阅读说明：本技术 包括用于容纳来自医疗设备的气体的过滤单元的容纳装置和方法 (Containing device and method comprising a filter unit for containing gas from a medical device ) 是由 H·U·许勒 R·黑施 R·施密德 于 2021-06-15 设计创作，主要内容包括：本发明涉及一种容纳装置(100)和用于容纳来自医疗设备(1)的气体的方法。容纳装置包括输送线路(6)、导出线路(8)、具有过滤器的过滤单元(4)和至少一个缓冲存储器。输送线路(6)建立医疗设备(1)和过滤单元(4)之间的流体连接。导出线路(8)建立过滤单元(4)和流体容纳部(7)之间的流体连接。气体被医疗设备(1)喷出,并且通过输送线路(6)引导至过滤单元(4),并且从那里通过导出线路(8)引导至流体容纳部(7)。过滤器从引导通过过滤单元(4)的气体过滤出至少一种气体成分。该或每个缓冲存储器能够临时容纳并且又输出气体。(The invention relates to a containing device (100) and a method for containing gas from a medical apparatus (1). The receiving device comprises a feed line (6), a discharge line (8), a filter unit (4) with a filter and at least one buffer store. The delivery line (6) establishes a fluid connection between the medical device (1) and the filter unit (4). The outlet line (8) establishes a fluid connection between the filter unit (4) and the fluid receptacle (7). The gas is emitted by the medical device (1) and is guided via a feed line (6) to the filter unit (4) and from there via a discharge line (8) to the fluid reservoir (7). The filter filters out at least one gas component from the gas guided through the filter unit (4). The or each buffer store can temporarily hold and output gas again.)

1. Receiving device (100) for receiving gas from a medical apparatus (1), in particular an anesthesia apparatus, wherein the receiving device (100) comprises:

-a conveying line (6, 16)

-derived lines (8, 32)

-a filter unit (4) having at least one filter (11, 20, 11.1, 20.1, 11.2, 20.2), and

-at least one buffer memory (19, 23, 36, 70),

wherein the or each filter (11, 20, 11.1, 20.1, 11.2, 20.2) of the filter unit (4) is designed to filter out at least one predetermined gas component, in particular at least one anesthetic agent, from the gas guided through the filter (11, 20, 11.1, 20.1, 11.2, 20.2),

wherein the delivery line (6, 16) is designed to establish, at least temporarily, a fluid connection with the medical device (1),

wherein the outlet line (8, 32) is designed to establish a fluid connection with the fluid receptacle (7) or the environment at least temporarily,

wherein a fluid connection (14, 30) is or can be established between the feed line (6, 16) and the filter unit (4) and between the discharge line (8, 32) and the filter unit (4), respectively,

wherein the or each buffer memory (19, 23, 36, 70)

-is in fluid connection (22.1) with the delivery lines (6, 16), respectively, and/or is in fluid connection (22.2) with the lead-out lines (8, 32), respectively, and

-is designed to temporarily store the gas from the supply line (6, 16) and/or the discharge line (8, 32) and subsequently to again output it to the supply line (6, 16) and/or the discharge line (8, 32), and

wherein the receiving device (100) is designed for

-conducting gas from the medical device (1) to the filter unit (4) through the delivery line (6, 16),

-leading through the filter unit (4) and here at least partly through the or a filter (11, 20, 11.1, 20.1, 11.2, 20.2), and

-leading to the fluid container (7) or the environment through the lead-out line (8, 32).

2. The containing device (100) according to claim 1, characterised in that the or a buffer store (23) is additionally in fluid connection (24) with the environment and is designed for outputting gas into the environment.

3. The containing device (100) according to any one of the preceding claims, characterised in that the filter unit (4) additionally comprises a filter housing (13) which is in fluid connection (14, 30) with the delivery line (6, 16) and in fluid connection (26, 35) with the lead-out line (8, 32),

wherein the or a filter (11, 20, 11.1, 20.1, 11.2, 20.2) is or can be mounted in a filter receptacle (13),

wherein the filter unit (4) is designed in such a way that, after the filter (11, 20, 11.1, 20.1, 11.2, 20.2) has been installed in the filter receptacle (13), a gap (19) is formed between the filter (11, 20, 11.1, 20.1, 11.2, 20.2) and the filter receptacle (13), and

wherein the gap (19)

-is in fluid connection (25) with the transfer line (6, 16), and is in fluid connection (34) with the lead-out line (8, 32), and

-providing or belonging to the or a buffer memory (19, 23, 36, 70).

4. The containing device (100) according to any one of the preceding claims, characterised in that the or a buffer storage (19, 23, 36, 70) comprises a housing (23) which is in fluid connection (26) with the filter unit (4) and which provides an inner space for containing gas.

5. The containing device (100) according to any one of the preceding claims, characterised in that the or at least one buffer store (23) is arranged downstream of the filter unit (4) as seen in the flow direction from the conveying line (6, 16) to the lead-out line (8, 32), or the filter unit (4) is arranged downstream of the or at least one buffer store (70).

6. The containing device (100) according to any one of the preceding claims, wherein the filtering unit (4) additionally comprises a filter housing (13) which comprises a filter housing

-enclosing an inner space, and

-is in fluid connection (14, 30) with the delivery line (6, 16) and is in fluid connection (26, 35) with the lead-out line (8, 32),

wherein the movably arranged plate (31) divides the interior space of the filter receptacle (13), preferably in a fluid-tight manner, into a filter hollow space (37) and a buffer reservoir hollow space (36),

wherein the or a filter (11, 20, 11.1, 20.1, 11.2, 20.2) is or can be mounted in a filter receptacle (13),

wherein the filter hollow space (37) is designed to accommodate a filter (11, 20, 11.1, 20.1, 11.2, 20.2) and

wherein the buffer memory hollow space (36)

-belong to or construct the or one buffer memory (19, 23, 36, 70), and

-is in fluid connection with the delivery line (6, 16) and with the lead-out line (8, 32), at least when no filter (11, 20, 11.1, 20.1, 11.2, 20.2) is installed in the filter housing (13).

7. The containing device (100) according to claim 6, wherein the plate (31) is movable back and forth relative to the filter holder (13) between a parking position and a buffer storage position, wherein the plate (31)

-when no filter (11, 20, 11.1, 20.1, 11.2, 20.2) is installed, is in a buffer memory location, and

-in the parking position when the filter (11, 20, 11.1, 20.1, 11.2, 20.2) is installed,

wherein the conveying line (6, 16) has at least one outlet opening (14, 14.1), wherein the discharge line (8, 32) has at least one inlet opening (35, 35.1),

wherein when said plate (31) is in a buffer memory position,

-the or one outlet opening (14.1) connects the transfer line (6, 16) with the buffer reservoir void space (30), and

-the or an inlet opening (35.1) connects the lead-out line (8, 32) with the buffer reservoir void space (30), and

wherein when the plate (31) is in the parking position,

-the or one outlet opening (14) connects the transfer line (6, 16) with the filter hollow space (37), and

-the or one inlet opening (35) connects the lead-out line (8, 32) with the filter hollow space (37).

8. The containment device (100) according to claim 6 or 7, characterised in that the containment device (100) comprises a slider (48) which comprises a slide (48)

-is arranged inside the filter housing (13),

-is movable to and fro between a buffer storage position and a parking position relative to the filter receptacle (13), and

preferably mechanically connected to the plate (31),

the feed line (6, 16) has a filter outlet opening (14) and a buffer storage outlet opening (14.1), and the discharge line (8, 32) has a filter inlet opening (35) and a buffer storage inlet opening (35.1),

wherein when the slider (48) is in a buffer memory position

-the buffer store outlet opening (14.1) connects the transfer line (6, 16) with the buffer store hollow space (30),

-said buffer memory inlet opening (35.1) connecting the lead-out line (8, 32) with the buffer memory empty space (30), and

-the slider (48) closes off the filter outlet opening (14) and the filter inlet opening (35), and

wherein when the slide (48) is in the park position,

-the filter outlet opening (14) connects the transfer line (6, 16) with the filter hollow space (37),

-the filter inlet opening (35) connects the lead-out line (8, 32) with the filter hollow space (37), and

-the slider (48) closes off the buffer storage outlet opening (14.1) and the buffer storage inlet opening (35.1).

9. The containing device (100) according to any one of the preceding claims, wherein the filter unit (4) additionally comprises a filter housing (13) and a filter sensor (47), wherein the filter unit (4)

-enclosing an inner space, and

-is in fluid connection (14, 30) with the delivery line (6, 16) and is in fluid connection (26, 35) with the lead-out line (8, 32),

wherein the or a filter (11, 20, 11.1, 20.1, 11.2, 20.2) is or can be mounted in a filter receptacle (13), and wherein the filter sensor (47) is designed to automatically determine whether the filter (11, 20, 11.1, 20.1, 11.2, 20.2) is mounted in the filter receptacle (13).

10. The receiving device (100) according to one of the preceding claims, wherein the volume of the or at least one buffer store (70) is variable, in particular the or at least one buffer store (70) is made of an elastic material, wherein a gas is fed into the buffer store (70) to expand the buffer store (70), and wherein the expanded buffer store (70) contributes to the contraction and thereby in turn outputs the received gas.

11. The containment device (100) according to any one of the preceding claims, characterised in that the containment device (100) comprises at least one overpressure valve (50), wherein the overpressure valve (50) opens if the difference between the pressure in the delivery line (6, 16) and the pressure around the delivery line (6, 16) is above a preset overpressure limit.

12. The receiving device (100) according to claim 11, characterised in that the overpressure valve (50) is connected to the outlet line (8, 32) by means of a fluid guide unit (64), wherein a fluid connection between the overpressure valve (50) and the fluid guide unit (64) is established when the overpressure valve (50) is opened.

13. The containing device (100) according to claim 11 or 12, characterised in that the containing device (100) comprises a concentration sensor (15) which is designed for determining the concentration of at least one gas component at a measuring location downstream of the filter (11, 20, 11.1, 20.1, 11.2, 20.2), wherein the containing device (100) is designed for, if at all, determining the concentration of at least one gas component at a measuring location downstream of the filter (11, 20, 11.1, 20.1, 11.2, 20.2)

-the overpressure valve (50) opens, or

-the concentration sensor (15) detects a concentration above a preset concentration limit,

a message is generated.

14. The containing device (100) according to any one of the preceding claims, characterised in that the containing device (100) comprises a negative pressure valve (80), wherein the negative pressure valve (80) opens if the difference between the pressure in the conveying line (6, 16) or inside the filter unit (4) and the surrounding pressure is below a preset negative pressure limit.

15. The containing device (100) according to claim 14, characterised in that at least one opening (21) is embedded in the wall (13) of the filter unit (4), wherein the interior of the filter containing part (13) is in fluid connection with the environment through the or at least one opening (21) in the wall (13) of the filter unit (4) when the negative pressure valve (80) is open, and wherein the closed negative pressure valve (80) closes the fluid connection between the interior of the filter unit (4) and the environment.

16. The containing device (100) according to any one of the preceding claims, characterised in that the filter unit (4) additionally comprises a filter receptacle (13) which is in fluid connection (14, 30) with the feed line (6, 16) and in fluid connection (26, 35) with the discharge line (8, 32), wherein the or one filter (11, 20, 11.1, 20.1, 11.2, 20.2) is fitted into the filter receptacle (13) and can be removed again from the filter receptacle (13).

17. The containing device (100) according to any one of the preceding claims, wherein the filter unit (4) comprises a first filter (11.1) and a second filter (11.2), wherein the containing device (100) comprises a switching device (72) designed to selectively fluidly connect the first filter (11.1) or the second filter (11.2) with the delivery line (6, 16) and the lead-out line (8, 32).

18. The receiving device (100) according to claim 17, characterised in that the first filter (11.1) is designed for filtering out a predetermined first gas component and the second filter (11.2) is designed for filtering out a predetermined second gas component which is different from the first gas component.

19. The containing device (100) according to any one of the preceding claims, characterised in that the filter unit (4) is designed for,

-guiding the gas through a filter (11, 20, 11.1, 20.1, 11.2, 20.2) in a path from the transfer line (6, 16) to the lead-out line (8, 32), and

-preventing gas from bypassing the filter (11, 20, 11.1, 20.1, 11.2, 20.2).

20. The receiving device (100) according to one of the preceding claims, wherein the wall (38) divides the filter (11, 20, 11.1, 20.1, 11.2, 20.2) into a first region (Ab) and a second region (Au), wherein the first region (Au) is fluidically connected to the supply line (6, 16) and the second region (Ab) is fluidically connected to the discharge line (8, 32), and wherein the filter unit (4) is designed such that gas flows from the supply line (6, 16) through the first region (Au) and subsequently through the second region (Ab) into the discharge line (8, 32).

21. The containing device (100) according to any one of the preceding claims, wherein the filter unit (4) comprises a data memory (92) and the containing device (100) comprises a reading device for reading the data memory (92), wherein at least one of the following information is stored in the data memory (92):

-a clear indication of the filter unit (4),

-information whether the filtering unit (4) is re-used or already used,

-information of which gas components the filter unit (4) can and/or cannot be used for,

-information about a point in time at which the filtering unit (4) starts to be used for filtering.

22. The containing device (100) according to any one of the preceding claims, wherein the containing device (100) comprises a composition-quantity determiner (93) designed to receive

-a signal for a time-varying volume flow of the fluid through the delivery line (6) towards the filter unit (4), and

-a signal for a time-varying concentration of the or at least one gas component in the delivery line (6), or

-a signal for how many quantities of gas components are fed into the delivery line (6),

the amount of the gas component contained hitherto in the filter unit (4) is approximately determined from these two signals,

comparing the number received so far with a predetermined maximum number that can be received by the filter unit (4), and

generating a message according to the comparison result.

23. The containing device (100) according to claim 22, characterised in that the filter unit (4) comprises a data memory (92) in which information about the maximum number that can be contained by the or at least one gas component filter (11, 20, 11.1, 20.1, 11.2, 20.2) is stored, wherein the component-quantity determiner (93) is designed to use the information stored in the data memory (92) as the preset maximum number when comparing.

24. The containing device (100) according to any one of the preceding claims, characterised in that the containing device (100) comprises a negative pressure generator, in particular a suction pump (10), wherein the lead-out line (8) is fluidly connected with the negative pressure generator (10), and wherein the negative pressure generator (10) is designed for generating a negative pressure in the lead-out line (8).

25. Use of a containing device (100) according to any one of the preceding claims for containing gas from a medical apparatus (1), in particular for containing at least one anesthetic agent from an anesthetic apparatus.

26. A medical device comprising

-a medical apparatus (1), in particular an anaesthetic apparatus, and

-at least one containing device (100) according to any one of claims 1 to 24,

wherein the respective delivery line (6, 16) of the or each receiving device (100) is at least temporarily in fluid connection with the medical apparatus (1).

27. The medical apparatus according to claim 26, characterized in that it comprises a further medical device (1.1), wherein a fluid connection (6.1, 6.2) between the medical device (1) and the delivery line (6) or between the further medical device (1.1) and the delivery line (6) of the same containing device (100) can be established selectively or simultaneously.

28. The medical device according to claim 26 or 27, wherein the receiving means (100) is arranged inside the medical apparatus (1).

29. A medical system comprising

-a medical device according to any of claims 26 to 28, and

a fluid receptacle (7), preferably a stationary fluid receptacle (7),

wherein the outlet line (8, 32) of the receiving device (100) is at least temporarily in fluid connection with the fluid receptacle (7).

30. Medical system according to claim 29, characterized in that it comprises a further fluid receptacle (7.1), preferably a further fixed fluid receptacle (7.1), wherein a fluid connection (7.1, 7.2) between the fluid receptacle (7) and the outlet line (8, 32) or between the further fluid receptacle (7.1) and the outlet line (8, 32) can be established selectively or simultaneously.

31. Method for receiving gas from a medical device (1), in particular from an anesthesia device, wherein the method is carried out using a receiving device (100), wherein the receiving device (100) comprises:

-a conveying line (6, 16),

-a derived line (8, 32),

-a filter unit (4) having at least one filter (11, 20, 11.1, 20.1, 11.2, 20.2), and

-at least one buffer memory (19, 23, 36, 70), and

wherein the method comprises the steps of:

-establishing a fluid connection between the medical device (1) and the delivery line (6, 16),

-establishing a fluid connection between the lead-out line (8, 32) and the fluid container (7) or the environment,

-the gas escapes from the medical device (1), in particular is ejected and/or sucked away,

-the containment device (100) conducts the escaping gas to the fluid containment (7) or to the environment through the delivery line (6, 16), the filtration unit (4) and the lead-out line (8, 32),

-wherein the whole gas or at least a part of the gas, when being led, is led through the filter unit (4), the or a filter (11, 20, 11.1, 20.1, 11.2, 20.2), and

-the filter (11, 20, 11.1, 20.1, 11.2, 20.2) filters out at least one predetermined gas component, in particular an anesthetic agent, from the gas guided through the filter (11, 20, 11.1, 20.1, 11.2, 20.2),

wherein if more gas escapes from the medical device (1) than is guided into the fluid receptacle (7) or into the environment, the gas is guided from the supply line (6, 16) and/or the discharge line (8, 32) into the or at least one buffer store (19, 23, 36, 70), and the buffer store (19, 23, 36, 70) temporarily stores the gas, and

wherein if a small amount of gas escapes, the temporarily stored gas is conducted from the or at least one buffer store (19, 23, 36, 70) to the discharge line (8, 32) and/or the delivery line (6, 16).

32. Method according to claim 31, characterized in that the filter unit (4) additionally comprises a filter housing (13) which comprises

-enclosing an inner space, and

-at least temporarily in fluid connection (14, 30) with the transfer line (6, 16) and at least temporarily in fluid connection (26, 35) with the lead-out line (8, 32),

wherein the movably arranged plate (31) divides the interior space of the filter receptacle (13) into a filter hollow space (37) and a buffer reservoir hollow space (36), preferably in a fluid-tight manner,

wherein the or a filter (11, 20, 11.1, 20.1, 11.2, 20.2) is mounted in a filter hollow space (37),

wherein the filter (11, 20, 11.1, 20.1, 11.2, 20.2) is removed from the filter receptacle (13) at least once and

wherein the buffer reservoir hollow space (36) is in fluid connection with the feed line (6, 16) and with the discharge line (8, 32) at least in the case of removal of the filter (11, 20, 11.1, 20.1, 11.2, 20.2).

Technical Field

The invention relates to a receiving device which can receive gas from a medical apparatus, in particular from an anesthesia apparatus. The invention also relates to a method for receiving gas from a medical device by means of such a receiving device.

