Assembly with inhalation valve for a breathing system

Abstract

The invention relates to a component with an inhalation valve for a breathing system, the component comprising: an inhalation opening of the inhalation valve for the flow of breathing gas into a pressure chamber in order to provide breathing gas in the pressure chamber for breathing of a patient, a closing element of the inhalation valve, the closing element being movably arranged in order to close the inhalation opening for the flow in a closed position and to at least partially open it in an open position, a transmission device of the inhalation valve, the transmission device being connected to the closing element via a connecting element in order to keep the closing element in the closed position in an initial position of the transmission device, preferably thereby providing the inhalation valve as a normally closed inhalation valve for the breathing system, a control pressure source for providing a control pressure to the transmission device in a control pressure chamber in order to move the transmission device from the initial position by the control pressure.

Description

Technical Field

[0001] The invention relates to an assembly with an inhalation valve for a breathing system. The invention also relates to a breathing system and a method. Background Art

[0002] Different types of exhalation valves and inhalation valves are known from the prior art, which are used for the breathing of a patient. For this reason, exhalation valves are often used as so-called "normally closed" valves (also called: normally closed, NC) in order to adjust the so-called positive end-expiratory pressure (abbreviated: PEEP, positive end-expiratory pressure) during the exhalation phase when the patient breathes. Inhalation valves can also be designed as so-called "normally open" valves (normally open, NO), which are open during inhalation and closed during exhalation.

[0003] Furthermore, in order to regulate the flow of breathing gas to the patient, a control pressure can be generated by a pump, which actuates the inhalation valve.

[0004] However, a disadvantage of conventional solutions is that the adjustment of such an intake valve can be associated with a high level of technical effort.

[0005] Specifically, for example, in the case of faulty control, for example in the case of a pump failure, a permanent open state of the inhalation valve may occur. As a result, the flow of respiratory gas to the patient occurs unhindered without further safety measures. Summary of the invention

[0006] The invention is based on the following object, at least partially to reduce the disadvantages described above. In particular, an object is to provide an improved solution for breathing control or breathing regulation close to the patient, in which a simple and stable pressure regulation is achieved. In addition, an object can be to reduce the technical expenditure for the reliable operation of the inhalation valve.

[0007] The above-mentioned object is achieved by an assembly with the features of claim 1, a breathing system with the features of claim 11 and by a method with the features of claim 12. Further features and details of the invention are derived from the corresponding dependent claims, the description and the drawings. Features and details described in connection with the assembly according to the invention are of course also applicable in connection with the breathing system according to the invention and the method according to the invention, and vice versa, so that reference can always be made to each other with regard to the disclosure of the various aspects of the invention.

[0008] The task is solved in particular by a component, preferably a valve component, which is provided with (that is, has) an inhalation valve for a breathing system. Such an inhalation valve can be used to control the flow of a fluid during an inhalation process. To this end, the inhalation valve can have an inhalation opening in order to specifically control the flow of breathing gas into the pressure chamber, and so that the breathing gas in the pressure chamber can be used to make the patient breathe. In other words, the inhalation opening of the inhalation valve is arranged for the flow of breathing gas into the pressure chamber, so that breathing gas is provided in the pressure chamber for the patient's breathing. In addition, a closing element of the inhalation valve can be provided, which is movably arranged so that the inhalation opening for the flow is closed in a closed position and at least partially opened in an open position. Thus, the closed position can be used to prevent the flow, and the open position is correspondingly used to achieve the flow. The manipulation of the movement of the closing element from the closed position to the open position and / or vice versa can thus cause the control of the flow. However, the persistent existence of the open position, for example when a control failure occurs, can lead to a critical state if possible.

[0009] Furthermore, the assembly according to the invention can have at least one of the following components, in particular for preventing such a critical state:

[0010] - a (particularly mechanical) transmission means of the inhalation valve, which is connected to the closure element via a (particularly mechanical) connecting element in order to hold the closure element in the closed position in the initial position of the transmission means, preferably so that the inhalation valve is provided as a normally closed inhalation valve for the breathing system,

[0011] a control pressure source, such as a pump, for providing a control pressure for the transmission element in the control pressure chamber in order to move the transmission element from the starting position by (in particular increasing) the control pressure.

[0012] This can have the following advantages: when the control pressure source or control pressure fails, the closure element remains in the closed position according to the initial position of the transmission means. In other words, the intake valve can be "normally" (that is, in the initial position when the control pressure disappears) closed.

[0013] In this case, it is particularly provided that the transmission means is designed for a force-transmitting coupling of the pressure chamber with the closure element, so that when the chamber pressure in the pressure chamber increases, the closure element is moved outside the initial position of the transmission means and in particular against the control pressure in the direction of the closed position. Here, the advantage is also achieved that the closed position can be brought about not only by adjusting the control pressure, but also in the normal state, that is to say even when the control pressure disappears, and the inhalation valve is closed when the chamber pressure increases. Even when the closure element is in a partially open state (in the open position), it can be moved automatically into the closed position if necessary when the control pressure disappears or decreases, so as to automatically bring about at least a reduction in the throughflow of breathing gas into the pressure chamber.

[0014] The initial position of the transmission element is understood within the scope of the invention to be a state in which the transmission element is in the absence of an external energy supply, such as, for example, by a control pressure (in particular in addition to the normally present air pressure). Only when an additional force is applied, for example, by increasing the control pressure, can the transmission element be moved from the initial position and this movement is transferred to the closure element via the connecting element. In this case, the movement is implemented in particular as a deflection, for example, of a transmission element in the form of a diaphragm.

[0015] It can be provided that the transmission means is designed to separate the control pressure chamber from the pressure chamber, preferably in a fluid-tight manner. Thus, the transmission means has an additional functionality, namely in particular sealing the control pressure chamber. Thus, in other words, the transmission means can have a sealing function.

