing air to the respiratory connection in connection.

The illustrated in Fig. 5 fifth embodiment corresponds in terms of the design of the housing 2 ^{V of} the embodiment shown in Fig. 4. In the rotatable in the housing 13 ^V aperture 13 ^V are aligned with the input 5 and the terminal 4 ^V and one with the output 6 and the terminal 4 ^V in the respective rotational position, Z-shaped aperture 18 ^V formed by 180 ° offset from one another. The sixth embodiment shown in FIG. 6 corresponds with regard to the embodiment of the housing 2 ^{VI to} the embodiments shown in FIGS. 4 and 5 and with regard to the embodiment of the diaphragm 13 ^{VI of} the fifth embodiment shown in FIG. In contrast to this embodiment, the aligned with the input 5 and the output 6 in the respective rotational position Z-shaped aperture 18 ^VI are arranged offset only 90 ° to each other. In this sixth embodiment, a breathing cycle is performed by oscillating rotational movement of the diaphragm 13 ^VI by 180 °.

In the seventh embodiment shown in FIGS. 7 and 8, the housing 2 ^VI1 essentially corresponds to the housings 2 ^IV , 2 ^V and 2 ^{VI of} the fourth to sixth embodiments according to FIGS. 4 to 6. In contrast to that about the vertical axis 20 of rotatable blades 13 ^IV, 13 ^V and 13 ^VI is the aperture 13 ^VI1 as by means of a Wells 23 about a horizontal axis 24 in a slot 25 of the housing 2 ^VI1 rotatable disc 26 with a arranged in the radial distance from the axis 24 of aperture 18 ^VI1 formed by the rotation of the disc 26 cyclically connects the inputs and outputs 5, 6 of the housing 2 ^VI1 with the terminal 4 ^VI1 .

In the eighth embodiment of the artificial lung 1 shown in Figs. 9 and 10, the housing 2 ^{VI11 is formed} as in the fourth to sixth embodiments and with a slit 27 as in the seventh embodiment. In the slot 27 as a diaphragm 13 ^VI11 a slide 28 by means of a pin 29 acting on a reciprocating drive (arrow 30) slidably. The slide has two superimposed aperture openings 18 ^VI11 , whose distance from each other is such that in the lower position of the slider 28 according to Fig. 9 of standing with the pressure-side blower 7 in connection input 5 with the lower aperture 18 ^VI11 and in the upper position of the slider 28 of the suction-side fan 8 in connection with the output port 6 ^VI11 in conjunction.

LIST OF REFERENCE NUMBERS

01 artificial lung

02 housing

03 pulmonary space

04 connection

05 entrance

06 output

07 blower

08 blower

09 Pipe connection

10 pipe connection

11 arrow

12 arrow

13 aperture

14 floor

15 wave

16 double-headed arrow

17 hollow cylinders

18 aperture

19 top

20 axis

21 housing cover

22 connecting channel

23 wave

24 axis

25 slot

26 disc

27 slot

28 slides

29 cones

30 arrow

Claims

claims

1. Artificial lung for simulating the load by a user when testing a respiratory protective device, in particular Druckluftatemschutzgerät, from a lung space for breathing air enclosing housing with a connection for supplying the breathing air to the breathing port of the respirator, characterized in that the lung space (3 ) for the breathing air comprehensive housing (2) is additionally provided with an input (5) and with an outlet (6) for the breathing air that at the input (5) and the output (6) each have a fan (7, 8 ) is connected to the supply and removal of the breathing air and that in the housing (2) via a drive (16) operable, the lung space (3) comprehensive, with at least one aperture (18) provided aperture (13) is arranged for generating a respiratory curve, the volumetric flow of the respiratory air between the inlet (5) for the respiratory air and the connection (4) for the supply of respiratory air to the respiratory protective device or between the connection (4) and the outlet (6) controls the removal of the breathing air.

2. Artificial lungs according to claim 1, characterized in that the housing (2) tubular and the aperture (13) in the housing (2) is rotatable.

3. Artificial lungs according to claim 2, characterized in that the inputs and outputs (5, 6) for the breathing air on the tubular housing (2) are arranged opposite and the diaphragm (13) as a hollow cylinder (17) with a between the input (5) and the outlet (6) for the breathing air rotatable aperture (18) is formed.

4. Artificial lungs according to claim 2, characterized in that the inputs and outputs (5, 6) for the breathing air on the tubular housing (2 ¹¹ ) arranged axially offset and the aperture (13 ¹¹ ) as a hollow cylinder (17) with two axially staggered, between the input (5) and the output (6) for the breathing air rotatable aperture openings (18 ¹¹ ) is formed.

5. Artificial lung according to one of claims 1 to 4, characterized in that the two blowers (7, 8) with a common, speed-controllable drive (arrow 16) are provided.

6. Artificial lungs according to one of claims 1 to 5, characterized in that two housings (2 ¹¹¹ ) arranged in parallel side by side and each with a rotatable aperture (13 ¹¹¹ ), each with an aperture (18 ¹¹¹ ) are provided and that the two with The housing (2 ¹¹¹ ) is connected to the covers (13 ¹¹¹ ) by a housing cover (21) with a connecting channel (22) connecting the connections (4).

7. Artificial lung according to one of claims 1 to 5, characterized in that the two apertures

(18 ^IV ) in the panel (13 ^IV ) are Z-shaped connected to each other.

8. Artificial lungs according to claim 7, characterized marked, that two Z-shaped aperture openings (18 ^V ) are arranged one above the other in the rotatable aperture (13 ^V ).

9. artificial lung according to claim 8, characterized in that the two Z-shaped aperture openings (18 ^VI ) offset by 90 ° to each other in the diaphragm (13 ^VI ) are arranged.

10. Artificial lung according to claim 9, characterized in that the diaphragm (13 ^VI ) is driven to oscillate by 180 °.

11. Artificial lungs according to claim 1, characterized in that the diaphragm (13 ^VI1 ) as a disc (26) with a ^radially spaced from the horizontal axis (24) arranged aperture (18 ^VI1 ) is formed and that the disc (26) to the horizontal axis (24) is rotatable within a slot (25) formed in the housing (2 ^VI1 ).

12. Artificial lung according to claim 1, characterized in that the diaphragm (13 ^VI11 ) as in a slot

(27) in the housing (2 ^VI11 ) back and forth slide

(28) is formed and provided with two spaced-apart aperture (18 ^VI11 ), which are ^aligned in the respective end positions of the slide (28) with the respective input or output (5 or 6) of the housing (2 ^VI11 ).

13. Use of a provided with at least one aperture, rotating or oscillating diaphragm for generating a volume flow of breathing air by means of at least one blower for the purpose of training an artificial lung for the examination of Druckluftatemschutzgeräten.