Background

In the case of the application of the receiving device and the method, the medical device is an anesthesia device which is connected to the patient and breathes and anesthetizes the patient by means of a breathing cycle. The anesthesia apparatus is supplied with the required gas and itself supplies the patient with a gas mixture, wherein the gas mixture contains oxygen and is enriched with at least one anesthetic agent, so that the patient is completely or at least locally anesthetized. Typically, anesthesia apparatuses implement several respiratory strokes, wherein a specific amount of gas is transported to the patient with each respiratory stroke. In one embodiment, the air exhaled by the patient enters the medical device again, and the medical device filters carbon dioxide out of the exhaled air.

In US 2001/0025640 a1, an anesthetic filter (anesthetic gas filter 2) is described, having a housing (enclosure 4), an inlet (inlet 6) and an outlet (outlet 8). A separating wall (partition 18) with holes 20 divides the housing 4 into a first chamber (first absorption volume 10) for a first filter (first absorbent 12) and a second chamber (second absorption volume 14) for a second filter (second absorbent 16). If the first filter 12 is removed from the first chamber 10, a first line (first shunt line 24) connects the inlet 6 with the aperture 20 and thus the second chamber 18. If the second filter 16 is removed from the second chamber 14, a second (second shunt line 26) connects the bore 20 and thus the second chamber 14 with the outlet 8. Two anesthetic indicators 22 and 22B show when the first filter 12 or the second filter 16 must be replaced.

Generally, in artificial respiration, more gas is delivered to the respiratory cycle than is withdrawn again. In this case, the remaining gas accumulates in the breathing cycle. The remaining gas must be removed from the breathing cycle. The remaining gas typically contains an anesthetic. Obviously, the patient should not be compromised. In particular, artificial respiration and anesthesia must be maintained.

Disclosure of Invention

The object of the present invention is to provide a receiving device and a method for receiving gas from a medical device, which device and method perform their function better than known receiving devices and methods.

This object is achieved by a receiving device having the features of claim 1 and by a method having the features of claim 31. Advantageous embodiments are specified in the dependent claims. If it is significant, an advantageous embodiment of the receiving device according to the invention is also an advantage of the method according to the invention, and vice versa.

The receiving device according to the invention comprises a conveying line and a discharge line. The delivery line can be connected, preferably releasably connected, to the medical device (from which the gas to be contained escapes), and is designed to establish at least one fluid connection between the medical device and the containing apparatus after the connection has been established. The outlet line can be connected, preferably releasably connected, to the fluid receptacle and is designed to establish at least one fluid connection between the fluid receptacle and the receiving device after the connection has been established. The fluid receptacle may be a fixed or moving fluid receptacle and act as a recess for the fluid. The fluid receptacle may also be a spatially separated suction within or outside the housing. Alternatively, the derived line leads into the environment.

The receiving device according to the invention furthermore comprises a filter unit. The filter unit comprises at least one filter.

The or each filter of the filter unit is designed to filter out at least one gas component from the gas guided through the filter. The design and/or characteristics of the filter and/or its material determine which gas component or components the filter filters out. Preferably, the filter is capable of filtering out at least one anaesthetic agent from the gas, i.e. the or at least one gaseous component is an anaesthetic agent.

The receiving device is designed to perform the following functions: gas ejected or sucked from the medical device or otherwise escaping from the device is directed through the delivery line to and through a filtration unit, wherein the filtration unit comprises a filter. At least a part of the gas, preferably all of the gas, is led through the filter, and the filter at least partially, preferably completely filters out the or at least one gas component from the gas, unless the filter is consumed or defective. The gas flowing through the filter unit and from which the at least one gas component is filtered is conducted via a discharge line into the fluid container or into the environment.

The method according to the invention is carried out using such a receiving device and comprises the following steps:

-establishing at least one fluid connection between the medical device and the delivery line;

-establishing at least one further fluid connection between the lead-out line and the fluid receptacle. Alternatively, the derived line is directed into the environment;

-gas escaping from the medical device. The medical device in particular ejects and/or sucks gas from the medical device. The escaped gas enters a conveying line;

the containment device guides the escaping gas through the delivery line, the filter unit and the outlet line to the fluid containment.

During the gas is guided through the filter unit, at least a part of the gas (preferably continuously or at least temporarily the entire gas) flows through the filter of the filter unit;

the filter filters out the or at least one predetermined gas component, in particular at least one anesthetic agent, from the gas flowing through the filter. The gas thus enters the lead-out line, completely or at least partially filtering the or at least one gas component from the gas.

The receiving device according to the invention furthermore comprises at least one buffer store, wherein the or each buffer store is in each case at least temporarily fluidically connected to the supply line, to the discharge line, or at least temporarily is fluidically connected not only to the supply line but also to the discharge line. Thus, gas escaping from the medical device may enter the or a buffer reservoir and escape from the buffer reservoir again and subsequently into the lead-out line. The method according to the invention is implemented using at least one such buffer memory.

The receiving device according to the invention and the method according to the invention reduce, on the one hand, the risk of gases with undesired gas components escaping into the surroundings of the medical device. The receiving device according to the invention and the method according to the invention in particular reduce the risk that anesthetic agent escapes into the ambient air and that the escaping anesthetic agent endangers the health of persons who are located near the medical apparatus and/or near the patient who breathes artificially, in particular persons who work in a hospital. This effect is achieved in particular in that the receiving device according to the invention and the method according to the invention guide the air escaping or escaping from the medical device into the fluid receiving space. The escaping of the ejected gas and its entry into the environment of the medical device is thereby completely or at least to a certain extent prevented.

On the other hand, the invention reduces the risk of escaping or escaped gases entering the supply system or the surrounding environment, for example in an external area outside the hospital.

In the application of the invention, the fluid receptacle is a stationary fluid receptacle and in particular belongs to a stationary infrastructure of a building. In this application, the receiving device according to the invention and the method according to the invention reduce the risk in many cases that gas with an undesired gas component enters a stationary infrastructure system, in particular an infrastructure system in a hospital, via a fluid receiving section, which is connected to the stationary infrastructure system. The infrastructure system may in turn output gas with an undesired gas composition to the medical device, which is often undesired, or eject the gas into the environment, which may lead to environmental pollution. The undesired effects are prevented in particular by the filter unit having the filter. A filter is understood below as a component of a filter unit, which filter is able to filter out the or at least one predetermined gas component from the gas during the gas is guided through the filter.

It is also possible for the fluid receptacle to guide the contained gas through a discharge line to the vicinity of the waste gas installation, and for the waste gas installation to suck in gas from a closed or also partially or completely open space and to contain the gas. In this application, the outlet line does not have to be connected to a fixed fluid receptacle. In this application, the invention also prevents the entry of undesired gas components of the gas into the environment.

According to the invention, the receiving device additionally comprises at least one buffer memory. In an alternative, the buffer store is in at least one fluid connection directly or indirectly with the feed line and in a further alternative is in at least one fluid connection directly or indirectly with the discharge line, and in a third alternative is in fluid connection not only with the feed line but also with the discharge line. By "indirect" is meant that the fluid connection leads through the other components of the device according to the invention.

In particular, if the fixed fluid receptacle cannot currently or cannot completely contain the gas, the buffer store can temporarily contain and temporarily store the gas, which is ejected or otherwise escapes from the medical device. The buffer storage reduces the risk that a reverse flow of the ejected gas occurs in this case. The retrograde flow may react to the medical device and cause damage to the patient connected to the device and/or damage to the medical device. A large backflow can also cause the fluid connection of the receiving device to leak, for example, as a result of an overpressure. Due to the buffer storage, it is in many cases not necessary to reduce the overpressure, so that the gas is discharged into the environment. By being discharged into the environment, anesthetic agents may be present in the environment, which is undesirable as described above. Furthermore, in many cases no human action is required due to the buffer memory.

If more gas escapes from the medical device and enters the delivery line than the lead-out line can absorb, the gas is guided into the or at least one buffer store, i.e. preferably led out of the delivery line. If the escaping gas is less than the discharge line can absorb, the gas flows out of the buffer reservoir again and is preferably guided to the discharge line and from there into the fluid receptacle.

It is desirable in many cases to change the filter from time to time, especially when the filter becomes clogged after a prolonged period of use. During the time when the filter or the entire filter unit is replaced, it is often necessary or desirable to continue the artificial respiration of the patient. Even in this case, it should be avoided that a large amount of residual gas enters the environment. When changing the filter, it should also be avoided, in particular, that large amounts of anesthetic enter the environment. In this case, the or at least one buffer store according to the invention of the receiving device also receives at least a portion of the remaining gas, ideally the entire remaining gas, and then again outputs it.

Since according to the invention the at least one buffer store is in fluid connection with the feed line and/or the discharge line, it is not necessary to connect two filter receptacles in series, a bypass line (bypass) is provided for each fluid receptacle, and it is ensured that at each point in time a filter is installed in at least one filter receptacle. In many cases, such a series connection of two filter receptacles requires more space than a single filter receptacle and a buffer memory. The buffer memory according to the invention can be arranged spatially remote from the filter receptacle. Furthermore, due to the invention, in many cases, there is no need to bypass the line (bypass) around the filter receptacle.

A "filter" in the sense of the claims is understood to be a component which is capable of filtering out at least one gas component from a gas mixture during the gas mixture flowing through the filter. The filter may self-combine the gas components, for example using activated carbon and/or because the filter contains zeolite. The filter may also chemically or thermally decompose the gas component. The filter may also act mechanically and comprise, for example, molecular sieves. Multiple actions may be combined.

A "line" in the sense of the claims is a fluid conducting unit which connects two points to each other in a fluid-tight and also gas-tight manner and which is capable of conducting fluid from one point to the other. The lines may be flexible, in particular folded or smooth hoses, or rigid, in particular drums or tubes. A line in the sense of the claims can also be a fluid-tight coupling which releasably connects the filter unit to another device.

A "buffer reservoir" for gas is understood to be a chamber for receiving gas, which is surrounded by walls. In use, the gas comprises at least one anesthetic agent. The chamber is arranged such that it can hold more gas than it can output during a first period of time and can again output the same amount of gas or gas it held during the first period of time during a subsequent second period of time. The volume flow of the gas into the buffer storage is greater than the volume flow of the gas out of the buffer storage during a first period of time and less than the volume flow of the gas out of the buffer storage during a second period of time. According to the invention, during a first time period, gas flows from the supply line and/or the discharge line into the or a buffer store, and during a second time period, gas flows from the buffer store back into the supply line and/or the discharge line.

In one embodiment, the or a buffer memory is connected to the supply line only at one point and is not connected at all to the discharge line, or is connected to the discharge line only at one point and is not connected at all to the supply line. In this embodiment, the gas flows into the buffer reservoir at this point and flows out of the buffer reservoir again at the same point.

In a further embodiment, the or a buffer store is connected to the feed line and/or the discharge line at two different points spaced apart from one another. In this further embodiment, the cross-sectional area of the buffer store is greater than the cross-sectional area of the feed line and greater than the cross-sectional area of the discharge line. In this further embodiment, the buffer store can temporarily store gas due to this larger cross-sectional area.

In one embodiment, during the first period of time, the volume of the cavity and/or the pressure prevailing in the cavity increases. Preferably, the volume or pressure is doubled during the first period of time. The volume or pressure is reduced again during the second period of time. Preferably, after the second time period, the volume and the pressure are again as small as at the beginning of the first time period. The wall of the buffer reservoir may be rigid or elastic, so that the volume of the buffer reservoir is constant or varies depending on the difference between the pressure in the buffer reservoir and the pressure acting on the buffer reservoir from the outside.

In one embodiment, the wall separates the chamber of the buffer reservoir from the environment in a fluid-tight manner. It is also possible that the buffer store is fluidically connected to the environment and that the gas presses air out of the buffer store during a first time period, so that the air flows into the environment, and that the gas is transported out of the buffer store and the air flows back into the buffer store during a second time period. In this design, the volume and pressure in the cavity can be kept constant. In this embodiment, the buffer store also reduces the risk of large amounts of anesthetic escaping into the environment.

In the non-interfering operation, the line for the gas has the same volume at all times, in contrast, in the non-interfering operation there is no fluid connection to the environment, and the task is to guide the gas from the delivery point to the removal point. Typically, at each point in time, the volume flow entering the line is equal to the volume flow leaving the line.

According to the invention, the filter unit comprises a filter. Preferably, the filter unit additionally comprises a filter receptacle. The filter is mounted in the filter receptacle or can be mounted in the filter receptacle and preferably removed again from the filter receptacle. The filter receptacle is in fluid connection with the delivery line and the lead-out line, respectively. In one embodiment, the installed filter can be removed again from the filter receptacle, for example in order to be replaced by a new or another filter (filter having other filter properties). According to a preferred embodiment, the filter can be inserted into the filter receptacle or subsequently removed from the filter receptacle. It is thereby possible to replace the filter if it contains such a quantity of the or a gas component of the gas escaping from the medical device that the filter cannot or can no longer sufficiently fulfill its desired filtering effect and/or if the filter is clogged.

Due to the filter receptacle, it is not necessary to temporarily disconnect and then again establish a fluid connection between the supply line and the discharge line or to the medical device in order to replace the filter. Thus, a spent filter can be quickly replaced by a new filter. The risk of failure at the first or re-establishment of a fluid connection is reduced. It is also possible to use the same receiving device in the filter receiving space with different filters in succession and thus to filter different gas components from the gas and/or to install the receiving device under different environmental conditions. This feature also facilitates the provision of a plurality of receiving devices according to the invention for different purposes of use, in particular for filtering out different gas components. The receiving device according to the invention only needs to be distinguished by differently designed filters. The remaining components of the receiving device may be identical or differ only in size.

In the embodiment with a filter receptacle, the method according to the invention comprises the following additional steps:

-if not already occurring, mounting the filter into the filter receptacle;

the receiving device guides the gas escaping from the medical device through the supply line, the filter receptacle and the discharge line into the fluid receptacle or into the environment;

the receiving device guides the gas through the filter receptacle such that at least a part of the gas, preferably all of the gas, flows through the filter, wherein the filter is mounted in the filter receptacle.

In the alternative, the filter forms a fixed component of the filter unit, and the entire filter unit is the only component. The feed line and the discharge line can preferably be connected, particularly preferably releasably connected, to the filter unit. If the filter is consumed and can no longer accommodate further amounts of gas components, or if the filter is clogged, the filter unit and the filter are separated together from the feed line and the discharge line, and a new filter unit is connected to the feed line and the discharge line.

Further, in the above, a design has already been described in which the filter unit comprises a filter receptacle and at least one filter. The or a filter can be mounted in the filter receptacle and removed again from the filter receptacle, for example in order to replace the filter by a new filter. In a preferred embodiment, the filter unit further comprises a filter sensor. The filter sensor can automatically determine whether the filter is mounted in the filter receiving portion. Preferably, the filter sensor generates a message if no filter is mounted in the filter receiving portion. In an implementation, the filter sensor generates the message only when no filter is installed in the filter accommodation portion for a period longer than a preset period of time. In a modification, the filter sensor generates the message only when no filter is installed for a period longer than this time period and additionally gas is flowing through the delivery line. The design with a filter sensor reduces the risk that the filter cannot be unintentionally installed in the filter receptacle and therefore cannot filter out gaseous components and that larger amounts of gaseous components enter the fluid receptacle. On the other hand, in many cases, unnecessary warnings when replacing the filter are avoided.

Preferably, the or at least one buffer store is not only in fluid connection with the supply line and/or the discharge line, respectively, but additionally also in fluid connection with the environment, i.e. continuously or at least in the case of a large pressure difference between the interior of the buffer store and the environment. The buffer memory is located between the transmission line and/or the derivation line and the environment. The risk of back flow in the case of large amounts of gas escaping from the medical device, if both the fixed fluid holder and the buffer reservoir cannot completely hold this amount, is thereby further reduced. Although the escape of gas into the environment is not desired. But the escape of gas into the environment is generally less harmful than the backflow of the gas. The design of the buffer store in fluid connection with the environment is particularly advantageous when the buffer store is rigid, i.e. its volume is not changeable. A buffer store with a constant volume is generally more mechanically stable than a buffer store with a variable volume, since its housing can be rigid. The fluid connection to the environment furthermore results in that no overpressure is formed in the buffer reservoir, which is undesirable in some cases.

In one embodiment, the filter unit comprises a plurality of filters connected in parallel. The receiving device is designed such that the gas flows through the supply line, the at least one filter and the discharge line. The filter is located in the flow path from the delivery line to the lead-out line. In one embodiment, the gas flows through a filter, and at least one further filter is located in a backup position. In a further embodiment, the gas is divided into at least two parallel flows and each flow flows through a filter.

In an embodiment, the filter unit comprises a receiving unit for at least two filters, in particular a turret receiving portion. The receiving unit is movable relative to the conveying line and relative to the discharge line. The current position of the receiving unit relative to the conveying line determines which filter is currently used and which filter is located in the backup position. In another embodiment, the filter unit comprises an adapter or a Y-piece that selectively directs the gas flowing out of the delivery line to the first or second filter, the Y-piece dividing the gas into two parallel flows and thus onto the two filters.

In the case of an application with a multi-filter design, all filters of the filter unit are of similar design and in particular are able to filter out the same gas components. When the gas is consumed or blocked, the containing unit is moved relative to the delivery line or relative to the lead-out line, so that the gas flows through the new filter. For example, the filter unit includes a drive for receiving the unit.

In another embodiment, a first filter in the containment unit is capable of filtering out a first gas component, a second filter filters out a second gas component, and optionally a third filter filters out the first, second, or third gas component. The three gas components are chemically and/or mechanically different from each other. Depending on the desired or necessary application, the first filter or the second filter or optionally the third filter is moved into the flow path from the feed line to the discharge line. Preferably, the filter unit comprises a selection unit by means of which a user can select the gas component to be filtered. It is also possible to arrange a sensor upstream of the filter, which sensor identifies which gas component to be filtered is located in the gas flowing to the filter. Based on the signal of the sensor, the correct filter is moved into the flow path of the gas. Or output a corresponding message to the user.

Different designs of the buffer memory are possible and at least some of these designs can be combined with one another. It is possible that the receiving device according to the invention comprises exactly one buffer memory, or at least two similar or also at least two different buffer memories.

In the already mentioned embodiment, the filter unit comprises a filter receptacle, into which the filter is or can be fitted. In a development of this embodiment, the space enclosed by the filter receptacle is larger than the filter in at least one direction, more precisely: a gap is present between at least one inner wall of the filter receptacle and the opposite outer wall of the filter. It is possible for the gap to adjoin both outer walls of the filter, for example the circumferential side and the end face, or also to adjoin only one outer wall, for example the circumferential side. The gap is in fluid connection with the feed line and the discharge line, respectively, and forms or belongs to the or a buffer reservoir. Preferably, the gap occupies at least 10%, particularly preferably even at least 20%, in particular at least 30%, of the space enclosed by the filter receptacle. Preferably, the gap is fluid-tightly separated from the environment, so that no gas can escape directly from the gap into the environment.