[0016] The advantage that an increased chamber pressure automatically leads to a reduction in the flow of respiratory gas into the pressure chamber can also be achieved by the assembly according to the invention. This reduction in the flow can counteract a further increase in the chamber pressure and can also achieve a reduction in the chamber pressure. This significantly simplifies the operation of the inhalation valve, in particular with regard to the regulation, in terms of technology. In this case, the chamber pressure is in particular specific to and / or corresponds to the patient's respiratory tract pressure.

[0017] In addition, the movement of the closure element in the direction of the closed position can possibly cause the closing of the inhalation valve to reduce or adjust the further flow of breathing gas. Conversely, the movement of the closure element in the direction of the open position can cause the opening of the inhalation valve to increase the further flow of breathing gas.

[0018] The present invention is also based on the following recognition, in particular, that although the conventional inhalation valve may also have full functionality, an excessively high chamber pressure leads to the opening of the inhalation valve. Because the chamber pressure can basically correspond to the airway pressure, this leads to an additional pressure build-up in the airway. Traditionally, the regulator must be technically expensive to permanently regulate this behavior based on the feedback of the chamber pressure and / or airway pressure and / or control pressure. Advantageously, according to the present invention, the inhalation valve can be constructed so that the increased chamber pressure applies the increased closing force to the inhalation valve. Thus, the increased chamber pressure in the inhalation valve leads to an increased closing of the inhalation valve, thereby preventing the increased pressure build-up of the chamber pressure by preventing further entry of the respiratory gas, and preferably even reducing the chamber pressure. Here, the chamber pressure can be understood as an equivalent to the control pressure for the inhalation valve. This further has the advantage that only a slow adjustment is required for a slow pressure adjustment or in extreme cases only a control is required without the chamber pressure or airway pressure feedback.

[0019] Advantageously, the regulation behavior of the inhalation valve corresponds to that of a self-stabilizing pressure regulator when a pressure increase in the chamber pressure in the pressure chamber causes the closing element to move into the closed position and thus causes a reduction in the inflow of breathing gas into the pressure chamber. The reduction in the inflow of breathing gas into the pressure chamber has the advantage that the increase in the chamber pressure is not further intensified by the breathing gas or can even be reduced. As a result, the expenditure for regulating the inhalation valve can be significantly reduced. For example, there is no need to actively regulate the opening of the closing element (movement in the direction of the open position) by means of a control pressure resistance. This is done automatically based on the pressure increase in the pressure chamber via the transmission device.

[0020] In order to achieve a higher dynamics of the inhalation valve with a wide opening or a higher possible volume flow, it may also be meaningful to actively open the opening of the inhalation valve more widely for an expected higher volume flow of the breathing gas. It may also be meaningful to close the inhalation valve quickly by reducing the control pressure when a target value for the chamber pressure is exceeded.

[0021] Advantageously, an exhalation valve used in conjunction with an inhalation valve can be designed in such a way that an increased chamber pressure leads to an opening of the exhalation valve, so that breathing gas escapes and the chamber pressure is thereby reduced.

[0022] Furthermore, within the scope of the invention, further advantages can be achieved if possible, in that the operation of the intake valve is technically significantly simplified with a normally closed intake valve. Advantageously, a self-stabilizing pressure regulator can also be constructed in this way, in which, in particular, an increased chamber pressure leads to an increased closing force on the intake valve, that is to say in particular on its closure element.

[0023] In this context, "normally closed" may mean within the scope of the invention that the valve is closed without an external energy supply, such as, for example, by a control pressure (in particular in addition to the normally present air pressure). The opening of the intake valve is only possible with the application of additional energy, for example, by increasing the control pressure for the intake valve.

[0024] It can be further advantageously provided that the transmission device further comprises:

[0025] - a first surface for being acted upon by the chamber pressure from the pressure chamber in order to transfer the increase in the chamber pressure into an increased force for moving the closure element in the direction of the closed position,

[0026] - a second side, which is acted upon by the control pressure from the control pressure chamber in order to transmit the increase in the control pressure into an increased force for moving the closing element in the direction of the open position,

[0027] In this case, the first surface and the second surface are preferably arranged opposite each other, in order to preferably transmit an increase in the chamber pressure and the control pressure as a mechanical deflection of the transmission means in opposite directions.

[0028] In other words, the force from the pressure chamber acting on the first surface due to the pressure increase of the chamber pressure in the pressure chamber is converted into a mechanical deflection of the transmission device and thereby (via the connecting element) into a movement of the closing element into the closed position, and the force from the control pressure chamber acting on the second surface due to the increase of the control pressure is converted (if possible also via the connecting element) into a movement of the closing element into the open position, so that in particular the control pressure and the chamber pressure or the suction duct pressure in the pressure chamber compete to provide a counter-movement of the closing element. It is possible that the surfaces have different sizes in order to adjust the influence of the control pressure and the chamber pressure to different degrees. For this purpose, for example, the first surface can be reduced relative to the second surface in such a way that the chamber pressure is prevented from being applied to the edge region of the transmission device (for example by sealing and / or bonding and / or the like in this edge region).

[0029] For example, it can be provided that the closure element has a closure element surface for closing the intake opening in the closed position, wherein the area ratio of the closure element surface to the first surface is in the range of 0.25 to 1, preferably in the range of 0.3 to 0.75, preferably in the range of 0.5 to 0.6. This area ratio can be varied in order to adapt the control behavior of the intake valve and / or in order to adapt to the pressure ratio. By selecting the ratio of the surfaces or areas, it can be ensured, for example, that the chamber pressure exerts a greater force on the first surface than on the closure element, which results in that, in the case of a higher chamber pressure, the closing function of the intake valve (movement of the closure element into the closed position) is fulfilled with an increased closing force.