In comparison with other possible designs of the buffer memory, the design with a gap takes up particularly little space and is mechanically stable. In addition, in some designs, the gap makes it easier for a person to grasp the filter in the gap and remove the filter from the filter receptacle.

In a period in which no filter is mounted in the filter accommodating portion, generally, the entire internal space of the filter accommodating portion can be used as a buffer memory. In the embodiment described immediately above, the inner space is larger than when the filter receptacle surrounds the filter without a gap, and therefore more gas can be accommodated. Thus, although no filter is installed and the filter receptacle is therefore open to the environment, only relatively little gas escaping from the medical device generally enters the environment. This is particularly desirable when the filter receptacle is open upwardly and the gas escaping from the medical device is heavier than air. Most anesthetics are heavier than air.

In the case of an embodiment with a filter receptacle enclosing a hollow space, the hollow space of the buffer store is preferably spatially separated and preferably separated, in particular fluid-tightly separated, from the hollow space for accommodating the filter, for example by a fixed or movable plate.

In a further embodiment, the buffer store comprises a housing which encloses a hollow space and which in one embodiment is a rigid housing, and in another embodiment is a resilient housing, and in a third embodiment is a housing having at least one rigid region and at least one resilient region. The housing is in at least one fluid connection with the supply line and the discharge line. The design with a buffer memory comprising a housing can also be combined with a design in which the filter unit forms a single component. In one embodiment, the housing of the buffer reservoir is additionally in at least one fluid connection with the filter unit, and the fluid connection is located between the housing and the feed line and/or is routed through the filter unit.

Preferably, a plurality of plates or other suitable guide elements are fitted into the interior space enclosed by the housing of the buffer store, which plates or guide elements provide a preferably meandering path through the housing. This embodiment makes it possible to connect the housing in a fluid-tight manner to the environment, and to nevertheless escape a relatively small amount of gas from the housing into the environment. The meandering path results in the gas flowing only slowly through the interior of the housing. The buffer store may have a rigid housing.

In one embodiment, the housing is in fluid connection with the environment, so that residual gases can escape into the environment. If a meander-shaped path is formed in the housing, relatively little gas generally escapes to the environment despite the fluid connection.

In both embodiments, the buffer memory is preferably designed such that it operates according to the principle "last-first-out" (LastIn-FirstOut).

In one embodiment, the housing of the buffer reservoir is arranged vertically or obliquely below the filter unit and is preferably in fluid connection with the filter unit. This embodiment is particularly advantageous when the gas having the gas component to be filtered is heavier than air and therefore sinks in the filter unit. Most anesthetics are heavier than air.

In one embodiment, the housing of the buffer store is arranged downstream of the filter unit. In an alternative embodiment, the filter unit is arranged downstream of the housing of the buffer store. The designation "downstream" relates to the direction of flow of the fluid from the delivery line to the lead-out line. Both embodiments result in a smaller vertical expansion of the receiving device according to the invention than the other possible embodiments.

It is possible that not only a gap is formed between the installed filter and the filter receptacle, but also a separate housing of the buffer store is arranged below or downstream or upstream of the filter unit. This embodiment can be implemented, providing a particularly large buffer memory. Further reducing the risk of gas escaping into the environment.

As already mentioned, in one embodiment, the filter unit comprises a filter receptacle in which the filter is or can be mounted. In a further development of this embodiment, the plate is mounted in the filter receptacle. The plate divides the interior space of the filter receptacle into a filter hollow space which is designed to accommodate the filter and a buffer memory hollow space which belongs to the or a buffer memory or forms a buffer memory. When no filter is installed in the filter receptacle, the buffer reservoir hollow space is at least fluidically connected on the one hand to the supply line and on the other hand to the discharge line.

The plate reduces the risk of gas from the fluid containing portion entering the environment even when no filter is installed in the filter containing portion. The design with the plate in the filter receptacle likewise saves space compared to other possible designs of the buffer memory. The need for a separate housing for the buffer memory is eliminated.

In one embodiment, the buffer reservoir hollow space is located below the filter hollow space. Preferably, the plates are arranged horizontally. This embodiment is particularly advantageous when the gas having the gas component to be filtered is heavier than air and therefore sinks in the filter receptacle. Most anesthetics are heavier than air.

The plate may be fixedly secured in the filter receptacle. In one embodiment, the plate can be moved back and forth relative to the filter receptacle between the parking position and the buffer storage position. The plate is in the parking position when the filter is mounted in the filter receptacle, and is otherwise in the buffer memory position. The transfer line comprises at least one outlet opening, which is preferably arranged inside the filter receptacle. The outlet line comprises at least one inlet opening, which is preferably arranged in the interior of the filter receptacle.

When the board is located in the buffer memory location, the following is established according to this design:

the or one outlet opening connects the transfer line with the buffer reservoir hollow space;

the or one inlet opening connects the buffer memory empty space with the lead-out line;

whereby the buffer reservoir hollow space is in fluid connection with the transfer line and the lead-out line, respectively;

in one embodiment, the plate seals the buffer reservoir hollow space from the environment and from the filter hollow space as fluid-tight as possible. The filter receptacle seals the two hollow spaces from the environment.

When the plate is in the parking position, the following is established according to this design:

the or one outlet opening connects the transfer line with the filter hollow space;

the or one inlet opening connects the lead-out line with the filter hollow space;

thereby, the filter hollow space and the correctly installed filter are in fluid connection not only with the delivery line, but also with the lead-out line;

in one embodiment, the plate separates two openings (which connect the feed line or the discharge line to the filter hollow space) from the buffer reservoir hollow space in a fluid-tight manner in the parking position;

in a further embodiment, the supply line and/or the discharge line are in fluid connection with the buffer reservoir hollow space when the plate is in the parking position.

The buffer reservoir void space provides a buffer reservoir inside the filter receptacle when the plate is in the buffer reservoir position. The buffer reservoir can thus accommodate the remaining gas from the medical device when no filter is currently installed. This is particularly the case when the filter in the filter receptacle is replaced. The plate in the buffer reservoir position separates the buffer reservoir empty space from the environment and reduces the amount of gas escaping into the environment.

Due to the movable plate, no additional means need be provided to achieve the desired filtering on the one hand and to prevent the escape of gas into the environment on the other hand. The plate enables a relatively simple mechanical design.

In one embodiment, the filter unit is designed such that when the filter is installed in the filter receptacle, the plate is moved from the buffer position into the parking position. When the filter is removed again from the filter receptacle, the plate is moved again from the parking position into the buffer memory position. Mechanical or pneumatic springs, for example, are intended to move the plate into the buffer store position and hold it therein. Preferably, the spring is supported on the housing of the filter receptacle.

In one embodiment, the filter unit is designed such that a movement of the plate from the parking position into the buffer storage position removes the filter from the filter receptacle.

In one embodiment, the plate is connected to an actuating element, which is preferably accessible from the outside of the filter receptacle and can preferably be actuated manually in order to move the plate back and forth between the two positions. For example, the filter is mounted in the filter receptacle and the actuating element is then actuated in order to move the plate into the parking position. This also leads the filter completely into the filter receptacle. To remove the filter, the handling element is again handled and the plate is moved to the buffer memory location. Thereby removing the filter from the filter receiving portion.

In a further embodiment, the drive can move the plate back and forth between two positions. The driver may preferably be controlled and/or activated from the outside.

Preferably, the plate snaps in at least one end position, particularly preferably in both end positions.

Preferably, the parking void is smaller than the buffer memory void. This embodiment thus saves space compared to other possible embodiments of the buffer memory.

In one embodiment, the actuating element and/or the drive to be actuated manually is connected to the plate. The plate can be moved from one position to another by means of the actuating element. The drive is capable of moving the plate from one position to another.

In a preferred embodiment, the filter is mounted and removed in contrast in such a way that the plate is moved from one position to another and the gas flow is thereby guided through the filter hollow space or the buffer hollow space. This embodiment eliminates a separate actuating element or a separate drive. It is possible that the blocking unit holds the plate in one position.

Preferably, the plate is elastically supported in the filter receptacle. At least one spring element is dedicated to moving the plate into the buffer storage position, in particular upward. The spring element is preferably supported on the filter receptacle. The installed filter moves the plate into the parking position counter to the spring force, preferably on the basis of its own weight and/or on the basis of the force effect when the filter is installed. This design eliminates the need to provide an operating element and/or an action and/or a drive to move the plate from one position to another. Instead, the panels are automatically moved from one location to another upon installation and upon removal. It is also possible for a latching connection or lock to hold the plate in the parking position.

According to the embodiment described immediately above, the plate in the interior of the filter receptacle separates the filter hollow space from the buffer reservoir hollow space, i.e., in the embodiment, it separates the filter hollow space from the buffer reservoir hollow space in a fluid-tight manner.

In a further development of the fluid-tight design, a slide is additionally located inside the filter receptacle, which slide is preferably mechanically connected to the plate. The slide can also be moved back and forth between the parking position and the buffer memory position, preferably together with the plate.

According to this embodiment, the conveying line comprises two outlet openings spaced apart from one another, namely a filter outlet opening and a buffer reservoir outlet opening. The outlet line also comprises two spatially separated inlet openings, namely a filter inlet opening and a buffer memory inlet opening.

When the plate and the slide are in the parking position, the conveying line is connected with the filter hollow space through the filter outlet opening. The outlet line is connected to the filter hollow space via the filter inlet opening. The slider blocks the buffer memory outlet opening and the buffer memory inlet opening. The gas escaping from the supply line is conducted through the filter hollow space and further through the filter to the discharge line. The slide block in the parking position prevents gas from bypassing the filter in the filter receptacle and flowing from the supply line through the buffer reservoir hollow space directly into the discharge line.

When the plate and the slide are in the buffer memory position, the conveying line is connected to the buffer memory hollow space via the buffer memory outlet opening. The lead-out line is connected with the hollow space of the buffer memory through the inlet opening of the buffer memory. The slider blocks the filter outlet opening and the filter inlet opening. The gas escaping from the supply line is conducted through the buffer reservoir hollow space to the discharge line. The slide in the buffer storage position prevents the gas from escaping from the supply or discharge line and entering the filter hollow space and from there into the environment. In this embodiment, the plate in the buffer storage position also separates, i.e. preferably separates in a fluid-tight manner, the buffer storage hollow space from the filter hollow space.

The embodiment just described with the plate and the slide results in a particularly simple mechanical implementation. It is possible that the actuating element and/or the drive to be actuated manually can move the slide. Preferably, the installation of the filter results in the plate and the slide being moved into the parking position and held therein. The removal of the filter results in the plate and the slide being moved into the buffer memory position and held therein. In an embodiment, at least one mechanical or pneumatic spring is used to move the plate and the slide into the buffer storage position and hold it therein. The spring is preferably supported on the filter receptacle. Instead of a spring, other elastic elements can also be used, which exert a force on the slider.

In one embodiment, the volume of the or at least one buffer store can be changed, preferably reversibly. In particular, the buffer memory comprises walls which are elastic completely or at least in one region. Thereby, the buffer memory can expand and contract again. The delivery of the gas expands the buffer reservoir and thereby increases its volume. The expanded buffer store can in turn output the stored gas, wherein the buffer store contracts and its volume decreases. In many cases, this design results in a particularly simple to construct buffer memory. A smaller overpressure is formed inside the buffer reservoir than in a buffer reservoir with a rigid housing.

Preferably, the expandable buffer reservoir is in fluid connection with the transfer line, arranged upstream of the filter unit. This embodiment results in a smaller time-dependent change in the amount of gas that reaches the filter unit per unit time. This embodiment reduces the risk of an undesirably high pressure acting on the medical device and thus on the patient connected to the medical device when the receiving device is connected to the medical device. The expandable buffer reservoir may also be fluidly connected to the lead-out line and arranged downstream of the filter unit.

In one embodiment, the receiving device comprises an expandable buffer reservoir and a buffer reservoir with a rigid housing and/or a buffer reservoir inside the filter receiving part. Preferably, the elastic buffer store is arranged upstream of the buffer store with the rigid housing. The amount of gas reaching the rigid buffer store per unit time is thus less variable over time. It is also possible that the expandable buffer store is in fluid connection with other buffer stores.

In use, the receiving device according to the invention is connected to a medical device, in particular an anesthesia device. The bag for manual respiration of the patient serves as the or a buffer store. The bag is connected to a transfer line or a lead-out line. Such manual breathing bags have generally been allowed for medical use and have standardized dimensions. The connecting piece of the receiving device according to the invention can be adapted to the dimensions.

In one embodiment, the receiving device additionally comprises at least one overpressure valve in or on the supply line. The overpressure valve opens if the pressure difference across the overpressure valve is above a predefinable overpressure limit. The opened overpressure valve discharges the gas into the environment. The overpressure valve is positioned such that it opens automatically if the difference between the pressure in the delivery line and the ambient pressure around the delivery line is above an overpressure limit. The overpressure valve thereby reduces the overpressure in the supply line and, in particular, the risk of a backflow in the supply line. The reverse flow may act in an undesirable manner on the device that ejects the gas into the delivery line.

In one embodiment, the overpressure limit is predefined by the design of the overpressure valve. In a further embodiment, the pressure sensor measures a pressure difference across the overpressure valve. In an implementation, a control device or comparator receives the measurement values of the pressure sensor and controls the overpressure valve such that the overpressure valve is opened when the pressure difference is above an overpressure limit. In another implementation, the measurement of the pressure sensor is output in a form perceptible by a human. When a pressure difference above an overpressure limit is detected, a warning is output, for example. The two implementations of the control device/comparator controlling the overpressure valve and outputting the measured values and/or the warning can be combined with each other.

In one embodiment, the or an overpressure valve is arranged in series with the filter unit and upstream of the filter unit, in particular in or on the feed line. In a further embodiment, the or an overpressure valve is arranged in parallel with the filter unit. In a further arrangement, when the overpressure valve is open, a portion of the gas flows through the delivery line and around the filter unit. In both embodiments, the feed line conducts the entire gas to the filter unit when the overpressure valve is closed.

In one embodiment, the open overpressure valve discharges gas into the environment. In a further embodiment, a fluid conducting unit, in particular a hose or another line, connects the excess pressure valve to the discharge line. When the overpressure valve opens, a fluid connection is established from the supply line through the fluid conducting unit to the discharge line. In a third embodiment, the overpressure valve is arranged inside the filter unit. When the overpressure valve is opened, the gas also flows through the supply line and the filter unit into the outlet line without escaping into the environment. However, at least a portion of the gas does not flow through the filter of the filter unit, but flows around the filter. Both preferred embodiments reduce the risk of gas escaping into the environment when the overpressure valve opens. Conversely, in overpressure, the gas flows around the filter into the outlet line.

A further possible arrangement of the overpressure valve can be combined with a design of the filter unit comprising a filter receptacle, wherein the filter can be mounted in the filter receptacle, and wherein the filter receptacle is in fluid connection with the supply line and the discharge line, respectively. In this embodiment, when the overpressure valve is closed, the gas is conducted from the supply line through the filter to the discharge line. When the overpressure valve is opened, gas also flows from the supply line through the interior of the filter holder into the discharge line. However, at least a portion of the gas flows by the filter. This design reduces the risk that gas can escape into the environment when the overpressure valve opens.

The or an overpressure valve can also be arranged on the filter receptacle or on or in the discharge line and, in the event of overpressure, discharges the gas into the environment.

In a development of the design with an overpressure valve, at least one opening is embedded in the wall of the filter unit. An overpressure valve closes the opening. When the overpressure valve opens on the basis of an overpressure, the filter unit is fluidly connected to the environment via the opening. It is also possible for the openings to be arranged parallel to the overpressure valve. Preferably, the overpressure valve closes automatically again when the overpressure is reduced.

In a further embodiment, the receiving device comprises at least one negative pressure valve. The negative pressure valve opens when the difference between the pressure in the conveying line or inside the filter unit on the one hand and the pressure in the surroundings on the other hand is below a preset negative pressure limit. Such a large negative pressure is generally undesirable, since it can suck gas away from the equipment connected to the conveying line. If the device is a medical device and is connected to a patient, the patient may be at risk due to the negative pressure. Such a negative pressure may for example be formed when gas is actively sucked away from the lead-out line and the filter unit and/or the conveying line is blocked or the conveying line does not connect the device correctly (misconnection) to the filter unit.

Similarly to the overpressure valve, in an embodiment, the negative pressure limit is predefined by the design of the negative pressure valve. In another embodiment, the control device or the comparator causes the negative pressure valve to open when the negative pressure falls below the negative pressure limit. In a third implementation, the message is output in a human perceptible form when the negative pressure is below the negative pressure limit. The implementation of the control device for automatically opening the negative pressure valve and outputting the message can be combined with one another.

In one embodiment, the filter element is inserted into at least one opening, preferably a plurality of openings, in the wall. A fluid connection between the interior of the filter unit and the environment can be established through the opening. If the filter unit comprises a filter receptacle (into which the filter is or can be fitted), the opening is preferably embedded in the wall of the filter receptacle.

When the negative pressure valve is open, a fluid connection between the interior of the filter unit and the environment is established, so that gas can flow from the environment through the negative pressure valve and the opening or openings into the interior of the filter unit. When the negative pressure is less than the negative pressure limit, the or a closed negative pressure valve closes the opening or openings and interrupts the fluid connection between the interior of the filter unit and the environment. The openings restrict the flow of gas into the filter unit.

In a modification of this embodiment, the negative pressure valve is embedded in the wall of the buffer reservoir or in the wall of the conveying line. When the negative pressure in the buffer store is below the negative pressure limit, gas flows from the environment into the buffer store. This configuration reduces the risk that too high a negative pressure in the buffer store sucks gas out of the conveying line or that the buffer store is damaged due to too high a negative pressure.

In a preferred embodiment of the design of the filter unit comprising the filter receptacle, the filter receptacle comprises a tank or is designed as a tank. The filter can be mounted into the tank from above and removed from the tank again. Preferably, the tank can be closed fluid-tightly with a lid, and the lid can in turn be removed, for example in order to replace the filter. When the gas to be filtered is heavier than air, the gas sinks in the tank and no significant amount can escape directly into the environment. When no filter is currently installed in the pot-shaped filter receptacle, for example during a filter change, only relatively little escaping gas enters the environment, even when the pot is not closed but is open to the environment, in particular during a filter change. This embodiment saves time when changing the filter.