[0030] In another feasible solution, it can be arranged that the area of ​​the second surface corresponds to the area of ​​the first surface or differs from the area of ​​the first surface by a maximum of 10%. As a result, the control pressure and the chamber pressure can cause the movement of the closing element in substantially the same manner. Alternatively, it is possible that the areas of the first surface and the second surface are different from each other, preferably differing by more than 10%. This can be achieved, for example, when the second surface has a larger area than the first surface, to increase the influence of the control pressure on the movement of the closing element. As a result, the following advantages are obtained, and a less powerful and / or smaller control pressure source or pump can also be used. This can also be achieved that the control pressure source or pump is preferably fixed to the suction valve (directly) via a coupling element, so that the assembly according to the present invention can be constructed in the form of a structural unit. Alternatively, the control pressure source can also be connected to the control pressure chamber via a hose (especially a pump hose).

[0031] According to another advantage, it can be provided that the transmission means is fixedly connected to the closure element via the connecting element in order to move the closure element from the open position into the closed position, preferably in the event of a pressure increase in the chamber pressure, in particular in the event of a pressure increase in the respiratory tract pressure (in the pressure chamber) due to an exhalation process, and to keep it closed in the closed position after the movement and / or in the initial position of the transmission means. In other words, the transmission means can be designed to convert a pressure increase in the chamber pressure into a force for moving the closure element, in order to apply this force to the closure element as an increased closing force, in particular when a pressure increase in the chamber pressure due to exhaled air from the patient in the pressure chamber is applied to the transmission means.

[0032] Furthermore, it is advantageous if the transmission means is designed in the form of a diaphragm, preferably in order to provide a movement of the closing element and, in particular, a force-transmitting connection by a mechanical deflection of the diaphragm as a function of the control pressure and / or the increase in the chamber pressure, wherein the diaphragm is preferably connected to the closing element via a connecting element in order to transmit the deflection to the closing element. In this case, the use of a diaphragm can provide a structurally simple and reliable feasibility for a force-transmitting connection between the pressure chamber and the closing element. As a result, the intake valve can be designed in such a way that an increased chamber pressure exerts an increased closing force on the intake valve via the diaphragm. The increased chamber pressure thus does not cause the intake valve to open (i.e., through the intake opening of the closing element), which could further increase the chamber pressure, but rather causes closing. As a result, the intake valve can independently regulate the chamber pressure and can increase safety during operation.

[0033] Furthermore, the diaphragm can be so flexible within the relevant pressure range, for example in a breathing system within a range of 0 mbar to approximately 100 mbar, that the middle of the diaphragm surface can be moved by the adjustment stroke required to open the closing element of the inhalation valve, for example by an adjustment stroke in a range of 0.1 mm to 3 mm (millimeters).

[0034] Furthermore, it is optionally possible within the scope of the invention that the transmission means is designed to provide the functionality of a normally closed intake valve in the initial position when the control pressure disappears, that is to say in particular when no control pressure is provided by a control pressure source or a pump. In this way, safety can be increased in a structurally simple manner and with little technical effort.

[0035] Advantageously, it can be provided in the present invention that the control pressure source is designed as a pump, and in particular the pump is designed as a piezoelectric pump, preferably in order to adjust the control pressure in the range of 0 mbar to 3 mbar, preferably to 0 mbar, during the patient's exhalation.

[0036] It can be provided within the scope of the invention that the control device is provided for automatically controlling and / or regulating the throughflow in order to determine the control pressure for moving the closure element in the direction of the open position and in order to provide the control pressure in particular in competition with the chamber pressure in the pressure chamber, so that the movement of the closure element is preferably dependent on the ratio of the control pressure to the chamber pressure. This has the advantage that the assembly can be safely and reliably adjusted for breathing.

[0037] Furthermore, the control device can optionally be designed to perform regulation in such a way that the intake valve opens particularly widely at the beginning of the intake process, so that a setpoint pressure and / or setpoint pressure difference in the pressure chamber can be quickly reached within the range of regulation. Instead of a pressure difference, a gas flow or a gas throughflow or a volume flow can also be mentioned, which causes a pressure difference when flowing through.

[0038] The pressure increase caused by coughing during inhalation can be quickly controlled, for example, by the inhalation valve being closed briefly by withdrawing the pressure in the control pressure chamber.

[0039] As an alternative to regulation, only control can optionally also be provided by the control device.

[0040] In particular for periodic control, the inhalation valve can be actuated periodically with a control pressure. In a first phase, that is to say during inhalation, the inhalation valve can be actuated, for example, with a control pressure in the range of 10 mbar to 30 mbar, in particular in the range of 15 to 25 mbar. In a second phase, that is to say during exhalation, the inhalation valve can be actuated with a lower control pressure than in the first phase, preferably with a control pressure of 0 mbar, that is to say the inhalation valve is in its "normal state", that is to say closed. The control can be used, if possible, without the regulation mentioned above. Alternatively, superposition with regulation is possible.

[0041] It can furthermore be advantageously provided that an auxiliary pressure chamber with a breathing opening is provided for conducting the provided breathing gas further to the patient, wherein the auxiliary pressure chamber is connected to the pressure chamber in fluid communication via the throttle opening, and wherein preferably at least one sensor arrangement is provided for detecting an actual pressure difference existing between the auxiliary pressure chamber and the pressure chamber, wherein the control device is designed to determine a control deviation between a setpoint pressure difference between the auxiliary pressure chamber and the pressure chamber and the detected actual pressure difference, in order to determine the control pressure as a function of the control deviation. As a result, the control can be further improved.

[0042] Likewise, the subject of the invention is a breathing system for breathing a patient with the aid of a breathing gas, comprising at least:

[0043] - a gas source for providing breathing gas;

[0044] - an assembly according to the invention with an intake valve, wherein the intake valve is preferably designed as a normally closed intake valve;

[0045] - An exhalation valve, which is preferably designed as a normally open exhalation valve.

[0046] The breathing system according to the invention thus entails the same advantages as it has been described in detail with reference to the assembly according to the invention.

[0047] Advantageously, the normally open exhalation valve is characterized in that it is closed by a (further) control pressure for the exhalation valve and is otherwise open when the (further) control pressure disappears.

[0048] The inhalation valve can optionally be used in a valve block for a breathing system, in particular for a breathing apparatus or an anesthesia apparatus. In this way, the assembly according to the invention can also be designed as a structural unit. A breathing system supplies breathing gas, for example, as a breathing gas mixture comprising oxygen and nitrogen, for example 79% by volume of nitrogen and 21% by volume of oxygen. In an anesthesia apparatus, anesthetic chemicals are also added to the breathing gas mixture.

[0049] Advantageously, the valve block forms a housing around the intake valve and protects the intake valve from contamination and other environmental influences. Important components of the intake valve may possibly be carried by the valve block.

[0050] In the present invention, it can be provided that the breathing system is designed in such a way that the increased pressure of the patient's exhaled air leads to an increase in the chamber pressure and thus to an increased closing force being exerted on the closure element. The closing function of the inhalation valve can thereby be intensified. The inhalation valve is closed, in particular, when the patient is exhaling when no control pressure is present. Coughing events during inhalation or also during exhalation can thus also lead to the closing of the inhalation valve or support the closing in addition to regulation (closed loop) or control (open loop).

[0051] Furthermore, it is possible for the intake valve to have a closing edge against which the closing element bears in the closed position of the intake valve.

[0052] The fluid, in particular the respiratory gas, which is introduced into the pressure chamber via the inhalation valve can have a pressure in the range of 30 mbar to 200 mbar, preferably in the range of 40 mbar to 150 mbar. The mentioned pressure ratios and the mentioned area ratios result in an optimal operating mode of the inhalation valve, wherein the pressure of the fluid to be introduced is counteracted when the inhalation valve is opened. For the self-stabilizing function of the inhalation valve, the pressure of the fluid to be introduced is important in that it also supports the closing.

[0053] Furthermore, a breathing opening of the valve block may be provided in order to introduce exhaled air into the pressure chamber and generate an airway pressure in the pressure chamber, wherein the airway pressure is preferably in the range of 30 mbar to 200 mbar. The airway pressure may also form (generate or influence) the chamber pressure.

[0054] The valve block can preferably have an exhalation valve, in particular a normally open exhalation valve, preferably an exhalation valve with a piezoelectric pump, which can be actuated within milliseconds and can thus be actuated rapidly. In particular, it can be provided that the exhalation valve is closed during inhalation. The exhalation valve can optionally be used in addition to the inhalation valve for regulating the pressure difference by detecting the actual pressure difference existing between one or the auxiliary pressure chamber and the pressure chamber by means of at least one sensor assembly, in particular when using a throttle, which is preferably arranged between the auxiliary pressure chamber and the pressure chamber.

[0055] The control device can have a processing unit, such as a microprocessor and / or a processor, in order to perform control and / or regulation. For this purpose, the processing unit can, for example, process program instructions of a control program and / or a regulation program.

[0056] The subject matter of the invention is also a method for operating an inhalation valve of a breathing system, in which the following steps are carried out:

[0057] - initiating a flow of breathing gas through an inhalation opening of the inhalation valve into the pressure chamber, in particular by means of a gas source, in order to provide breathing gas in the pressure chamber for breathing of the patient;

[0058] - providing a closing element of the intake valve, which is movably arranged in order to close the intake opening for the throughflow in a closed position and at least partially open it in an open position;

[0059] - providing an inhalation valve, in particular a mechanical transmission means, which is connected to the closure element via the inhalation valve, in order to hold the closure element in the initial position of the transmission means in the closed position, preferably thereby providing the inhalation valve as a normally closed inhalation valve for the breathing system;

[0060] - providing a control pressure source, preferably a pump, for providing a control pressure to a transmission device in a control pressure chamber so that the transmission device is moved from an initial position by the control pressure, in particular by increasing the control pressure; wherein the transmission device is configured as a force-transmitting connection between the pressure chamber and the closing element, so that when the chamber pressure in the pressure chamber increases, the closing element is moved outside the initial position of the transmission device and in particular in the direction of the closed position against the control pressure.

[0061] The method according to the invention thus entails the same advantages as it has been described in detail with reference to the assembly according to the invention. In addition, the method can be applied to operate the assembly according to the invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0062] Further measures to improve the invention are derived from the following description of some exemplary embodiments of the invention shown in the figures. All features and / or advantages including structural details and spatial arrangements derived from the claims, the description or the drawings may be important to the invention both per se and in various combinations.

[0063] In which respectively schematically:

[0064] Figure 1 A schematic diagram showing the components of an assembly according to the invention in an open position,

[0065] Figure 2 A schematic diagram showing the components of an assembly according to the invention in a closed position,

[0066] Figure 3 A schematic diagram showing components of a breathing system according to the invention,

[0067] Figure 4 A schematic diagram showing components of an assembly according to the invention,

[0068] Figure 5 A schematic diagram showing an exhalation valve of a breathing system according to the present invention is shown,

[0069] Figure 6 A schematic diagram showing components of a breathing system according to the invention,

[0070] Figure 7 shows the temporal course of the patient's breathing pressure, the position of the membrane of the inhalation valve and the position of the membrane of the exhalation valve,

[0071] Figure 8 shows an exemplary time profile of the manipulated variable for the control pressure of the inhalation valve and of the exhalation valve,

[0072] Fig. 9 shows a further exemplary time profile of the manipulated variable for the control pressure of the inhalation valve and of the exhalation valve,

[0073] Fig.10 A further exemplary time profile of the manipulated variable for the control pressure of the inhalation valve and of the exhalation valve is shown.