According to the invention, the filter unit is in at least one fluid connection with the transfer line. In one embodiment, a section of the conveying line leads through the interior of the filter unit. This section is preferably located between the wall of the filter unit and the filter mounted in the filter receptacle. If the filter unit comprises a filter receptacle, preferably a section of the conveying line leads through the interior of the filter receptacle and, in the case of a filter installation, is located between the filter and the wall of the filter receptacle. The outlet opening in this section of the conveying line determines at which point the gas escapes from the conveying line and enters the filter receptacle and thus the filter. The outlet opening may be located near the bottom of the filter unit, in particular near the filter receptacle. This embodiment is particularly advantageous when the gas from which the or at least one gas component is to be filtered is heavier than air, in particular in gas mixtures with anesthetic agents. The outlet opening may also be positioned near the upper end of the filter unit. It is also possible for the first outlet opening to open into the filter and for the second outlet opening to open into a buffer reservoir in the filter receptacle. Depending on whether a filter is installed, one outlet opening is open and the other outlet opening is closed, or vice versa.

The lead-out line may also comprise a section arranged inside the filter unit and between the wall of the filter unit and the installed filter. If the filter unit comprises a filter receptacle, then preferably this section of the lead-out line is located between the filter and the wall of the filter unit. The section may have one inlet opening, optionally at least two inlet openings.

This embodiment can be combined with the embodiment described above, wherein a hollow space is present between the filter receptacle and the filter, and the hollow space belongs to the buffer memory. Preferably, the section of the feed line and the section of the discharge line in the filter receptacle are separated from the buffer store in the filter receptacle in a fluid-tight manner.

It is possible that the gas only enters the receiving device according to the invention, so that the gas is transported into the conveying line, for example ejected by a device connected to the conveying line. In a further embodiment, additionally or alternatively, gas is sucked out of the discharge line. According to a further embodiment of the invention, the receiving device further comprises a vacuum generator, in particular a suction pump, which is preferably arranged on or downstream of the discharge line. A negative pressure generator is fluidly connected to the lead-out line and generates a negative pressure in the lead-out line. The negative pressure in the lead-out line sucks the gas. The suctioned gas is suctioned from a device connected to the delivery line, in particular a medical device, through the delivery line, the filter unit and the discharge line. Preferably, at least one fluid connection connects the or one buffer reservoir with the lead-out line. The negative pressure caused by the negative pressure generator empties the buffer reservoir through the fluid connection even when no or only a small amount of gas currently escapes from the medical device.

In the embodiment already described, the filter unit comprises a filter receptacle and a filter. The filter receptacle is in fluid connection with the delivery line and the lead-out line, respectively. The filter can be mounted in the filter receptacle and can in turn be removed from the filter receptacle, for example in order to replace it with a new filter. The design described above with the negative pressure generator achieves a further advantage if it is realized in combination with the filter receptacle and the filter. In various embodiments, the filter receptacle is at least partially in fluid connection with the environment when the filter is replaced. The negative pressure generator sucks the gas out of the filter housing even when the filter is not mounted. The negative pressure generator thereby reduces the amount of gas escaping from the filter receptacle into the environment.

The negative pressure generator is advantageous even when the or at least one buffer reservoir is continuously or at least temporarily in fluid connection with the environment, for example in order to reduce overpressure. The negative pressure generator reduces the overpressure and reduces the risk of large amounts of gas escaping into the environment.

In a modification, the negative pressure generator is in fluid connection with the delivery line of the receiving device. The filter unit and/or the at least one buffer store are arranged downstream of the negative pressure generator. This embodiment facilitates the pneumatic resistance of the filter unit to be overcome.

It is possible that the gas sucked in by the vacuum generator is sucked into the above-mentioned fluid receptacle via the supply line and from there further into the discharge line. The outlet line and the fluid receptacle also prevent a large amount of gas constituents from escaping into the environment when no filter is installed in the filter receptacle. This effect occurs primarily because the negative pressure caused by the negative pressure generator draws gas away from the buffer reservoir and thus prevents the gas from escaping into the environment.

The negative pressure generator has the following additional functions: the resulting negative pressure overcomes the pneumatic resistance of the filter of the containing device and reduces the risk of reverse flow upstream of the filter.

In a development of this embodiment, the control device of the receiving device controls the regulating unit of the vacuum generator and causes the vacuum generator to achieve the desired volume flow in the discharge line. The sensor measures the actual volume flow and the control device receives the measured value of the sensor for the actual volume flow and controls the regulating unit so as to reduce the difference between the desired and the actual volume flow, i.e. to regulate or control the volume flow in the derived line.

Preferably, the negative pressure generator comprises a suction pump. Instead of the suction pump, other negative pressure generators, for example, injection systems, can also be fluidically connected to the discharge line.

Preferably, the gas is guided through the filter unit on its way from the supply line to the discharge line, forcibly on a predetermined path, i.e. the gas is guided forcibly. The forced guidance results in the entire gas flowing through the filter and no gas flowing past the filter. The risk of undesired gases entering the fluid receptacle is thereby reduced.

It is furthermore preferred that the gas is forced through the filter. In one embodiment, the wall divides the filter into at least two regions. Preferably, the wall extends parallel or obliquely to the direction of gas flow through the filter. A first region of the filter is fluidly connected to the transfer line and a second region of the filter is fluidly connected to the drain line. The filter is designed such that the gas flows through the delivery line, then through the first region, the second region and then into the discharge line. In this embodiment, the gas is filtered twice, i.e. once in the first region and once in the second region. Even when one area is clogged and a smaller or even no filtering effect is achieved, in many cases there are additional areas to filter. This design therefore increases reliability.

Preferably, the containing means comprises at least one check valve. The non-return valve is arranged, for example, in the discharge line or the supply line. Flow in the direction from the transfer line through the lead-out line can be achieved and flow in the opposite direction is prevented. When the outlet line is connected to the fluid receptacle, the check valve prevents fluid from passing from the fluid receptacle through the outlet line and the delivery line into the device connected to the delivery line. Such backflow may damage the equipment, or in the case of medical equipment, harm the patient connected to the equipment. The receiving device may also comprise a plurality of non-return valves, for example a non-return valve in the delivery line and a non-return valve in the discharge line.

Typically, the filter of the filtration unit is only able to accommodate the maximum amount of the or each gas component to be filtered and is consumed. After accommodating the maximum number, the filter unit must be replaced. The maximum number is for example preset by the manufacturer of the filter unit or may be calculated in advance. Furthermore, in some designs of the filter, it is possible that the filter swells due to the liquid and for this reason can no longer accommodate a further amount of gas constituents and therefore has to be replaced.

In one embodiment, the receiving device comprises a component sensor, in particular an anesthetic agent sensor, for the or at least one gas component to be filtered. The sensor measures a measure for the amount or concentration of a gas component in the gas flowing past at a measurement point downstream of the filter. If the scale exceeds a preset composition limit, the composition sensor triggers the output of a warning. The amount or concentration above the anesthetic limit indicates that the filter is no longer able to adequately filter out the gas component from the gas flow flowing through. In one embodiment, the warning is output in a form perceptible by a human at a spatially remote location, for example in a control center. It is possible for the receiving device to have different composition sensors for different gas compositions.

In a preferred embodiment, the sensor comprises a measuring probe or other measuring value receiver, which is arranged in the interior of the filter receptacle of the filter unit. If the gas component to be filtered is heavier than air and therefore sinks, the measured value receiver is preferably located below the filter in the filter receptacle. In a further embodiment, the sensor is arranged downstream of the filter unit. In both embodiments, the measurement value receiver is positioned downstream of the filter and measures the concentration of at least one gas component to be filtered in the gas flowing past. If the filter is no longer able to filter a sufficient amount of gas components from the flowing gas stream, the sensor will register an increased concentration of gas components that are to be filtered but are not actually filtered.

In addition, possible embodiments of the filter unit with a filter receptacle have already been described above, in which an overpressure valve in the interior of the filter receptacle opens when the pressure in the interior of the filter receptacle exceeds a predetermined overpressure limit. When the overpressure valve is opened, in an implementation, at least a portion of the gas reaching the filter receptacle is guided to bypass the filter in the filter receptacle. In this case, the sensor with the measured value receiver measures the increased concentration of the gas component to be filtered in the interior of the filter receptacle. The sensor detects an increased concentration both when an overpressure occurs and the overpressure valve opens and the gas therefore flows in the filter receptacle past the filter, and when the overpressure valve closes and the gas, although flowing through the filter, can no longer filter out the gas component to a sufficient extent.

In one embodiment, the warning is output when at least one of the following occurs:

the sensor just described measures the increased concentration of the gas component in the interior of the filter receptacle,

the overpressure valve on the feed line, the filter unit, the discharge line or on the or a buffer store opens or has been opened,

the negative pressure valve on the feed line, the filter unit, the discharge line or on the buffer reservoir or buffer reservoirs is or has been opened.

This embodiment ensures that a warning is output not only when the filter is consumed (because the filter contains a large amount of gas components), but also when the filter is clogged for other reasons, for example by plugging or incorrect installation or without removing the packaging. In many cases, a warning is also output when clogging occurs upstream of the filter.

In a further embodiment, the receiving device comprises a component-quantity determiner. The component-quantity determinator determines approximately the measure of the quantity of the filter which has been accommodated so far for a predetermined gas component, in particular an anesthetic agent. By "to date" is preferably meant: starting from the point in time when the currently used filter has started to be used in the filter unit. The component-quantity determiner may be arranged inside the device connected to the transmission line or implemented on a computer, for example on a smartphone. To approximately determine the quantity, in one embodiment, a component-quantity determiner receives and uses

On the one hand, a signal for the time-varying volume flow of gas through the delivery line to the filter unit, and

on the other hand, a signal for the time-varying concentration of the or at least one gas component in the delivery line.

In a further embodiment, the component-quantity determinator receives a signal for feeding the gas component into the supply line. For example, a measure for the amount of anesthetic added to the carrier gas.

The component-quantity determiner receives the signal by wire or by radio waves. The component-quantity determiner calculates approximately the quantity hitherto accommodated by the filter from the two signals. The product of the gas volume flow and the concentration provides the volume flow of the gas component. In the case of a concentration change over time, the integration is carried out numerically on the product.

This design eliminates the need for a sensor downstream of the filter unit. The devices that can be connected to the supply line usually already comprise a sensor for the volume flow. In some cases, the concentration of the gas constituent may be measured by another sensor of the device, or adjusted on the device. The component-quantity determinator is at least temporarily in data connection with the two sensors, either wired or wirelessly (via radio waves).

In one embodiment, information is stored in the data memory about the number of gas components that the filter of the filter unit has hitherto contained. If the filter can accommodate different gas components, then in a development of this embodiment, for each possible gas component that the filter can accommodate, an identification of this gas component and information on how many gas components the filter has so far accommodated are written on the data carrier.

The data carrier can be a component of the filter unit and is, for example, fixed to the filter unit. The data memory belonging to the filter unit is preferably designed as an RFID chip, which can also be designed as a bar code. The data memory may be spatially separated from the filter unit. The quantity contained so far can be measured by the sensor of the filter unit or approximately determined by the just described ingredient-quantity determiner. Preferably, the information about the stored quantity can be determined and read from a remote location and compared with a preset prescribed value, which preset the maximum quantity that the filter can accommodate. This embodiment makes it possible to provide a new filter or a new filter unit with a filter in time. Furthermore, the design with a data memory for the amount to be stored facilitates the sorting of consumed filters and/or the obtaining of material from filters. The information stored in the data memory can be used to match the collation to the gas composition and/or the gas quantity contained by the filter.

It is possible that the same filter can accommodate different gas compositions during use. Preferably, for each gas component, information about the maximum possible quantity is stored in the data memory in each case. The number of filters accommodated so far is compared with the maximum possible number stored in the data memory for each gas component.

In one embodiment, the or one of the gas components that the filter is capable of filtering out of the gas flowing through is an anesthetic agent. In a further embodiment, the component is a gas that is combustible and/or harmful to humans. The gas component may also be a quantity of particles contained or possibly contained in a gas, such as dust or microorganisms or viruses or other pathogens possibly in the air. It is possible that the filter is capable of filtering out a plurality of gas components, for example a plurality of different anesthetics and/or at least one anesthetic agent and particles, from the gas flowing through.

The invention further relates to a medical device comprising at least one medical apparatus and a receiving device according to the invention. The or a medical device is in particular an anaesthetic device. The delivery line of the receiving means is at least temporarily in fluid connection with the or one medical device. Preferably, the fluid connection can be established and subsequently released again. Thereby, the same receiving means may be connected in turn with different medical devices, and the same medical device may be connected in turn with different receiving means.

In one embodiment, the receiving device according to the invention is spatially separated from the medical device. The delivery line of the containment device is fluidly connected to the medical apparatus. Preferably, the receiving means can be connected to different medical devices in sequence. In a further embodiment, the receiving device according to the invention is a component of a medical device and is arranged inside the medical device. Preferably, the lead-out line provides a coupling site for fluids ejected and/or aspirated by the medical device.

In one embodiment, the medical device comprises first and second medical devices. Alternatively or simultaneously, a fluid connection between the delivery line and the first medical device and/or between the delivery line and the second medical device can be established. This embodiment eliminates the need to provide the two medical devices with their own receiving devices with filter units.

If two medical devices are connected to the receiving device at the same time, the volume flow and/or the pressure in the delivery line can in some cases change less than if the receiving device is connected to only one medical device.

It is also possible that the receiving device according to the invention is in selective or simultaneous fluid connection with three or more medical devices respectively.

According to the invention, the outlet line can be connected to a fluid receptacle, which in the embodiment is a stationary fluid receptacle. The stationary fluid receptacle preferably belongs to a medical infrastructure system, in particular a stationary infrastructure system in a hospital. Medical infrastructure systems can also provide the required gases and other fluids to the medical equipment. Optionally, a negative pressure generator of the fluid receptacle, for example a suction pump, is at least temporarily in fluid connection with the outlet line and is capable of sucking in gas.

The invention further relates to a medical system comprising a medical device having at least one medical apparatus and a receiving device according to the invention and a fluid receiving part. The outlet line of the receiving device is at least temporarily in fluid connection with the fluid receiving portion.

In a refinement of this embodiment, the medical system comprises at least one further fluid receptacle. Particularly preferably, the two fluid receptacles of the medical system are fixed fluid receptacles. Alternatively or simultaneously, a fluid connection between the fluid receptacle and the outlet line or between a further fluid receptacle and the outlet line can be established. It is also possible that the medical system comprises three or more fluid receptacles, wherein the outlet line is in selective or simultaneous fluid connection with at least three respective fluid receptacles.

The design with at least two fluid receptacles makes it possible to receive a particularly large amount of gas from the medical device. It is also possible to selectively divert gases ejected and/or sucked away by the medical device to one fluid receptacle or to another fluid receptacle, which is particularly advantageous in some cases when the medical device ejects different gases in sequence, for example gases with different anesthetics.

In other applications, the containment device is used to remove microorganisms, other pathogens, or particles from the air in an area, such as an enclosed space in a building or vehicle. Preferably, the containing means comprises, or is in fluid connection with, a transport unit. The transport unit transports the air to be cleaned from the space back to the space via the transport line, the filter unit and the lead-out line.

Drawings

The invention is described subsequently with the aid of examples. Here:

fig. 1 shows a medical device with an anesthesia apparatus and a receiving device according to the invention;

fig. 2 shows a design with a pneumatically acting buffer reservoir inside the filter receptacle and surrounding the filter, in which a filter cartridge with a filter is installed;

FIG. 3 shows the design of FIG. 2 with the filter cartridge removed;

FIG. 4 shows a modification of the design of FIG. 2, in which gas is forced through the filter cartridge and the filter cartridge is installed;

fig. 5 shows a modification of the embodiment of fig. 4, in which an overpressure valve is arranged in the supply line, which, in the event of an overpressure, discharges gas into the environment;

fig. 6 shows a modification of the design of fig. 5, in which the open overpressure valve does not discharge gas into the environment but into a discharge line;

fig. 7 shows a modification of the design of fig. 6, in which the measuring probe of the filter unit also measures the properties of the gas discharged from the overpressure valve;

fig. 8 shows different possible implementations of the overpressure valve of fig. 5 to 7;

fig. 9 shows a cross-sectional view of the design of fig. 4 to 7 in the plane a-a of fig. 4 to 7;

FIG. 10 shows the design of FIG. 4 with the filter cartridge removed;

FIG. 11 shows a design with a negative pressure valve on the canister;

fig. 12 shows a different possible implementation of the negative pressure valve of fig. 11;

fig. 13 shows different possible implementations of a flexible buffer memory in a conveying line;

fig. 14 shows a design of a buffer storage with a mechanical action inside the filter receptacle and additionally below the filter, in which a filter cartridge is installed;

FIG. 15 shows the design of FIG. 14 with the filter cartridge removed;

FIG. 16 shows a modification of the design of FIGS. 14 and 15 in which gas is forced through and installed with a filter cartridge;

FIG. 17 shows the design of FIG. 16 with the filter cartridge removed;

fig. 18 shows a further modification of the design of fig. 14 and 15, in which a mounted filter holds the movable slide in the parking position;

FIG. 19 shows the design of FIG. 18 with the filter removed and the slider in a buffer memory location;

FIG. 20 shows a design with a separate buffer storage under the filter receptacle, with a filter cartridge installed;

FIG. 21 shows the design of FIG. 20 with the filter cartridge removed;

FIG. 22 shows a combination of multiple designs of buffer storage with a filter cartridge installed therein;

FIG. 23 shows the combination of FIG. 22 with the filter cartridge removed;

FIG. 24 shows a design with a separate buffer memory downstream of the filter receptacle;

fig. 25 shows a modification of the device according to fig. 1, which additionally comprises an anesthetic agent dose learning device and a data memory on the filter unit;

FIG. 26 shows a filter unit with two filters mounted in a turret housing;

fig. 27 shows a configuration in which two medical devices are connected to the same receiving device according to the invention;

fig. 28 shows a design in which two fixed gas containers are connected to the same container device according to the invention.

Detailed Description

In an embodiment, the invention is used for artificial respiration of a patient, and at least one anesthetic agent is delivered to the patient. During the time the patient is being artificially breathed, the patient is located in a closed space, for example a ward of a hospital or on a vehicle.

Fig. 1 shows a medical device for anaesthetizing a patient P and for artificially breathing the patient. The patient P is supplied with breathing air via an inspiratory gas line 27. The breathing air is mixed with at least one anesthetic agent in order to keep the patient P anesthetized. The breathing air exhaled from the patient P contains carbon dioxide (CO 2) and is drawn away through the expiratory gas line 28. The two gas lines 27, 28 are connected to a medical device in the form of an anesthesia device 1, which maintains a breathing cycle in order to supply the patient P with breathing air and anesthetic agent and in order to suck off and contain exhaled air.

The anesthesia apparatus 1 is supplied with breathing air under pressure, pure oxygen (O2) and laughing gas (N2O) by the hospital infrastructure. In an embodiment, the anesthesia apparatus 1 comprises the following components:

a mixer 29 which produces a mixture from two of the three gases delivered, namely air, O2 and N2O, which mixture serves as carrier gas for the anesthetic agent, wherein the mixer 29 can thus be constructed as described in DE 102008057180B 3,

a fan unit 5 which moves the gas in the breathing cycle and thereby maintains the breathing cycle,

an anesthetic vaporizer 2 comprising a tank 49 for anesthetic agent in liquid state, and

a filter unit 3 with a scale filter inside the device, which filters out CO2 from the respiratory air exhaled by the patient P and conducted out through the expiratory gas line 28.