[0074] Elements with the same function and mode of action are respectively provided with the same reference symbols. DETAILED DESCRIPTION

[0075] exist Figures 1 to 3Components of an assembly 1 according to the invention are shown separately in FIG. The assembly 1 comprises an inhalation valve 10 for a breathing system 100. An inhalation opening 11 of the inhalation valve 10 is provided for a flow 301 of breathing gas 300 into a pressure chamber 110, so that the breathing gas 300 is provided in the pressure chamber 110 for breathing by the patient 200. In addition, a closing element 12 of the inhalation valve 10 is movably arranged so as to close the inhalation opening 11 for the flow 301 in a closed position 320 and to at least partially open it in an open position 310. The open position 310 is in Figure 1 Schematically shown in FIG, and the closed position 320 is Figure 2 It is schematically visualized in FIG.

[0076] exist Figure 4 and 6 3 shows the assembly 1 according to the invention in an open position 310 with further details.

[0077] In addition, a mechanical transmission device 13 of the inhalation valve 10 is provided, which is connected to the closing element 12 via a mechanical connecting element 14 so as to maintain the closing element 12 in the closed position 320 in the initial position of the transmission device 13, preferably providing the inhalation valve 10 as a normally closed inhalation valve 10 for the breathing system 100.

[0078] In the illustrated embodiment, the control pressure source 130 is specifically configured as a pump 130, wherein the implementation scheme with respect to these embodiments is not limited to this specific configuration. The pump 130 can be used to provide a control pressure PS for the transmission device 13 in the control pressure chamber 15, so that the transmission device 13 is moved from an initial position by the control pressure PS, in particular by an increase in the control pressure PS. Here, the transmission device 13 can be configured as a force-transmitting connection for the pressure chamber 110 and the closing element 12, so that when the chamber pressure PK in the pressure chamber 110 increases, the closing element 12 moves outside the initial position of the transmission device 13 and in particular in the direction of the closed position 320 against the control pressure PS. Figure 4 and 6 , it can be seen that the transmission means 13 can be arranged adjacent to the pressure chamber 110 so that the chamber pressure PK can act on the first surface S1 of the transmission means 13. For this purpose, for example, an opening of the suction valve 10 is provided in order to subject the transmission means 13 to the chamber pressure PK. In this case, the first surface S1 can be used to act with the chamber pressure PK from the pressure chamber 110 in order to transmit the increase in the chamber pressure PK into an increased force for moving the closure element 12 in the direction of the closed position 320 and thus for a coupling that acts to transmit force.

[0079] In addition to the first surface S1, the transmission means 13 can also have a second surface S2 for being acted upon by the control pressure PS from the control pressure chamber 15 in order to transmit the increase in the control pressure PS into an increased force for moving the closing element 12 in the direction of the open position 310. Figure 4 and 6 , the transmission means 13 can also be arranged adjacent to the control pressure chamber 15. Furthermore, the transmission means 13 can also be used to separate the control pressure chamber 15 from the pressure chamber 110, preferably in a fluid-tight manner. For this purpose, the transmission means 13 can form a delimitation of the control pressure chamber 15, possibly together with further walls of the control pressure chamber 15. These further walls are embodied, for example, in the form of an elastomer.

[0080] Preferably, the first surface S1 and the second surface S2 can be arranged opposite each other, for example, they are arranged on opposite sides of the transmission means 13, so as to transmit the increase of the chamber pressure PK and the control pressure PS into a mechanical deflection of the transmission means 13 in opposite directions. In this case, the closure element 12 can have a closure element surface S3 for closing the intake opening 11 in the closed position 320, wherein the area ratio of the closure element surface S3 to the first surface S1 is in the range of 0.25 to 1, preferably in the range of 0.3 to 0.75, preferably in the range of 0.5 to 0.6. In contrast, the area of ​​the second surface S2 can correspond to the area of ​​the first surface S1 or can differ from it by a maximum of 10%.

[0081] The transfer device 13 can be fixedly connected to the closing element 12 via the connecting element 14 so that when the chamber pressure PK increases, in particular when the pressure of the respiratory tract pressure PAW increases due to the exhalation process, the closing element 12 moves from the open position 310 to the closed position 320 and remains closed in the closed position 320 after the movement and / or in the initial position of the transfer device 13.

[0082] In addition, the transmission device 13 can be constructed in the form of a diaphragm 13, in particular a pressure diaphragm, preferably in order to provide movement of the closing element 12 and in particular a connection that transmits force by mechanical displacement of the diaphragm 13 as a function of an increase in the control pressure PS and / or the chamber pressure PK, wherein the diaphragm 13 is connected to the closing element 12 via a connecting element 14 in order to transmit the displacement to the closing element 12.

[0083] according to Figure 4 and 6 , the transmission means 13 is designed to provide the functionality of the normally closed intake valve in the initial position when the control pressure PS disappears, ie when no control pressure SP is provided.