The anesthetic vaporizer 2 adds anesthetic agent from the canister 49 to the carrier gas. For example, the anesthetic vaporizer 2 vaporizes and/or sprays anesthetic agent in the canister 49 into the carrier gas.

The anesthesia apparatus 1 delivers gas to the respiratory cycle. The filter unit 3 draws gas, in particular CO2, from the breathing cycle. In summary, more gas is thus delivered to the breathing cycle than is removed. It is therefore desirable to derive the residual gas from the breathing cycle. The residual gas, which is subsequently referred to as "residual gas", is removed from the anesthesia apparatus 1 by means of the two gas lines 6 and 8, i.e. by means of the feed line 6 and the discharge line 8. On the one hand, the fan unit 5 ejects gas and delivers the ejected residual gas into the delivery line 6, wherein the volume flow rate of the ejected residual gas varies over time and the course of the variation over time of the volume flow rate has, for example, the shape of a half-sine curve. On the other hand, the ejected residual gas is guided through the outlet line 8 and, in one design, is sucked in.

In the exemplary embodiment, the outlet line 8 leads to a fixed fluid receptacle 7, which is embedded in the wall W. The fluid receptacle 7 is preferably a component of a fixed infrastructure of a hospital, which accommodates and further conducts gases emitted by different medical devices.

Preferably, a check valve 65 is inserted into the discharge line 8, which check valve allows gas to pass from the discharge line 8 in the direction of the fluid receptacle 7, but prevents gas from flowing back from the fluid receptacle 7 through the discharge line 8. In an alternative embodiment, the check valve 65 is integrated into the fluid receptacle 7. It is also possible that the or a check valve 65 is positioned in the delivery line 6 or in the connection between the delivery line 6 and the anesthesia apparatus 1. In all possible positions, the non-return valve 65 enables the anesthesia apparatus 1 to eject gas, but prevents gas from flowing back into the anesthesia apparatus 1 and thus possibly having an effect on the patient P.

The medical device furthermore comprises a receiving device 100 according to the invention with a filter unit 4 and lines 6, 8. The filter unit 4 includes filters 11, 20 and a tank 13, which functions as a filter housing. These components are described in detail later.

In the embodiment shown in fig. 1, the supply line 6 is located partly outside the anesthesia apparatus 1. It is also possible that the supply line 6 is located completely inside the anesthesia apparatus 1 and that the filter unit 4 is releasably coupled to the anesthesia apparatus 1. It is also possible that the receiving device 100 according to the invention is located completely inside the anesthesia apparatus 1.

In one embodiment, the anesthesia apparatus 1 only causes residual gas to be ejected via lines 6 and 8.

In a further embodiment, a suction pump 10, which is fluidically connected to the discharge line 8, sucks residual gas from the holding device 100. The suction pump 10 can preferably be switched on and off and generates a volume flow which is remote from the filter unit 4 and passes through the discharge line 8. In the illustrated implementation, the suction pump 10 is positioned in front of the wall W and is fluidly connected to the lead-out line 8. In another embodiment, the suction pump 10 is located in or behind the wall W and is in fluid connection with the fluid receptacle 7 and is also in indirect fluid connection with the outlet line 8 via the fluid receptacle 7.

In this embodiment of the suction, the volume flow, i.e. the volume flowing through the discharge line 8 per unit time, is constant over time or follows another predetermined course over time. An optional volume flow sensor 9 measures the volume flow in the lead-out line 8, i.e. the volume per unit time. In one embodiment, the suction pump 10 is controlled, for example, by a control device of the receiving device 100 as a function of the measured values of the volume flow sensor 9, so that the actual volume flow through the outlet line 8 is equal to the desired, predetermined volume flow. The actual volume flow in the outlet line 8 is thus automatically regulated.

In a further embodiment, a pressure sensor, not shown, measures the pressure in the discharge line 8 or upstream of the discharge line 8, preferably also at a measuring point upstream of the filter unit 4 described below. As soon as the measured pressure exceeds a predetermined pressure limit, the suction pump 10 is activated and the residual gas is sucked into the discharge line 8. The suction pump 10 remains activated until the measured pressure drops below the pressure limit again.

The residual gas ejected from the anesthesia apparatus 1 and sucked away may contain O2, N2O and/or anesthetic agents. Accordingly, the remaining gas is guided to the accommodating device 100 according to the present invention. The receiving device 100 is fluidically connected in a fluid-tight manner to the anesthesia apparatus 1 via the supply line 6 and to a fixed fluid receptacle in the form of a gas receptacle 7 via the discharge line 8. The gas container 7 is arranged on and partly behind the wall W and belongs to a hospital infrastructure. Preferably, the connection between the anesthesia apparatus 1 and the delivery line 6 and the connection between the discharge line 8 and the gas holder 7 can be released and subsequently established again.

The remaining gas is led through the filter unit 4. The delivery line 6 leads from the anesthesia apparatus 1 to the filter unit 4. The lead-out line 8 leads from the filter unit 4 to the gas container 7. The gas receiver 7 receives the filtered gas, which flows through the outlet line 8. The filters 11, 20 of the filter unit 4 filter out undesired components, in particular the or each anesthetic agent, from the residual gas. Preferably, the containing device 100 is designed such that the residual gas is forcibly guided through the filter unit 4 and cannot bypass the filter unit.

Since the gas container 7 contains the filtered residual gas after undesired components have been filtered from the residual gas, it is prevented in many cases that a relevant amount of undesired gas components, for example O2, N2O and/or anesthetic agents, enter the hospital infrastructure or hospital rooms or are ejected into the environment of the hospital. The first event (anesthetic agent in a hospital infrastructure or room) is undesirable because escaping gas (particularly anesthetic agent) may harm the health of people in the room, and O2 may additionally damage equipment. The second event is undesirable because environmental emissions should be kept small.

In the embodiment shown subsequently, the delivery line 6 connects the filter unit 4 with the medical device 1. It is also possible that the filter unit 4 can be releasably coupled directly to the medical device 1, for example by two corresponding coupling elements. This embodiment saves on the delivery line 6 outside the medical device 1.

In the design described later, the filter unit 4 comprises a filter receptacle in the form of a tank 13 which is rotationally symmetrical with respect to a central axis, which is arranged vertically in use. The approximately cylindrical filter can be installed in the tank 13 from above and taken out again from the tank 13. Alternatively, the lid 42 may be placed onto the tank 13 from above and removed again. The filters 11, 12 also belong to the filter unit 4.

In one embodiment, the tank 13 includes a filter sensor 47 that determines whether the filter 11, 20 is installed in the tank 13. For example, the contact switch of the filter sensor 47 closes an electric circuit when the filter 11, 20 is installed, or the contact switch interrupts such an electric circuit when the filter 11, 20 has been installed. Or the installed filter 11, 20 interrupts the grating. This embodiment makes it possible to generate a warning and to output the warning in a human-perceptible form if no filter 11, 20 is installed in the tank 13 for a period of time greater than a preset time limit. In a development of this embodiment, the warning is output only when it is additionally determined that the gas mixture flows through the feed line 6 and/or into the filter unit 4.

Fig. 2 to 17 show a plurality of possible embodiments of the receiving device 100, in which a buffer store described below is arranged between the filter cartridge and the tank 13 in the filter unit 4. Like reference numerals have the same meaning. Fig. 2 to 7, 10, 11 and 14 to 17 show the filter unit 4 in a side view, with the middle axis of the filter unit 4 lying in the drawing plane. Fig. 9 shows the filter unit 4 in a cross-sectional view in the plane a-a of fig. 4 to 7, wherein the middle axis of the cylindrical filter unit 4 is perpendicular to the drawing plane of fig. 9. Fig. 20 to 24 show different embodiments, in which the buffer store is arranged outside the tank 13, and in which the filter unit 4 is likewise shown in a side view. It is also possible that the containing device 100 has a buffer storage in the tank 13 and a buffer storage outside the tank 13.

In the embodiment shown, the filter unit 4 comprises:

the actual filter 11 for anesthetic agent, which is subsequently referred to as "filter element" or also "anesthetic agent filter",

a cylindrical filter cartridge 20, which preferably completely and hermetically surrounds the anesthetic filter 11, except for the openings described subsequently,

a circumferential projection 12 on the upper part of the filter cartridge 20,

a cylindrical canister 13, which houses the filter cartridge 20 with the anesthetic filter 11 and has a bottom 44 and a peripheral side,

a tank transfer line 16, which is connected fluid-tightly with the transfer line 6, directs the transferred residual gas from the opening 22.1 towards the bottom 44 of the tank 13, and ends in the outlet opening 14,

a tank outlet line 32, which is connected in a fluid-tight manner to the outlet line 8, guides the residual gases escaping from the anesthetic filter 11 towards the outlet line 8, starting in the inlet opening 35 or in the level of the bottom 39 of the filter cartridge 20 and leading to the opening 22.2,

a measurement probe 15 that measures a measure of the amount of anesthetic agent below or within the lower region of the anesthetic filter 11,

a consumption display 17, which shows, in particular, when the filter cartridge 20 with the anesthetic agent filter 11 has to be replaced, and

a measurement line 18 leading from the measurement probe 15 to the consumption display 17.

Subsequently, the component comprising the filter element 11 and the filter cartridge 20 is referred to simply as "filter 11, 20" or also simply as "anesthetic agent filter 11, 20". In one embodiment, the filter element 11 and the filter cartridge 20 form a single component, which can only be replaced in its entirety. It is also possible for the filter elements 11 to be inserted into the filter cartridge 20 and in turn removed from the filter cartridge 20, so that the same filter cartridge 20 can be used successively for different filter elements 11.

The filter element 11 for anesthetic agents preferably has the shape of a cylinder and is preferably designed as a rigid body, which particularly preferably consists of or contains activated carbon. The filter element 11 may also comprise a zeolite. When the filters 11, 20 are mounted in the tank 13, the median axis of the cylinder is arranged vertically and lies in the plane of the figures of fig. 2 to 7, 10, 11, 14 to 24 and 26 and is perpendicular to the plane of the figures of fig. 9. Particularly preferably, the filter element 11 is designed as a monolithic piece made of activated carbon with a plurality of parallel channels. The filter element 11 thus designed exerts less aerodynamic resistance and is very light compared with other filters having similar filtering performance. However, such a filter element 11 is sensitive to mechanical action and can in particular be broken relatively easily. Such filter elements made of activated carbon and having channels are described, for example, in DE 102015012410 a 1.

The filter cartridge 20 protects the filter element 11 to some extent against mechanical damage. The filter cartridge 20 preferably likewise has the shape of a cylinder, the central axis of which preferably coincides with the central axis of the filter element 11, and has a cover 42, a bottom 39 and a peripheral side 43 extending between the cover 42 and the bottom 39. The cover 42 and the peripheral side 43 are impermeable to fluids, except for optional openings as described further below. The bottom 39 is also impermeable to fluids in one design and permeable to fluids in another design. Preferably, the filter cartridge 20 is made of a hard plastic or metal. Preferably, at least one guide element (not shown) is arranged externally to the filter cartridge 20, corresponding to a corresponding guide element inside the wall of the tank 13. Two corresponding guide elements ensure that the filter 11, 20 is correctly (in the correct rotational position) mounted in the tank 13.

In one embodiment, the filter 11, 20 comprises a data memory 92, which is preferably fastened to the outside of the filter cartridge 20 and is designed, for example, as an RFID chip or a bar code. The data memory 92 stores information about the filters 11 and 20. A reading device, not shown, of the housing apparatus 100 can read this information. In a preferred embodiment, the reading device is a reading and writing device, i.e. is also able to write information on the data memory 92.

Preferably, the data memory 92 stores an explicit identification of the filter 11, 20. The flag distinguishes the filter 11, 20 from all other filters used in the hospital. In an embodiment, the reading device reads in an unambiguous flag and stores in a central data memory (not shown) which filter 11, 20 is currently in fluid connection with which anesthesia apparatus or other medical apparatus of the hospital. The information is updated as needed.

In general, the filter 11, 20 should be or can be used only in a single container 100 until it is consumed and then cannot be used or can be reused only after being put into service. Undesired reuse can be prevented, for example, by evaluating the data memory 92 just described. In the preferred embodiment, the data memory 92, on the contrary, contains information, for example in the form of a logo, as to whether the data memory 92 and thus the filter 11, 20 to which the data memory 92 is fixed have been installed in the receiving device 100. The data memory 92 of the new filter 11, 20 contains information that the filter 11, 20 has not been installed. The reading and writing device reads this information after the filters 11, 20 have been installed. If the filters 11, 20 have been installed in the receiving device 100 in advance, the reading and writing means generate corresponding messages. Furthermore, it stores on the data storage 92 the information that the filter 11, 20 has now been installed in the containing device 100. Preferably, the read and write device generates a failure message if the read and write device cannot find the data memory 92 after installing the filters 11, 20, or cannot read the data memory 92. In the case of a bar code, the reading device reads in, for example, the unequivocal marking of the filter 11, 20 and subsequently renders the bar code 92 unreadable, for example by spraying a liquid or painting or gluing.

In one embodiment, the information about when the filter 11, 20 with the data memory 92 is first installed in the tank 13 of the receiving device 100 can be stored on the data memory 92 and can be read again. The date of installation is not stored in the new filter 11, 20. The reading and writing device stores data, optionally the point in time at which the filters 11, 20 are installed into the tank 13. The information can then be read again in order to know how long the filter has been used in the tank 13. In some cases the maximum service time of the filter 11, 20 is preset. In other implementations, the bar code 92 contains information of when to manufacture the filters 11, 20. The reading device reads in the date of manufacture and subsequently renders the bar code unreadable.

The design with the date of installation just described can also be used to prevent multiple sequential installations of the same filter 11, 20. If the read and write device has revealed an earlier installation date in the data memory 92 in the just installed filter, the filters 11, 20 have been used earlier and the read and write device generates a corresponding message. If the bar code 92 is not readable, a fault message is also output.

In one embodiment, information about which anesthetic agents the filter element 11 can be used for and/or information about which anesthetic agents the filter element cannot be used for are stored in the data memory 92. The reading device reads information from the data storage 92. Preferably, the reading device is in data connection with the anesthesia apparatus 1 and transmits information about permitted or not permitted anesthetic agents of the currently used filter element 11 to the anesthesia apparatus 1. Information about which anesthetic agent is currently used is stored in a data memory inside the anesthesia apparatus 1, for example, on the basis of user input. The anesthesia apparatus 1 automatically checks whether the filter element 11 is allowed for the or each currently used anesthetic agent. In the case of an unallowable filter element 11, the anesthesia apparatus 1 generates a corresponding fault message in a human-perceptible form.

The tank 13 is connected in a fluid-tight manner to the feed line 6 and the discharge line 8. The material of which the walls of the tank 13 are made is impermeable to fluids and is not chemically attacked by the anesthetic. Preferably, the walls of the tank 13 are made of hard plastic or metal.

When the filter cartridge 20 is mounted in the tank 13 correctly and in particular in the correct rotational position, in the design the outlet opening 14 of the tank feed line 16 overlaps the inlet opening 25 in the filter cartridge 20. The inlet opening 35 overlaps the outlet opening 34 in the filter cartridge 20. Two openings 14, 35 are located near the bottom 44 of the canister 13 and two openings 25, 34 are located in the peripheral side 43 and near the bottom 39 of the filter cartridge 20. The residual gas can flow into the filter element 11 through the inlet opening 25 in the filter cartridge 20 and again out of the filter element 11 through the outlet opening 34 in the filter cartridge 20. The anesthetic agent filter 11, 20 causes a forced guidance of the gas flowing through the anesthetic agent filter 11, 20, so that the remaining gas flows through the anesthetic agent filter 11, 20 in a relatively long path from the inlet opening 25 to the outlet opening 34.

In the embodiment shown in fig. 5, an overpressure valve 50 is arranged on the supply line 6, wherein the overpressure valve 50 is in fluid connection with the supply line 6. An overpressure valve 50 is located upstream of the filter unit 4. The overpressure valve 50 is closed or open in relation to the difference between the pressure in the delivery line 6 and the pressure in the environment surrounding the delivery line 6. As long as the pressure difference is below a preset overpressure limit, the overpressure valve 50 is closed. As soon as the pressure difference reaches or exceeds a predetermined overpressure limit, the overpressure valve 50 opens automatically or is opened and a fluid connection between the supply line 6 and the environment is established. The remaining gas can escape to the environment. Preferably, the overpressure valve 50 closes again automatically or is closed as soon as the pressure difference is again below the overpressure limit.

In a simple mechanical implementation, the overpressure valve 50 comprises a valve plate 51 which is located on an upwardly open valve port 52. The ratio between the weight of the valve plate 51 and the area of the upper opening of the valve port 52 determines the overpressure limit obtained. The pressure of the gas above the overpressure limit lifts the valve plate 51 from the valve port 52 so that the gas can escape. Gravity in turn lowers the valve plate 51.

Fig. 6 shows a modification in which the excess pressure valve 50 is likewise used, but the excess pressure valve 50 does not discharge the remaining gas into the environment. Conversely, the overpressure valve 50 is connected in parallel with the filter unit 4. An overpressure valve 50 is located in the interior of the tank 13 and there on or near the end of the tank transfer line 16. When the pressure difference in the tank transfer line 16 is above the overpressure limit, gas escapes from the tank transfer line 16 through the overpressure valve 50 into the tank 13. A hose 64, which is only schematically illustrated, guides the residual gas escaping from the overpressure valve 50 in the event of an overpressure through the filter unit 4 to the outlet line 8. The hose 64 may be at least partially disposed within the interior of the tank 13.

In one embodiment, the measuring probe 15 measures a measure of the amount of anesthetic agent that is not contained by the filter element 11 and therefore leaves the filter 11, 20. Preferably, the measurement probe 15 is located downstream of the filter unit 4 and measures the concentration of the or at least one anesthetic agent in the gas flow around the probe 15. Ideally, the anesthetic filter 11, 20 filters and holds the entire anesthetic agent from the gas flowing through. If the amount of anesthetic agent not sucked by the filter element 11 or otherwise contained is above a preset limit, this indicates that the filter element 11 is filled with anesthetic agent, or is blocked, cannot contain additional anesthetic agent and therefore must be replaced. In an embodiment, the measurement probe 15, the measurement line 18 and the consumption display 17 belong to the filter cartridge 20. The same filter cartridge 20 may be used for a plurality of filter elements 11 in sequence. It is also possible that the measuring probe 15, the measuring line 18 and the consumption display 17 are located separately from the filter cartridge 20.

In one embodiment, the filter cartridge 20 is suspended in the tank 13, with the circumferential rim 12 being located above the upper edge of the tank 13. The two upper sealing elements 41 or the single circular sealing element 41 close the region between the upper edge of the can 13 and the circumferential edge 12. Preferably, a sealing ring or other suitable sealing element 41 is guided completely around the upper edge of the tank 13, so that the installed filter cartridge 20 is suspended in the tank 13 in a gas-tight manner. Because the filter cartridge 20 is suspended in the tank 13 and is not as high as the tank 13 in the embodiment, a gap is formed between the bottom 39 of the filter cartridge 20 and the bottom 44 of the tank 13, which belongs to a buffer storage described later. It is also possible that the filter cartridge 20 does not have a circumferential rim 12 and is not suspended in the tank 13 but stands on the bottom 44 of the tank 13.

In all embodiments, the filter unit 4 comprises a buffer reservoir 19 (according to the embodiments of fig. 2 to 11 and 14 to 19) or a rotatable buffer reservoir 70 (fig. 13) inside the rigid tank 13 or a rigid buffer reservoir 23 (according to the embodiments of fig. 20 to 23) on the supply line 6 or the discharge line 8, wherein the buffer reservoirs 19, 23, 70 are not only fluidically connected to the gas lines 6 and 8, but also to the environment and can receive and discharge fluid. The buffer reservoirs 19, 23, 70 contain gas escaping from the anesthesia apparatus 1 as long as the rate of inflow of fluid in the delivery line 6 is greater than the rate of outflow of fluid in the outlet line 8. When the fluid flow in the outlet line 8 is conversely greater than the fluid flow in the supply line 6, the buffer store 19, 23, 70 again outputs the contained gas. In particular when the patient P exhales, i.e. during an exhalation phase, typically more fluid flows out of the anesthesia apparatus 1 into the delivery line 6 than out of the delivery line 6. When the patient P inhales, i.e. in the inspiration phase, less fluid flows into the delivery line 6 than out.

The described embodiments of the buffer memories 19, 23, 70 can be combined. It is possible for the receiving device 100 according to the invention to have one, two or three of the different buffer memories 19, 23, 70 just described and/or two similar buffer memories.

In the embodiment, a rigid buffer reservoir 23 is located below the tank 13. The gas to be contained is generally heavier than air and descends through an opening 26 in the bottom 44 of the tank 13 into a buffer storage 23 located below the tank 13.

In the example of fig. 7, a preferably horizontal separating wall 53 separates the buffer memory 19 from the filter unit 4. The gas which flows through the filter unit 4 and is filtered therein and the remaining gas which escapes from the overpressure valve 50 reach the space 54 between the filter unit 4 and the separating wall 53. The gas from this space 54 reaches the buffer reservoir 19 through an opening in the separating wall 53 and then flows from the buffer reservoir 19 through the tank lead-out line 32 into the lead-out line 8.

In the embodiment of fig. 7, the measuring probe 15 is located in the space 54, i.e. downstream of the filters 11, 20, and measures the concentration of the anesthetic agent in the space 54. Concentrations above the preset limit have at least one of the following two reasons:

the filter unit 4 is blocked or otherwise consumed and can for this or other reasons no longer adequately filter the anesthetic agent from the flowing gas stream;

the pressure in the tank transfer line 16 is above the negative pressure limit and the overpressure valve 50 opens and outputs gas into the space 54 in the tank 13.

Both events require replacement of the filter unit 4. The display unit 17 signals to the user that the filter unit 4 is to be replaced.

Fig. 8 shows seven different possible implementations of the overpressure valve 50. The overpressure valve 50 in the embodiment according to fig. 4, 6 or 7 can be implemented with each implementation.

Fig. 8 a) shows the already described embodiment 50.1, in which the valve plate 51 is located on the valve port 52. The valve plate 51 is raised at a sufficiently large pressure so that gas can escape from the clearance between the raised valve plate 51 and the valve port 52. The ratio between the weight of the valve plate 51 and the area of the opening of the valve port 52 determines the overpressure limit.

The overpressure valve 50.2 according to fig. 8 b) additionally comprises a pressure spring 55, which is supported on the housing of the overpressure valve 50 and which acts in an effort to press the valve plate 51 upward against the force of gravity. Preferably, the valve plate 51 is designed more heavily than in the embodiment according to fig. 8 a). The overpressure limit is additionally determined by the spring constant of the compression spring 55. The overpressure valve 50.2 according to fig. 8 b) opens only when a pressure above the overpressure limit exists for a sufficiently long time. Thus relieving short-term pressure spikes. The risk of leakage in the overpressure valve 50 is reduced. Such overpressure valves are described for example in US 8997741B 2.

In the overpressure valve 50.3 according to fig. 8 c), the valve plate 51 is replaced by a valve ball 56, which is located on the valve port 52. The overpressure limit is in turn determined by the ratio between the weight of the valve ball 56 and the area of the valve port 52.

The overpressure valve 50.4 according to fig. 8 d) comprises a valve cover 57 which is fixed to the valve port 52 and can be rotated relative to the valve port 52 about a horizontal axis of rotation perpendicular to the drawing plane of fig. 8. The overpressure rotates the valve cover 57 away from the valve port 52, against gravity, to form an opening at the free end of the valve port 52. Gravity and optionally a traction spring, not shown, strive to keep the valve cover 57 in the closed position. Alternatively, an optional drag spring is dedicated to pulling the valve cover 57 into the open position against gravity and remains in the open position. The relatively heavy valve cover 57 connected to the optional tension spring leads in particular to the overpressure valve 50.4 opening only when the overpressure is present for a sufficiently long time. Short-term pressure fluctuations are mitigated.

The overpressure valve 50.5 according to fig. 8 e) comprises a U-shaped tube 58, in which a liquid 59 is located in the lower part. The liquid 59 evaporates only when the temperature is above the temperature at which the overpressure valve 50 is installed and stored. If the pressure reaches or exceeds the overpressure limit, the gas escapes from the tube 58 in the form of bubbles. This embodiment reduces the risk of gas escaping undesirably through leaks particularly well.

The overpressure valve 50.6 according to fig. 8 f) comprises a controllable on-off valve 61 and a pressure sensor 60 in the feed line 52 to the controllable on-off valve 61. The signal of the pressure sensor 60 is further directed to an electrical comparator or processor. If the comparator or processor or also the pressure sensor 60 itself detects an event that the pressure in the supply line 52 is above the overpressure limit, the comparator or processor or also the pressure sensor controls the switching valve 61 and thus the switching valve opens. If the pressure drops again below the overpressure limit, the comparator or the processor or also the pressure sensor closes the switching valve 61 again. Optionally, the signal for the measured pressure and/or the information that the overpressure limit is exceeded is further directed to an output unit, not shown, preferably in combination with a sign of the position of the overpressure valve 50.6 in the hospital. The output unit outputs the measured pressure or message in a form that can be perceived by a human. The output unit can be arranged spatially remote from the receiving device 100, for example in a control center.

In the overpressure valve 50.7 according to fig. 8 g), a duckbill 65 is placed on the valve opening 52. In the event of a pressure above the overpressure limit, the duckbill 62 opens and closes again under a lower pressure.

Two undesirable events that may cause harm to the patient P must be prevented:

a backflow occurs in the supply line 6, for example because the filter element 11 contains four anesthetic agents and is therefore either partially blocked by liquid, or because the anesthesia apparatus 1 currently ejects relatively large amounts of gas into the supply line 6. The backflow may propagate into the anesthesia apparatus 1 and act on the breathing cycle;

the residual gas is sucked away from the anesthesia apparatus 1 via the supply line 6 and the discharge line 8, for example because the anesthesia apparatus 1 currently ejects relatively little gas into the supply line 6.

The overpressure valve 50 described with reference to fig. 4 to 8 prevents an overpressure that may occur, for example, on the basis of a backflow. In order to prevent two undesired events, in one embodiment, the buffer reservoir 19 is fluidically connected to the environment via at least one opening 21, preferably a plurality of openings 21, in the wall of the tank 13. When there are multiple openings 21, a fluid connection is also maintained if one opening 21 is blocked (e.g. because an object is being sucked). The embodiment in which the at least one opening 21 is embedded in the wall of the buffer reservoir 19 is particularly relevant in connection with suction, i.e. the suction pump 10, which sucks gas into the discharge line 8, see fig. 1. If the residual gas reaches the buffer reservoir 19 only by the anesthesia apparatus 1 blowing out the residual gas, i.e. if no suction is performed, the buffer reservoir 19 preferably has no continuous fluid connection to the environment.

It is possible to provide the overpressure valve 50 and the opening 21 in the wall of the tank 13, or also only the overpressure valve 50 or only the opening 21. By way of example, the openings 21 are shown in fig. 2 to 4, 10, 11 and 14 to 17, and the overpressure valve 50 is shown in fig. 5 to 7.

As already mentioned, in an implementation, the buffer reservoir 19 is in fluid connection with the environment in the rigid tank 13 through at least one opening 21. In an implementation, a rigid buffer reservoir 23 below tank 13 or downstream tank 13 is fluidly connected to the environment through at least one opening 24. Through the openings 21 or 24, residual gas can flow back and forth between the buffer reservoirs 19, 23 and the environment. This is illustrated in fig. 2 to 24 by dashed arrows.

In a modification, an overpressure valve 50 is arranged in front of or on the position of the opening 24 in the wall of the buffer reservoir 23, which then opens or is opened when the difference between the pressure in the buffer reservoir 23 and the ambient pressure is above a preset overpressure limit. The overpressure valve 50 may be constructed as described with reference to fig. 8.

Fig. 20 to 24 show a design with a rigid buffer reservoir 23 which is fluidically connected to the environment via an opening 24 or an overpressure valve 50, in the case of an overpressure valve 50 of course only when the valve is open. It is also possible for the rigid buffer reservoir 23 to be fluidically connected to the elastic buffer reservoir 70 via the opening 24, i.e. to a buffer reservoir with a variable volume. The elastic buffer memory 70 can be constructed as described with reference to fig. 13.

Fig. 11 shows an alternative or also a complement to the design, i.e. the interior of the tank 13 is always in fluid connection with the environment via the opening 21. An alternative approach reduces the amount of anesthetic agent that escapes from the canister 13. Furthermore, the subsequently described alternative results in the pressure in the tank 13 not exceeding a preset negative pressure limit below the pressure in the environment surrounding the tank 13. Too large a negative pressure is generally undesirable, since it may suck gas away from the anesthesia apparatus 1. The embodiment described below to avoid too large a negative pressure in the tank 13 is particularly relevant in conjunction with suction, i.e. the suction pump 10, which sucks gas into the discharge line 8. If the tank 13 has at least one opening 21, an undesirable underpressure may in particular occur when the or each opening 21 is blocked. The consumed or clogged filter 11, 20 can likewise lead to too great a negative pressure during suction.

The negative pressure valve 80 covers the opening 21 in the peripheral side wall of the tank 13. The negative pressure valve 80 opens when there is a negative pressure in the tank 13 that is greater than the negative pressure limit, i.e. when the pressure in the tank 13 exceeds the negative pressure limit below the ambient pressure. Otherwise, the negative pressure valve 80 is closed. The opening 21 limits the maximum volume flow into the tank 13. The opening may belong to a negative pressure valve 80.

In one embodiment, a warning is shown on a spatially remote warning unit or is output in another manner as soon as the negative pressure valve 80 is opened. The warning is output, for example, in the control center. In response to the warning, the user may verify the canister 13.

Fig. 12 shows seven different possible implementations of the negative pressure valve 80 of fig. 11. Fig. 12 shows exemplarily a portion of the peripheral side wall of the tank 13 and the covered opening 21. Each of the illustrated embodiments of the vacuum valve 80 corresponds to the embodiment of the overpressure valve 50 illustrated in fig. 8. In fig. 12, the same reference numerals have the same meanings as in fig. 8.

In the embodiment according to fig. 2 to 17, the feed line 6 opens into a tank feed line 16, which is guided vertically or obliquely along the inner wall of the tank 13 and has an outlet opening 14 near the bottom 39 of the filter cartridge 20. There is an inlet opening 25 in the peripheral side surface 43 and near the bottom 39 of the filter cartridge 20. The residual gas escaping from the anesthesia apparatus 1 flows through the delivery line 6 and the opening 22.1 in the tank 13 into the tank delivery line 16. The gas is generally heavier than air. Thus, the remaining gas ejected flows downward in the tank transfer line 16 arranged vertically or obliquely. The remaining gas ejected flows through the gas lines 6 and 16 until reaching the outlet opening 14 and enters the anesthetic filter 11, 20 through the inlet opening 25. The residual gas is ejected from the medical device 1 and/or sucked in by the suction pump 10 and passes through the filter element 11, wherein the residual gas is forcibly guided over a preferably serpentine-shaped path, thereby filtering the anesthetic agent from the gas. The filtered residual gas escapes from the outlet opening 34, from the filter cartridge 20, flows into the tank outlet line 32 through the inlet opening 35, and enters the outlet line 8 through the opening 22.2 in the tank 13 and from there into the gas holder 7.

In the embodiment according to fig. 2 to 17, the buffer reservoir 19 is formed by the gap between the inner wall of the tank 13 and the outer wall of the filter cartridge 20. The gap 19 is adjacent to the peripheral side and the bottom 44 of the can 13.

Fig. 13 shows three possible implementations of a buffer store 70, which is fluidly connected to the transfer line 6 and is arranged in series with the filter unit 4 and upstream of the filter unit 4. In all implementations, the buffer memory 70 is constructed of an elastomeric material. Ambient pressure acts on the buffer memory 70 from the outside. When a sufficient amount of gas flows into the feed line 6 and thus a sufficiently large pressure prevails in the buffer store 70, the elastic buffer store 70 expands, i.e. if the difference between the pressure in the feed line 6 and the ambient pressure is greater. When the pressure decreases, the elastic buffer store 70 contracts again and thus in turn discharges the contained gas into the supply line 6.

It is also possible for the elastic buffer reservoir 70 to be fluidically connected to the outlet line 8. It is also possible for a first elastic buffer reservoir 70 to be fluidically connected to the feed line 6 and for a second elastic buffer reservoir 70 to be fluidically connected to the discharge line 8.

According to the embodiment according to fig. 13 a), the supply line 6 has a connection 71, which is preferably arranged below the supply line 6 or the discharge line 8 and points downwards (anesthetic agent is heavier than air). A buffer store 70 in the form of an elastic bag 70.1 is suspended from a connecting piece 71. At high pressure, gas flows from the supply line 6/discharge line 8 via the connection 71 into the bag 70.1 and inflates the bag. In the event of a pressure reduction, the bag 70.1 contracts again and the contained gas is again discharged into the supply line 6/discharge line 8. Preferably, the connector 71 has a standard diameter of 22 mm. A bag originally provided or designed for manual breathing may preferably be used as bag 70.1, since such a manual breathing bag is already standardized and allows for medical use.

In the embodiment according to fig. 13 b), a section of the conveying line 6 or the discharge line 8 is completely or at least partially surrounded by a buffer store 70 in the form of an elastic bag 70.2. This section of the feed line 6 or the discharge line 8 has holes or other openings so that the bag 70.2 is in fluid connection with the feed line 6 or the discharge line 8. The elastic bag 70.2 completely covers the opening in the feed line 6 or the discharge line 8. The elastic bag 70.2 expands again under high pressure and contracts under low pressure.

In the embodiment according to fig. 13 c), the elastic buffer store 70 has the shape of a bellows 70.3, which is fluidically connected to the supply line 6 or the discharge line 8 via a connection 72. The bellows 70.3 expands along the longitudinal axis under high pressure and contracts again under lower pressure. The bellows 70.3 can be located above or below or to the side of the feed line 6 or the discharge line 8.

In the embodiment according to fig. 20 and 21, the buffer store 23 is formed by a separate buffer store, which preferably comprises a bellows. The inlet opening 30 is disposed in the upper third of the filter cartridge 20 and the outlet opening 34 is disposed in the bottom 39 of the filter cartridge 20. The buffer reservoir 23 is fluidly connected to the tank 13 via an opening 26. Opening 26 overlaps with outlet opening 34. Due to the outlet opening 34 in the bottom 39 of the filter cartridge 20, the buffer reservoir 23 is also in fluid connection with the anesthetic filter 11, 20. Furthermore, the buffer reservoir 23 is in fluid connection with the outlet line 8 and with the environment via an opening 24. The return duct leads from opening 26 to opening 24.

The remaining gas that is ejected flows through the delivery line 6 and reaches the inlet opening 30 in the filter cartridge 20 from the side. The residual gas flows from top to bottom through the anesthetic filter 11, 20 and escapes again from the anesthetic filter 11, 20 in the outlet opening 25. As soon as the suction pump 10 sucks in gas, this gas is sucked back out of the buffer store 23 via the outlet line 8. The buffer memory 23 operates according to the principle LastIn-FirstOut. The meander shape of the buffer memory 23 enables a long tube in a relatively small size. The long tube reduces the mixing of the remaining gas of the spray with the ambient air.

The filter element 11 contains the anesthetic agent and is thereby gradually clogged and/or saturated. If the filter element 11 is to a large extent clogged or saturated and therefore no longer able to accommodate further anesthetic agent, or if the filter element is swollen, the filter element 11 or the entire anesthetic filter 11, 20 must be replaced. In many cases, an optional waste display 17 shows the event. The filter cartridge 20 with the filter element 11 and the display units 16, 17, 18 is removed from the tank 13. Fig. 3, 10 and 15 show the situation after removal of the filter cartridge 20. During the replacement of the filter cartridge 20 with the filter element 11, the artificial respiration of the patient P cannot be interrupted. Thus, a fluid connection between the anesthesia apparatus 1 and the gas holder 7 is maintained. Also, the escape of large amounts of sprayed gas to the environment is prevented when no filter cartridge 20 is installed in the tank 13.

In the embodiments according to fig. 2 to 10, this is achieved pneumatically, i.e. in that the residual gas is sucked in, in the embodiments according to fig. 14 to 17 mechanically, i.e. by the elastically mounted plate 31, in the embodiments according to fig. 20 and 21 and 24 by the meandering shape of the buffer store 23, and in the embodiments according to fig. 22 and 23 by the combination of the elastically mounted plate 31 and the meandering shape of the buffer store 23. The elastic buffer reservoir 17 of fig. 13 also prevents, to a certain extent, a large amount of anesthetic from escaping into the environment when the filter cartridge 20 is replaced.