[0084] In addition, according to Figure 6 A control device 150 may be provided for automatic control (Steuerung) and / or regulation (Regelung) of the flow 301 in order to determine a control pressure PS for moving the closing element 12 in the direction of the open position 310, and in order to provide the control pressure PS in particular in competition with the chamber pressure PK in the pressure chamber 110, so that the movement of the closing element 12 is preferably related to the ratio of the control pressure PS and the chamber pressure PK. In addition, an auxiliary pressure chamber 140 with a breathing opening 141 is provided for further guiding the provided breathing gas 300 to the patient 200, wherein the auxiliary pressure chamber 140 is fluidically connected to the pressure chamber 110 via a throttle opening 142, and wherein at least one sensor component 120 is provided for acquiring an actual pressure difference dP existing between the auxiliary pressure chamber 140 and the pressure chamber 110, wherein the control device 150 is implemented to determine a control deviation between a theoretical pressure difference between the auxiliary pressure chamber 140 and the pressure chamber 110 and the acquired actual pressure difference dP, so as to determine a control pressure PS based on the control deviation.

[0085] exist Figure 3 and 6 Components of a breathing system 100 according to the invention for enabling a patient 200 to breathe with the aid of breathing gas 300 are shown, wherein the breathing system 100 has a gas source 250 for providing the breathing gas 300, and a component 1 according to the invention having an inhalation valve 10 in the form of a normally closed inhalation valve 10 and a normally open exhalation valve 20.

[0086] In the following description of the invention, further exemplary embodiments of the assembly 1 according to the invention or of the breathing system 100 according to the invention are described, which are optional developments of the previously mentioned embodiments of the invention.

[0087] according to Figure 3 The breathing system 100 can also exist, for example, in the form of a breathing apparatus 100 or an anesthesia apparatus. The valve block 2 as part of the breathing system 100 can have at least the following components and, if possible, be combined in the form of a structural unit:

[0088] - Suction valve 10,

[0089] - a pressure chamber 110 , in particular in the form of a main pressure chamber, and

[0090] - Exhalation valve 20.

[0091] Conventionally, the inhalation valve 10 and the exhalation valve 20 are designed as normally open valves, that is to say they are open when not acted upon by pressure or other energy. Such a conventional inhalation valve 10 may also be fully functional. However, the control behavior then does not correspond to a self-stabilizing pressure regulator. According to the invention, the inhalation valve 10 may differ from this embodiment.

[0092] The inhalation valve 10 may be provided with an inlet 16 which is connected via a hose to a gas supply of a gas source 250. Correspondingly, the exhalation valve 20 may be provided with an outlet 26 which may be optionally connected to an exhalation hose.

[0093] Furthermore, the valve block 2 can have a breathing opening 141. A breathing mask or a tube, through which the patient 200 breathes, can be connected to the breathing opening 141.

[0094] As in Figure 4 , the closure element 12 can be held in a bell-shaped holding element 17, wherein a circumferential closure edge 18 formed at the bottom of the holding element 17 forms an inhalation opening 11 for the passage of the breathing gas 300 into the pressure chamber 110 of the valve block 2. The breathing gas 300 can be provided by a gas source 250. In addition, the chamber pressure PK can correspond to the airway pressure PAW in the example shown. The chamber pressure PK can be determined by the pressure of the breathing gas 300 during inhalation and by the exhalation pressure of the patient 200 during exhalation.

[0095] Furthermore, a closing element surface S3 of the closing element 1 is shown. In this case, the surface enclosed by the closing edge 18 (hereinafter also referred to as the crater surface) can roughly correspond to the area of ​​the closing element surface S3.

[0096] The transmission element 13 can have two opposite sides with a first surface S1 and a (opposite) second surface S2. The first surface S1 can face the pressure chamber 110 in order to be acted upon with a chamber pressure PK. The second surface S2 can face the control pressure chamber 15 in order to be acted upon with a control pressure PS. The chamber pressure PK then acts on the surface S1 as the outer side of the transmission element 13 and can cause a mechanical deflection of the transmission element 13 depending on the ratio of the chamber pressure PK to the control pressure PS.

[0097] The connecting element 14 can be connected on one side to the outer side of the transmission means 13 at the first surface S1, and on the opposite side to the closing element 12. Thus, the connecting element 14 enables the mechanical deflection of the transmission means 13 to be transmitted into the movement of the closing element 12. As a result, the increase in the chamber pressure PK is transmitted into the deflection of the transmission means 13, and the deflection of the transmission means 13 is transmitted into the movement of the closing element 12 in the direction of the closed position 320.

[0098] Arrow 301 shows a throughflow 301 of breathing gas 300 in the manner of a gas flow during inhalation. In this way, breathing gas 300 first flows into pressure chamber 110 and then flows to patient 200. In order to control at least throughflow 301 for the breathing of patient 200, a control and / or regulation of inhalation valve 10 can be provided. Inhalation valve 10 has the advantage that it can be used for breathing control and / or breathing regulation together with pneumatically driven valves 10, 20 close to the patient with a stable operating point. This enables improved regulation of a constant chamber pressure PK, in particular airway pressure PAW, by an optimized valve design of inhalation valve 10.

[0099] Advantageously, the intake valve 10 is designed in this case such that an increased chamber pressure PK exerts an increased closing force on the intake valve 10, in particular the closure element 12. As a result, the intake valve 10 can independently control the chamber pressure PK, which is thus the pressure equivalent of the control pressure PS of the pump 130. As a result, only a slow regulation or, in extreme cases, only a control without feedback of the chamber pressure PK is required for a slow pressure adjustment. In other words, the intake valve 10 can be regulated at least partially by the intake valve 10 itself.

[0100] This results in an advantageous NC (normally closed) inhalation valve 10 with control or regulation close to the patient for breathing purposes, wherein close to the patient means, for example, a distance from the patient of less than 0.5 m or 0.25 m (meter).