In the pneumatic solution according to fig. 2 to 10, residual gas accumulates in the gap 19 between the tank 13 and the filter cartridge 20. If a suction pump 10 is present, this gas is sucked off from the bottom 44 of the tank 13 via the lead-out line 8. The inlet opening 35 to the tank lead-out line 32 preferably has a larger cross-sectional area than the entire cross-sectional area of the opening 21 in the tank 13. When the volume flow through the feed line 6 fluctuates over time, it is therefore also possible in particular for only a small portion of the residual gas to escape from the tank 13 upwards and through the opening 21 into the environment. The tank 13 itself acts as the or a buffer reservoir.

Preferably, the gas is guided through the filter unit 4 by means of forced guidance. The forced guidance is subsequently explained with reference to fig. 4 to 10 (pneumatic solution) and fig. 14 to 19 (mechanical solution).

Mounted to the inside of the filter 11, 20 is a wall 38 which is impermeable to the fluid. The wall 38 preferably extends parallel to the median axis of the filter 11 at a distance and preferably has the shape of a plane that is flat or curved along a vertical axis. The wall 38 divides the filter cartridge 20 and thus the filter element 11 in the filter cartridge 20 into a raised area Au and a lowered area Ab for the gas, see fig. 9. The elevated regions Au and the lowered regions Ab each have the shape of a circular arc segment, viewed in the viewing direction parallel to the central axis of the filters 11, 20. The elevated area Au is in fluid connection with the inlet opening 25. In this implementation, the bottom 39 of the filter cartridge 20 is permeable to gas, at least in the drop zone Ab, acting as an outlet opening and thus replacing the outlet opening 34 in the peripheral side 43. The fall-down region Ab opens into the permeable bottom 39.

The gas from the conveying line 6 is forced to be guided through the filter unit 4 as follows: as in the other embodiments, gas is ejected from the medical device 1 and/or sucked into the outlet line 8. The gas flows through the canister feed line 6 and the outlet opening 14 and the inlet opening 25 into the elevated area Au, which is located between the wall of the filter cartridge 20 and the vertical wall 38. There is a gap between the wall 38 of the filter cartridge 20 and the cover 42. The gas passes from the rise region Au through the gap to the fall region Ab without leaving the can 13. Gas flows through the drop zone Ab to the passable bottom 39 and then through the tank lead-out line 32 to the lead-out line 8. The gas is preferably filtered both in the elevation region Au and also in the fall region Ab, but at least in the fall region Ab.

The two lower sealing elements 40 or the circumferential sealing ring 40 prevent the gas sucked in from the tank feed line 14 from bypassing the space between the bottom 39 of the filter cartridge 20 and the bottom 44 of the tank 13 of the filter cartridge 20. This gas flows past the filters 11, 20 and is therefore not filtered, which is undesirable.

In the mechanical solution according to fig. 14 to 19 and 22, the plate 31 is supported near the bottom 44 of the tank 13. The plate 31 switches the gas path according to whether the filter cartridge 20 is installed or removed. In a preferred design, the plate 31 occupies the entire cross-sectional area of the tank 13, except for the tank gas lines 16 and 32 and the unavoidable clearances. The plate 31 divides the inner space of the tank 13 into a filter hollow space 36 and a buffer reservoir hollow space 37. The filter hollow space 37 is located above the plate 31 and is capable of accommodating and enclosing the filters 11, 20. The buffer memory empty space 36 is located between the plate 31 and the bottom 44 and belongs to a buffer memory, which will be described later. Preferably, a circumferential sealing ring 40 surrounds the peripheral face of the plate 31.

The transfer line 6 is fluidly connected to the installed filter cartridge 20 via the canister transfer line 16 and the opening 14. The outlet line 8 is fluidly connected to the installed filter cartridge 20 through the opening 35 and the tank outlet line 32. The plate 31 is movable back and forth between a parking position (fig. 14, 16, 18, 22) and a buffer memory position (fig. 15, 17, 19). When the filter cartridge 20 is installed, the plate 31 is in the parking position and the filter cartridge 20 is in fluid connection with the delivery line 6 and the outlet line 8, respectively, or only with the outlet line 8 (fig. 22). The plate 31 and the sealing ring 40 prevent the gas from flowing from the supply line 6 to the outlet line 8, bypassing the filter cartridge 20. When the filter cartridge 20 is removed, the plate 31 is in the buffer storage position and the buffer storage empty space 36 is in fluid connection with the feed line 6 and the outlet line 8, respectively. The sealing ring 40 prevents or at least reduces the risk of gas escaping from the buffer reservoir hollow space 36 upwards and into the environment.

The design of how the plate 31 moves is described later. This embodiment results in a particularly simple mechanical design. A plurality of spring elements 33 are supported on the bottom 44 of the tank 13 and strive to press the plate 31 upwards, i.e. away from the bottom 44 of the tank 13, against the force of gravity and into the buffer storage position and hold it therein. When the filter cartridge 20 is installed in the tank 13, the plate 31 is pressed downwards into the parking position against the spring force of the spring element 33. This effect is caused by the weight of the filter cartridge 20, or by the user squeezing the filter cartridge 20 down in the canister 13. When the filter cartridge 20 is removed again, the spring element 33 presses the plate 31 upwards into the buffer storage position until the plate 31 reaches the end below the tank gas lines 16 and 32. The plate 31 in combination with the optional sealing ring 40 largely prevents the escape of residual gas from the tank 13 up to the environment. It is possible that a not shown blocking unit holds the plate 31 in position.

Fig. 18 and 19 show further embodiments of the mechanical solution of the buffer store 19. The same reference numerals have the same meanings as in fig. 14 to 17. The plate 31 in turn divides the inner space of the tank 13 into a filter hollow space 37 and a buffer reservoir hollow space 36. The plate 31 thereby separates the buffer memory 19 from the installed filters 11, 20. The buffer reservoir 19 is in turn located between the plate 31 and the bottom 44 of the tank 13. In the embodiment according to fig. 18 and 19, no opening 21 is embedded in the wall of the tank 13. This embodiment is preferably used in applications without the suction pump 10.

The slide 48 inside the tank 13 is fixedly connected to the plate 31 and can be moved up and down together with the plate 31 between a buffer storage position (fig. 19, without the filters 11, 20 installed) and a parking position (fig. 18, with the filters 11, 20 installed in the filter hollow space 37 in the tank 13). The spring element 33 strives to move the plate 31 and the slide 48 together upwards into the buffer memory position. The weight of the installed filter 11, 20 and optionally the user installing the filter 11, 20 presses the plate 31 and thus the slide 48 downwards into the parking position against the spring force of the spring element 33. Optionally, the plate 31 snaps into the parking position.

On the lower end of the tank transfer line 16, two outlet openings 14 and 14.1 are arranged, which are subsequently referred to as filter outlet openings or buffer reservoir outlet openings. The filter outlet opening 14 is located above the buffer memory outlet opening 14.1. If the filters 11, 20 are properly installed (fig. 18), the filter outlet opening 14 overlaps the inlet opening 25 of the canister 20 as in the previous embodiment. The filter outlet opening 14 of the tank transfer line 16 opens into the inlet opening 25 of the filter 11, 20. The slide 48 pressed downward releases the filter outlet opening 14 and closes off the buffer reservoir outlet opening 14.1. If no filter 11, 20 is installed and the slide 48 is in the buffer store position (fig. 19), the tank feed line 16 is fluidly connected to the buffer store 19 via the buffer store outlet opening 14.1. The buffer memory outlet opening 14.1 leads to a buffer memory 19. The slide 48 pressed upward releases the buffer outlet opening 14.1 and closes the filter outlet opening 14.

The corresponding applies to the tank lead-out line 32. A buffer storage inlet opening 35.1 is attached to the lower end of the tank lead-out line 32 below the filter outlet opening 35. If the filters 11, 20 are installed and the slide block 48 is in the parking position, the filter inlet opening 35 overlaps the outlet opening 34 of the filter cartridge 20. The outlet opening 34 of the filter 11, 20 opens into a filter inlet opening 35 of the tank lead-out line 32. The downwardly pressed slide 48 releases the filter inlet opening 35 and closes off the buffer memory inlet opening 35.1. If no filter 11, 20 is installed, the tank outlet line 32 is fluidly connected to the buffer reservoir 19 via the buffer reservoir inlet opening 35.1. The buffer reservoir 19 leads to a buffer reservoir inlet opening 35.1 of the tank lead-out line 32. The slide 48 pressed upwards releases the buffer inlet opening 35.1 and closes the filter inlet opening 35.

If the plate 31 and the slide 48 are in the parking position (fig. 18), the gas flows through the tank feed line 16 and the openings 14 and 25 into the filter element 11 and subsequently through the openings 34 and 35 into the tank outlet line 32. The slider 48 prevents gas from entering the buffer reservoir 19. If the plate 31 and the slide 48 are in the buffer store position (fig. 19), the gas flows through the tank feed line 16 and the opening 14.1 into the buffer store 19 and through the opening 35.1 into the tank outlet line 32. The plate 31 largely prevents gas from escaping upwards from the buffer reservoir 19.

Fig. 22 and 23 show an embodiment which combines the spring-mounted plate 31 of fig. 14 to 17 and the buffer store 23 of fig. 20 and 21 and likewise comprises the tank conveying line 16. In the case shown in fig. 22, the filter cartridge 20 having the filter element 11 is installed, and in the case shown in fig. 23, the filter cartridge is removed. A sealing element or ring 40 is fixed to the plate 31. Furthermore, a further circumferential sealing ring 40 is fixed in the interior of the tank 13. The tank transfer line 16 and the bracket 45 hold the sealing ring 40 in place.

The plate 31 is in the parking position in fig. 22 and in the buffer memory position in fig. 23. When the plate 31 is in the parking position, the circumferential webs below the plate 31 contact the base 44 and prevent gas from the supply line 6 from flowing below the plate 31 through into the outlet line 8. Thereby preventing gas from bypassing the anaesthetic filter 11, 20. Conversely, the gas flows through the opening 22.1 and is first conducted in the gap between the tank 13 and the filter cartridge 20 up through the tank feed line 16 to the inlet opening 25, then through the filters 11, 20 and to the outlet opening 34. The gas flows into the outlet line 8 through the opening 22.2.

When the filter cartridge 20 is removed and the plate 31 is in the buffer storage position (fig. 23), the sealing element 40 on the plate 31 and the sealing ring 40 inside the tank 13 prevent the undesired event that gas flows from the buffer storage hollow space 36 up beside the plate 31 and escapes into the environment. Conversely, the plate 31 and the tank 13 largely separate the buffer reservoir hollow space 36 from the environment.

In this modification, the opening 26 is also embedded in the bottom 44 of the tank 13, and the tank 13 is fluidly connected to a rigid buffer reservoir 23, comprising a bellows, through the opening 26. The inlet opening 25 of the filter cartridge 20 is disposed adjacent the lid 42 of the filter cartridge 20 and the outlet opening 34 is disposed adjacent the bottom 39 of the filter cartridge 20. The measurement probe 15 and the measurement line 18 are arranged near the lid 42 of the filter cartridge 20. When the filter cartridge 20 is installed into the canister 13, the plate 31 is pressed downward against the force of the spring 33, and thus gas is guided into the filter cartridge 20. When the filter cartridge 20 is removed, the spring 33 presses the plate 31 upward without crimping the plate 31. When the filter cartridge 20 is installed, gas can flow around the plate 31 into the buffer reservoir hollow space 36 and from there into the buffer reservoir 23 and back again, thereby fulfilling the function of a buffer reservoir.

Fig. 24 shows a design in which a rigid buffer reservoir 23 is arranged downstream of the filter unit 4 and is in fluid connection with the outlet line 8. The designation "downstream" relates to the direction of flow of the gas in front of the medical device 1 to the fluid receptacle 7. The buffer storage 23 may also be arranged upstream of the filter unit 4 and be fluidly connected to the transfer line 6.

The embodiment according to fig. 24 makes it possible to design the filter unit 4 smaller and/or the filters 11, 20 larger than in the embodiments according to fig. 2 to 19 and fig. 22 and 23, since there is no need for a hollow space between the filter cartridge 20 and the tank 13, which space acts as a buffer reservoir. Furthermore, the vertical dimension is smaller compared to the previously described embodiments. The export line 8 leads through a buffer memory 23. The buffer store is also indirectly in fluid connection with the transfer line 6 via the filter unit 4. The volume flow sensor 9 and the suction pump 10 are preferably located downstream of the buffer store 23.

In the embodiment according to fig. 24, the buffer store 23 is arranged downstream of the filter unit 4. In the modification shown in fig. 13, the filter unit 4 is likewise arranged upstream or downstream of the elastic buffer store 70. In this modification, an optional volume flow sensor 9 and a suction pump 10 are preferably also arranged downstream of the filter unit 4.

The embodiments described thus far include a measurement probe 15 that measures a measure of the amount or concentration of anesthetic within the filter cartridge 20. The event of a quantity or concentration above a predetermined anesthetic agent limit shows that the filter element 11 no longer filters out sufficient anesthetic agent from the gas flow flowing through. In response to the detection event, a warning is output on the consumption display 17. When the overpressure valve 50 is open, a warning is preferably also output. A possible reason for the overpressure valve 50 to open is that the filter element 11 is blocked, for example because the filter element 11 swells on account of moisture.

The or a consumption display 17 may be arranged on the filter unit 4 or the tank 13. It is also possible for the consumption display or warning unit to be arranged spatially at a distance, for example in a control center. When the measuring probe 15 detects a high concentration of anesthetic agent or when the overpressure valve 50 is open and therefore the filters 11, 20 need to be checked and replaced when needed, a warning is shown in the control center.

An alternative embodiment avoids the necessity of providing a measuring probe 15 for the amount or concentration of anesthetic agent inside the tank 13. Instead, the amount of anesthetic agent flowing through the delivery line 6 to the anesthetic filter 11, 20 is approximately determined. According to a possible embodiment, the respective current volume flow into the delivery line 6, i.e. the volume per unit time of the gas ejected into the delivery line 6 by the anesthesia apparatus 1, is measured at a plurality of successive sampling points in time. Or otherwise determine the current volume flow. Furthermore, it is approximately measured or determined in another way what concentration the anesthetic agent in the gas flow currently has. From the two values, a volume flow of anesthetic agent is calculated, which flows through the feed line 6 in the filter unit 4 at a specific sampling time and is ideally completely accommodated by the filter element 11. The integration is carried out numerically on these values for the anesthetic volume flow. This approach provides an approximation of the number of anesthetic filter elements 11 that have heretofore been accommodated. The approximation calculated in this way can be greater than the actually accommodated quantity, in particular when the overpressure valve 50 is temporarily opened, or when at least one leak occurs between the anesthesia apparatus 1 and the filter 11, 20.

In an alternative embodiment, the measurement of the quantity of liquid anesthetic in the anesthetic tank 49 is repeated, for example, by means of a float in the tank 49. This amount decreases over time as anesthetic from the canister 49 is added to the carrier gas. The part of the anesthetic agent leaving the canister 49 is added to the carrier gas, e.g. by evaporation, and enters the delivery line 6. The amount of anesthetic agent that has heretofore left the canister 49 is an upper limit of the amount that the filtering element 11 of anesthetic agent has heretofore been contained.

The two just described designs can be combined, in particular in order to reduce inaccuracies.

Preferably, the value of the contained quantity is set to zero when a new filter 11, 20 is installed in the tank 13. The filter 11, 20 for example comprises a data carrier 92, for example an RFID chip, wherein the data carrier 92 is preferably arranged on the outer wall of the filter cartridge 20. The receiving device 100 comprises read and write devices, for example RFID read and write devices, for such data carriers. In an alternative embodiment, the user enters information by means of a stationary or portable computer or by means of another input unit, i.e. a new filter 11, 20 is installed in the tank 13.

In the embodiment, a predetermined concentration is determined, which is set at the anesthetic vaporizer 2, see fig. 1. In a further embodiment, the actual concentration of the anesthetic agent is measured at least one measuring point in the anesthesia apparatus 1.

The anesthetic vaporizer 2 typically comprises a reserve tank 49 for anesthetic agent in liquid state. In one embodiment, the filling state sensor measures a measure for the amount of liquid anesthetic agent in the tank, for example by means of a float. The quantity of anesthetic agent in liquid state that has been vaporized up to now is derived from the measured values of the filling state sensor. The amount that has been vaporized to date is an upper limit of the amount that the filter element 11 of anesthetic agent can accommodate to date.

In one embodiment, the anesthesia apparatus 1 ejects the anesthetic agent into the delivery line 6 only during the expiration phase. Therefore, only those values at the sampling time points in the expiratory phase are considered when calculating the anesthetic amount. Such a method is described, for example, in DE 102006027052B 3. In a further embodiment, the supply of breathing air or other fresh air is very large, so that the anesthesia apparatus 1 also ejects the anesthetic agent during the inspiration phase.

In one embodiment, information is stored on a data memory, for example the data memory 92 described immediately above on the outer wall of the filter cartridge 20, as to how much anesthetic agent the filter element 11 can maximally hold. This number is preset. The comparator repeatedly compares the amount of anesthetic agent that the filter element 11 has received so far and that has been approximately calculated as just described with the preset and stored maximum acceptable amount of the filter element 11. As soon as the actually received quantity differs from the preset and stored maximum quantity by less than a preset limit of absolute value or percentage, a warning is output in a human-perceptible form, for example on a spatially remote output unit, the output unit being located in particular in the control center.

Fig. 25 shows an exemplary embodiment, in which corresponding components are supplemented with respect to the arrangement of fig. 1. Like components have the same reference numerals as in fig. 1. Additionally shown are:

a filling state sensor 89, which measures a measure for the current filling state in the anesthetic tank 49 and which for example comprises a float and/or a level (Waage) on the surface of the anesthetic in the tank 49,

a volume flow sensor 90, which belongs to the anesthesia apparatus 1 and measures the volume flow of gas, i.e. the volume per unit time, the anesthesia apparatus 1 ejects gas into the delivery line 6,

a concentration sensor 91 which measures the concentration of the anesthetic agent which is set on the anesthetic vaporizer 2 and/or which the anesthetic vaporizer 2 actually obtains,

a data memory 92 of the filters 11, 20 of the filtering unit 4, and

an anesthetic quantity determiner 93 that processes the data.

In fig. 25, a non-return valve 65 is shown, which is arranged between the anesthesia apparatus 1 and the receiving device 100, i.e. upstream of the delivery line 6. The check valve 65 allows the passage of gas from the anesthesia apparatus 1, but prevents the flow of gas from the delivery line 6 into the anesthesia apparatus 1.

The gas from the fluid reservoir 7 cannot flow into the anesthesia apparatus 1 in particular.

In the example shown in fig. 25, information about the maximum number that can be accommodated by the anesthetic filter element 11 is stored on the data memory 92. The maximum amount can be expressed as the volume of the anesthetic in gaseous or liquid state, or also as its weight.