[0101] exist Figure 5 2 shows an exhalation valve 20 (exhalation valve) of a breathing system 100 according to the invention. It can have a connection 21 for forming an exhalation opening 24, a closure 22 for closing the exhalation opening 24 and a chamber wall 23 for forming a chamber for the exhalation valve 20. A further pump 130 (which is provided in addition to the pump 130 for the inhalation valve 10) can generate a pumping pressure in the chamber, by which the closure is pressed against the exhalation opening 24 of the connection 21 and thus the exhalation valve 20 is closed. The exhalation valve 20 is thus a normally open valve, that is to say NO (normally open). When the exhalation valve 20 is open, the exhalation air flow from the patient 200 can pass through the exhalation valve 20 from the valve block 2 to the outside into the ambient air or into a feedback system, which is used in particular in anesthesia-breathing systems 100, but also in respirators 100 without anesthesia function.

[0102] In the exhalation valve 20, an excessively high chamber pressure PK of the pressure chamber 110 of the valve block 2 can lead to an opening process, thereby allowing the breathing gas 300 to escape and thus allowing the chamber pressure PK to drop. The exhalation valve 20 is thus a self-regulating valve that can be regulated despite higher dynamics.

[0103] Figure 6 Another view of a breathing system 100 according to the invention with a component 1 according to the invention, which comprises an inhalation valve 10. It is shown that the valve block 2 forms a pressure chamber 110. The chamber pressure PK in the pressure chamber 110 can have an influence on the inhalation valve 10, by which the transmission means 13 is loaded. In addition, the transmission means 13 can also be loaded with a control pressure PS relative to the chamber pressure PK, which is generated by a pump 130 for controlling and / or regulating the breathing system 100, in particular the inhalation valve 10. For this purpose, the pump 130 is connected to the control pressure chamber 15 via a pump hose 131 in fluid communication. Alternatively, the pump 130 can be fixed to the inhalation valve 10, preferably via a coupling element, so that in particular the component 1 according to the invention can be constructed in the form of a structural unit. The embodiments in conjunction with this exemplary embodiment also relate to this variant. In the example shown, the chamber pressure PK can essentially correspond to the airway pressure PAW, if possible with a deviation dP. The deviation is thus the actual pressure difference dP between the airway pressure PAW and the chamber pressure PK, which can optionally be evaluated for control and / or regulation purposes.

[0104] exist Figure 7 4 shows a first coordinate system 401 for illustrating an exemplary course of the airway pressure PAW over time t. In addition, a second coordinate system 402 is shown for illustrating the course of the position of the transmission device 13 of the inhalation valve 10 over time t. When the transmission device 13 is implemented as a diaphragm 13, the position of the transmission device 13 can be shown in the form of a degree of displacement of the transmission device 13. The position of the transmission device 13 is associated with the position of the closure element 12 (and, for example, proportionally). Therefore, the position of the transmission device 13 is indicated in the second coordinate system 402, in which the closure element 12 is in the closed position 320 and in the open position 310. The course of the state of the exhalation valve 20 over time t is shown in the third coordinate system 403. The course starts here with a closed position 404 of the exhalation valve 20 and transitions to an open position 405 of the exhalation valve 20.

[0105] Furthermore, coordinate systems 401 , 402 , 403 show inhalation phases EP1 , EP2 provided during the breathing or regulation of breathing system 100 , which alternate periodically with exhalation phases AP1 , AP2 , which are also shown.

[0106] The profile of the airway pressure PAW can be provided in such a way that it is at a first, higher value in the inhalation phases EP1 , EP2 and at a value lower than the first value in the exhalation phases AP1 , AP2 .

[0107] The course of the position of the transmission means 13 of the intake valve 10 and, in the same way, the course of the position of the closing element 12 can be carried out with respect to time t as follows: in the intake phases EP1, EP2, they are respectively raised from a first position value (open position 310) to a second value (closed position 320) which is higher than the first value and remain at a higher value in the exhalation phases AP1, AP2, for example, at the value reached at the end of the intake phases EP1, EP2. In other words, the intake valve 10 can be opened widely at the beginning of the intake phases EP1, EP2 and then closed more and more until the end of the respective intake phase EP1, EP2. This means in the normally closed intake valve 10 that, in the intake phases EP1, EP2, the control pressure PS must be increased at the beginning in order to cause the opening. The intake valve 10 is closed in the exhalation phases AP1 and AP2, so that no additional control pressure PS should be applied here in the normally closed intake valve.

[0108] The state of the exhalation valve 20 over time t is shown as follows: in the inhalation phases EP1, EP2 it is at a first relatively high value (closed 404) and in the exhalation phases AP1, AP2 it drops strongly from the value in the inhalation phases EP1, EP2 to a smaller value (open 405) and then increases again relatively quickly.

[0109] The preset target for the airway pressure PAW in the case of inhalation can be, for example, a constant pressure with a higher value of, for example, 20 mbar or 25 mbar. In the case of exhalation, the preset target for the airway pressure PAW can also be, for example, a constant pressure value, which, however, is much lower than the preset target in the case of inhalation. In the case of exhalation, the preset target can be, for example, 4 mbar to 5 mbar.

[0110] To control and / or regulate Figure 7 The direction shown in Figure 6 1. For this purpose, it can, for example, actuate the pump 130 for controlling the inhalation valve 10 and / or a further pump 130 for controlling the exhalation valve 20. In order to influence the position of the closing element 12 of the inhalation valve 10 within the scope of control and / or regulation, the pump 130 can generate a control pressure PS in the control pressure chamber 15, e.g. Figure 6The pumps 130 are each designed, for example, as micropumps, in particular based on piezoelectric ceramics. The required speed of the pressure regulation determines the quality of the pressure regulation for breathing and can be less than 10 ms (milliseconds) and not more than 50 ms, depending on the requirements.