The anesthetic agent quantity determiner 93 receives the measurement values of the sensors 89, 90 and 91 and information on the maximum quantity of the data storage 92. As just described, the anesthetic agent amount determiner 93 calculates a measure of the amount of anesthetic agent accommodated so far by the filter element 11, compares the amount accommodated so far with the maximum amount, and outputs a warning when the amount accommodated so far approaches the maximum amount of the filter element 11.

In one embodiment, the anesthetic quantity determiner 93 is implemented in the anesthesia apparatus 1, which is illustrated in fig. 25. It is also possible that the anesthetic quantity determiner 93 is implemented on a separate computer, for example a smartphone.

The design allows for the possibility that the same filter element 11 can accommodate different anesthetics in succession or also simultaneously. For example, it is possible to use the receiving device 100 in different operations one after the other, in which different anesthetics are used. It is also possible that the containment device 100 is used in one operation, wherein a mixture of a plurality of anesthetic agents is used.

According to this embodiment, the data memory 92 stores information about the maximum number of reference anesthetic substances that can be accommodated by the filter element 11. Furthermore, a scaling factor is stored for each anesthetic agent in which the filter element 11 can be used, namely on the data memory 92 or on a further data memory. The filter element 11 is able to contain a maximum amount of anesthetic agent, which is equal to the product of the conversion factor and the maximum amount of reference anesthetic agent.

The anesthetic agent quantity determiner 93 receives, in use, the measured values of the sensors 90 and 91 and the data storage 92, information on the maximum quantity of the reference anesthetic agent, a scaling factor and information on which anesthetic agent is used in which period, respectively. The anesthetic quantity determinator 93 is, for example, in data connection with the anesthesia apparatus 1, and the anesthesia apparatus 1 transmits information to the anesthetic quantity determinator 93 which anesthetic is currently used and thus which anesthetic flows or can flow through the filter element 11.

As just described, the anesthetic agent quantity determiner 93 calculates, for each anesthetic agent used, how much quantity of anesthetic agent the filter element 11 has so far contained. The anesthetic quantity determinator 93 converts the quantity of anesthetic contained thus far into a corresponding quantity of reference anesthetic for each possible anesthetic, based on the inverse of the conversion factor. The anesthetic quantity determiner 93 adds up the respective quantities of reference anesthetic and calculates therefrom an equivalent contained total quantity of reference anesthetic. The filter element 11 is consumed and must be replaced when the sum of the equivalent amounts reaches or exceeds the maximum amount of reference anesthetic agent.

In many cases, how much anesthetic agent the filter element 11 can accommodate depends not only on the type of anesthetic agent, but additionally on the conditions of use. In one embodiment, the just described scaling factor for the anesthetic is additionally dependent on at least one subsequently measurable use condition:

the temperature, pressure and/or humidity of the gas flowing through the filter element 11,

-the concentration of the anesthetic agent in the gas,

-the temperature, pressure and/or humidity of the surrounding air.

In one embodiment, a warning that the filter element 11 is almost or completely consumed is output in the form of a signal light. Green means that the number actually accommodated is larger than a preset distance below the maximum number. Yellow means that the actual contained quantity is still below the maximum quantity, but less than the preset distance. Red means that the actual contained quantity reaches or exceeds the maximum quantity. In a further embodiment, the hitherto contained amount of anesthetic is output as a percentage of the maximum possible amount of anesthetic, for example separately for each anesthetic.

The design just described uses information about the maximum possible number of filter elements 11 currently used for anesthetic agents that can be accommodated. In one embodiment, information about the maximum number is stored on the data memory 92 of the installed filter 11, 20. The reading device of the receiving apparatus 100 is capable of reading the data memory. In a further embodiment, the reading device reads in which type of filter 11, 20 is installed. For each possible type of filter unit 4, the respective maximum amount of anesthetic agent that can be accommodated by that type of filter unit is stored in a data memory.

In one embodiment, the read and write device stores information on the data memory 92 for each anesthetic used, how much anesthetic the filter unit 11 has received so far. Preferably, the information is continuously updated. This information can then be used to again groom the filter element 11 and/or to obtain the anesthetic agent contained by the filter element 11. The process steps in cleaning the filter element 11 can be related to the type and amount of anesthetic agent to be contained.

Optionally, information about the hitherto contained amount of reference anesthetic is additionally stored on the data memory 92 or on a central data memory. This information is preferably continuously updated, resulting in a time-varying course of the consumed amount of the reference anesthetic. The time-dependent course enables an approximate prediction of the remaining service life of the filter element 11.

In one embodiment, the quantities stored to date are stored for each anesthetic agent on the data memory 92 or on a central data memory. Preferably, the storage is re-implemented after each operation or other installation of the filter 11, 20. The number received so far is read or otherwise determined before or at the beginning of the operation. The difference between the number of accommodations after and before operation provides a measure of consumption during operation.

In all of the embodiments described so far, the filter unit 4 comprises a single filter element 11, optionally in a filter cartridge 20. Fig. 26 shows an exemplary embodiment in which the filter unit 4 has two filter elements 11.1 and 11.2 in each filter cartridge 20.1, 20.2. Like reference numerals have the same meaning as in the previous drawings.

The two filters 11.1, 20.1 and 11.2, 20.2 are mounted in two corresponding receptacles of the receiving unit 71, the receiving unit 71 having the shape of a resolver receptacle and being rotatable about a rotational axis 73. The horizontal axis of rotation 73 is rotatably connected to the peripheral side wall of the tank 13 and lies in the plane of the drawing of fig. 26. Thereby, optionally, the filter 11.1, 20.1 or the filter 11.2, 20.2 can be brought into a position between the outlet opening 14 on the lower end of the tank transfer line 16 and the lower end of the tank lead-out line 32. Thereby, the filter 11.1, 20.1 or the filter 11.2, 20.2 is selectively in a position in which the gas flows through the supply line 6, the filter 11.1, 20.1 or 11.2, 20.2 and the discharge line 8. In the case shown in fig. 26, the gas can flow through the filters 11.1, 20.1, while the filters 11.2, 20.2 are in the parking position.

The receiving unit 71 is preferably snapped into place when it is in a position relative to the tank 13 in which the inlet opening 25 of the filter 11.1, 20.1 or 11.2, 20.2 overlaps the outlet opening 14. The risk of gas flowing past the filter element 11.1 or 11.2 is thereby reduced.

It is possible for the user to manually rotate the containing unit 71 about the axis 73. In another embodiment, an optional motor 72 can rotate the containment unit 71 relative to the tank 13 about an axis 73. In one embodiment, the motor 72 can be controlled from the outside or activated by a user input, for example, by a button press. A controlled or activated motor 72 causes the containing unit 71 to rotate further around a position. This can also result from an external control or activation in that the filter 11.1, 20.1 or the filter 11.2, 20.2 is selectively located in the position through which the gas flows.

In an implementation, the control device receives the above-mentioned measurement values of the measurement probe 15 in the tank 13 and is able to control the motor 72. As soon as the measuring probe 15 measures a high concentration of anesthetic agent, the control device controls the motor 72 and the motor 72 rotates the receiving unit 71 further around a position.

In one embodiment, the two filters 11.1, 20.1 and 11.2, 20.2 are constructed similarly and are able to filter out one and the same anesthetic agent or several same anesthetic agents from the gas flowing through. When the filter is consumed, the accommodation unit 71 is rotated manually or by the motor 72. In a further embodiment, the filter element 11.1 is able to filter out a first anesthetic agent and the filter element 11.2 is able to filter out a second anesthetic agent. Depending on which anesthetic agent is currently to be filtered out of the gas flow, the filter 11.1, 20.1 or the filter 11.2, 20.2 is brought into a position in which the inlet opening 25 overlaps the outlet opening 14.

It is naturally possible that the receiving unit 71 comprises receiving portions for more than two filters. It is also possible that the containing unit 71 is not rotatable relative to the tank 13, but moves linearly or pivots.

In the alternative, containment device 100 includes an adapter (Weiche) disposed between transfer line 6 and tank 13. The adapter selectively directs the gas flowing through the supply line 6 to the first filter 11.1, 20.2 or the second filter 11.2, 20.2 or optionally a third filter, not shown.

In the embodiments described so far, the receiving device 100 according to the invention is connected to a single medical device 1. Fig. 27 shows two alternative embodiments, in which the same receiving device 100 according to the invention is connected or connectable to two medical devices 1 and 1.1. The same reference numerals have the same meaning as in the preceding embodiments.

In the embodiment according to fig. 27 a), the receiving device 100 can be connected selectively to the medical device 1 or the medical device 1.1. The line 6.1 leads from the medical device 1 to an adapter 96, which belongs to the receiving device 100. The line 6.2 likewise leads from the medical device 1.1 to the adapter 96. In the position shown in fig. 27 a), the adapter 96 establishes a fluid connection between the line 6.1 and the delivery line 6. The adapter 96 can be adjusted into a position in which it establishes a fluid connection between the line 6.2 and the delivery line 6.

In the embodiment according to fig. 27 b), the receiving device 100 comprises a Y-shaped part 97 instead of the adapter 96. The two sides of the Y-shaped element 97 are connected to the two lines 6.1 and 6.2. The beam of the Y-shaped member 97 is connected to the transfer line 6. Due to the Y-shaped part 97, two medical devices 1 and 1.1 are simultaneously connected with the receiving device 100 according to the invention.

In the embodiments described so far, the receiving device 100 is connected to a fixed fluid receptacle 7 in the wall W. Fig. 28 shows two alternative embodiments, in which the receiving device 100 is connected or connectable selectively or also simultaneously to the fixed fluid receptacle 7 or the further fixed fluid receptacle 7.1.

In the embodiment according to fig. 28 a), the adapter 98 selectively connects the outgoing line 8 to the line 8.1 or to the line 8.2. The line 8.1 leads to the fluid receptacle 7 and the line 8.2 leads to the further fluid receptacle 7.1. In the position shown in fig. 28 a), the filter unit 4 is connected to the fluid receptacle 7 via lines 8 and 8.1.

In the embodiment according to fig. 28 b), the two sides of the Y-shaped part 99 are connected to the two lines 8.1 and 8.2. The beam of the Y-piece 99 is connected to the lead-out line 8. The filter unit 4 is thereby simultaneously in fluid connection with the two fluid receptacles 7 and 7.1. Due to this embodiment, if the fixed fluid receptacles 7, 7.1 are defective or cannot individually accommodate the total amount of gas to be ejected, then the gas is also accommodated.

List of reference numerals

1 an anaesthetic apparatus comprising an anaesthetic evaporator 2, a mixer 29, a scale filter 3 and a fan unit 5

2 anesthetic vaporizer in an anesthesia apparatus 1, comprising an anesthetic tank 49

3 Scale Filter which filters CO2 from exhaled air

A 4-filter unit for filtering the anesthetic agent from the gas output by the anesthetic device 1, comprising an activated carbon filter 11 in a cartridge 20, a cartridge 20 and a tank 30, connected to the delivery line 6 and the outlet line 8

5 Fan Unit of an anesthesia apparatus 1 which moves gas in a breathing cycle

6 conveying line leading from the anesthesia apparatus 1 to the filter unit 4

6.1, 6.2 lines connecting the adapter 96 or the Y-piece 97 with the medical devices 1 and 1.1

7 fixed gas-containing part of the hospital infrastructure, contained by the wall W, connected to the filtering unit 4 by a lead-out line 8

7.1 additional fixed gas-containing part, contained by wall W

8 lead-out line leading from the filter unit 4 to the gas container 7

8.1, 8.2 lines connecting the adapter 98 or the Y-piece 99 to the gas holders 7 and 7.1

9 volumetric flow sensor in the outlet line 8

A suction pump 10 on the discharge line 8 or in the fluid reservoir 7 is in fluid connection with the discharge line 8

11 the cylindrical activated carbon filter of the filter unit 4, acting as a filter element, is surrounded by a filter cartridge 20

11.1, 11.2 cylindrical filter element in receiving unit 7.1

12 surrounding projection of the filter cartridge 20, resting on the upper edge of the pot 13

13 tank into which the feed line 6 leads and from which the lead-out line 8 leads out, acting as a filter holder

An outlet opening of the 14-tank transfer line 16, arranged on the lower end of the tank transfer line 16, overlaps with the inlet opening 25 in the installed state of the filter cartridge 20

14.1 buffer store outlet opening of the tank transfer line 16, arranged below the outlet opening 14, in fluid connection with the buffer store 19 when no filter 11, 20 is installed

15 measuring probe for measuring the state of the activated carbon filter 11

16 tank transfer line inside the tank 13, forming a fluid-tight continuation of the transfer line 6, leading the gas from the transfer line 6 to the bottom 44 of the tank 13, ending in the outlet opening 14

17 consumption display for activated carbon filter 11

18 signal lines from the measuring probe 15 to the consumption display 17

19 buffer reservoir in the form of a gap between the tank 13 and the filter cartridge 20

20 cylindrical cartridge, enclosing an activated carbon filter 11, comprising a surrounding protrusion 12, carrying a data memory 92

20.1, 20.2 cylindrical filter cartridge for a filter element 11.1, 11.2

21 opening in the tank 13, connected to the environment

22.1 opening in tank 13 where transfer line 6 ends

22.2 opening in tank 13 where lead-out line 8 ends

23 buffer memory in the form of a fret tube with an opening 24

24 opening of the buffer memory 23, establishing a connection with the environment

25 near the inlet opening of the bottom 39 or cover 42 of the cartridge 20 overlap the outlet opening 14 with the filters 11, 20 installed

26 opening of the buffer storage 23, connected to the inlet opening 25

27 inspiratory gas line for supplying respiratory air to a patient P

28 expiratory gas line for sucking away the respiratory air exhaled by the patient P

29 mixer of an anesthesia apparatus 1 for generating a carrier gas for an anesthetic

30 inlet opening in cover 42 of filter cartridge 20

31 elastically supported plate, close to the bottom 44 of the tank 13, dividing the tank into a filter hollow space 37 and a buffer reservoir hollow space 36

32 tank 13, conducting gas from the bottom 44 of the tank 13 to the lead-out line 8

33 spring elements supported on the bottom 44 of the tank 13 and tending to press the plate 31 upwards away from the bottom 44

34 outlet opening, close to the bottom 39 of the cartridge 20, overlapping the inlet opening 35 in the mounted condition of the filters 11, 20

35 inlet opening of the tank outlet line 32, in the installed state of the filter 11, 20, is in fluid connection with the outlet opening 34

35.1 buffer reservoir inlet opening of tank outlet line 32, in the case of removal of filters 11, 20, is in fluid connection with buffer reservoir 19

36 in the lower region of the tank 13, formed by the plate 31 and the walls and the bottom 44 of the tank 13, belong to a buffer reservoir separated from the filter hollow space 37 by the plate 31

37 filter hollow space in the upper region of the tank 13, capable of accommodating the filters 11, 20, separated from the buffer reservoir hollow space 36 by the plate 31

38 vertical separating walls inside the filters 11, 20, separating the raised areas Au from the lowered areas Ab

39 bottom of the filter cartridge 20

40 lower sealing element preventing gas flow from the tank transfer line 16 around the filter cartridge 20 to the tank lead-out line 32

41, between the upper edge of the tank 13 and the surrounding rim 12 of the filter cartridge 20

42 cover of the filter cartridge 20

43 peripheral side surface of the filter cartridge 20

44 bottom of tank 13

45 holding element for the lower sealing element 40

47 filter sensor in tank 13, which determines whether a filter 11, 20 is installed

48 slide block inside the can 13 connected to the plate 31

49 anesthetic can of anesthetic vaporizer 2

50 overpressure valve in the delivery line 6

50.1 realization of an overpressure valve 50, comprising a valve plate 51 and a valve port 52

50.2 realization of overpressure valve 50, including valve plate 51, valve port 52 and pressure spring 55

50.3 realization of overpressure valve 50, comprising valve plate 51 and valve ball 56

50.4 implementation of overpressure valve 50, comprising valve port 52 and valve cover 57

50.5 realization of an overpressure valve 50, comprising a U-shaped tube 58 with a liquid 59

50.6 realization of an overpressure valve 50, comprising a pressure sensor 60 and a controllable on-off valve 61

50.7 realization of overpressure valve 50, comprising valve port 52 and duckbill 62

51 a valve plate of the overpressure valve 50, which is arranged on a valve port 52

52 overpressure valve 50

53 separating wall in the tank 13, between the filter unit 4 and the buffer storage 19

54 space between the filter unit 4 and the separating wall 53

55 pressure spring, which strives to press the valve plate 51 upwards

56 ball valve, located on the valve port 52

57 valve cover rotatably connected with the valve port 52

58U-shaped tube in which a liquid 59 is located

59 liquid in tube 58

60 pressure sensor in the supply line to a controllable switching valve 61

61 controllable switch valve

62 duckbill piece positioned on the valve port 72

64 hoses connecting the excess pressure valve 50 to the outlet line 8

65 check valve in the discharge line 8, prevents gas from flowing back from the fluid reservoir 7 through the discharge line 8 into the anesthesia apparatus 1

70 elastic buffer storage on the conveying line 6

71 for the two filters 11.1, 20.1 and 11.2, 20.2, are designed as turret receptacles and can be rotated about an axis 73

A motor 72 capable of rotating the containing unit 71 about an axis 73

73 the axis of rotation of the containing unit 71, is rotatably connected to the tank 13

80 tank 13

89 fill state sensor measuring a measure for the current fill state in the anesthetic canister 49

90 volume flow sensor of an anesthesia apparatus 1, measuring the volume flow of gas which the anesthesia apparatus 1 emits into the delivery line 6

91 concentration sensor for measuring the concentration of anesthetic agent adjusted on the anesthetic evaporator 2 or actually obtained by the anesthetic evaporator 2

92 data memory of the filter 11, 20, on which information is stored about the maximum amount of anesthetic agent that can be accommodated by the filter element 11, the data memory in the design case being a bar code on the RFID chip or cartridge 20

93 an anesthetic agent quantity determiner, which obtains the measured values of the volume flow sensor 90, the concentration sensor 91 and information about the maximum quantity of the data memory 92, determines the quantity of anesthetic agent contained so far in the filter element, and compares the quantity contained so far with the maximum quantity.

96 adapter for selectively connecting the transmission line 6 to the line 6.1 or the line 6.2

97Y-piece, connecting lines 6.1 and 6.2 with feed line 6

98 adapter for selectively connecting the outgoing line 8 to the line 8.1 or the line 8.2

99Y-piece, connecting lines 8.1 and 8.2 and lead-out line 8

100, comprising a filter unit 4, a feed line 6, a discharge line 8, a volume flow sensor 9 and a suction pump 10

A drop zone in the Ab filters 11, 20 where gas in the cartridge 20 sinks down to the bottom 39

Elevated regions in the Au filters 11, 20 where the gas in the filter cartridge 20 rises up to the lid 42

P patient, connected to an anesthesia apparatus 1 and inhaling at least one anesthetic

A W wall accommodating the fixed gas accommodating portion 7.