[0111] Furthermore, an auxiliary pressure chamber 140 may be provided, which is arranged adjacent to the pressure chamber 110 (as the main pressure chamber 110). The auxiliary pressure chamber 140 may be connected to the (main) pressure chamber 110 in fluid communication via a throttle opening 142 for exchanging breathing gas 300. Furthermore, a breathing opening 141 of the auxiliary pressure chamber 140 may be provided in order to allow the patient 200 to breathe with the breathing gas 300. The breathing opening 141 may be constructed in the wall of the valve block 2. The breathing gas 300 may reach the patient 200 from the auxiliary pressure chamber 140 as inhaled gas through the breathing opening 141 and may reach the auxiliary pressure chamber 140 from the patient 200 as exhaled gas. The pressure in the auxiliary pressure chamber 140 may in particular correspond to the airway pressure PAW, and the chamber pressure PK in the pressure chamber 110 may correspond to the airway pressure PAW with a deviation dP.

[0112] Important breathing parameters or operating parameters to be regulated or controlled are, for example:

[0113] - Gas flow (flow),

[0114] - chamber pressure PK in the pressure chamber,

[0115] - the concentration of carbon dioxide CO2, and

[0116] - The concentration of oxygen O2.

[0117] As in Figure 6 As further shown in FIG. 1 , a sensor assembly 120 may be provided for control and / or regulation. It is, for example, arranged at least partially in the pressure chamber 110 or (according to the embodiment shown) outside the pressure chamber, but is arranged in fluid communication with the pressure chamber 110. The sensor assembly 120 comprises in particular a first sensor 121 for acquiring the airway pressure PAW in the auxiliary pressure chamber 140 and a second sensor 122 for acquiring the flow rate between the auxiliary pressure chamber 140 and the pressure chamber 110. The second sensor 122 can also be understood as a differential pressure sensor, which acquires the actual pressure difference dP between the pressure chamber 110 and the auxiliary pressure chamber 140. Here, the pressure drop via the throttle opening 142 acquired as the actual pressure difference dP by the second sensor 122 corresponds to the flow rate through the throttle opening 142. The values ​​acquired by the sensors 121, 122 can be supplied to the regulation.

[0118] The purpose of regulating the breathing system 100 or the inhalation valve 10 is to ensure a pressure regulation that is as simple, robust, stable and tolerant as possible. Table 1a below shows exemplary requirements for an inhalation valve 10 .

[0119]

[0120] Table 1 b below shows exemplary requirements for the exhalation valve 20 .

[0121]

[0122] exist Figure 6 , it is shown that the second sensor 122 can be connected to the auxiliary pressure chamber 140 via the first fluid line 123 and can be connected to the (main) pressure chamber 110 via the second fluid line 124. In this way, the second sensor 122 can detect the actual pressure difference dP between the pressure chamber 110 and the auxiliary pressure chamber 140. In addition, the third fluid line 125 branches off from the first fluid line 123 and leads to the first sensor 121. This makes it possible to detect the airway pressure PAW via the first sensor 121. In order to supply the information about the actual pressure difference dP and the airway pressure PAW determined during the detection to the regulation, the sensors 121, 122 can be connected to the control device 150 for information transmission. Here, the first control unit 151 can detect the information of the first sensor 121, and the second control unit 152 can detect the information of the second sensor 122. The acquired information can be evaluated by the control device 150, and the corresponding pump 130 of the inhalation valve 10 and the exhalation valve 20 can be controlled by the control device 150 according to the evaluation result.

[0123] In the inhalation valve 10, such an actuation can cause the pump 130, which is connected to the control pressure chamber 15 via the pump hose 131, to generate a control pressure PS in the control pressure chamber 15. The inhalation valve 10 can be designed structurally in such a way that the opening and closing of the inhalation valve 10, that is to say the closing element 12, can only be given by the pressure ratio between the chamber pressure PK and the control pressure PS. As a result, the position of the transmission means 13, in particular the diaphragm 13, can be adjusted in such a way that the construction forces are balanced. Here, the input pressure from the gas source 250, by which the throughflow 301 of the breathing gas 300 is caused, can be constantly at, for example, 50 mbar.

[0124] If the transmission means 13 is conceived ideally, i.e. without its own force / travel and without damping (force / speed), then no additional adjustment is possible. However, a real transmission means 13 requires force in order to move out of its zero position. This corresponds to a type of spring characteristic curve.

[0125] Likewise, very fast movements can be hindered by damping. The counterforce generated by damping, that is to say usually by the compression of the elastic body, can possibly lead to a reduction in the driving force and a type of speed limitation. Abrupt pressure changes, which are required, for example, by the airway pressure PAW (cough) or the control pressure PS (start of inspiration or exhalation), can possibly lead only to a slow movement of the transmission means 13 and thus to a non-arbitrarily fast equalization of the pressure ratios.

[0126] For this reason, it is particularly meaningful to regulate the control pressure. This allows a significantly faster balancing process to be achieved compared to a control without feedback of the airway pressure PAW. In this case, the regulator provided by the control device 150 can, if possible, only be occupied with balancing sudden events. A permanent readjustment of unstable operating points is then eliminated.

[0127] When the transfer means 13 is implemented as a diaphragm, the diaphragm surface can, for example, have a diameter of 20 mm. The crater surface of the suction valve 1 can, for example, have a diameter of 8 mm. The ratio of the diaphragm area to the crater area can influence the behavior of the suction valve 10 with respect to closing, depending on the ratio of the chamber pressure PK to the control pressure PS. This is illustrated by way of example at the following formula, where AM is the diaphragm area, PEIN is the input pressure of the gas source, and AK is the crater area (PEIN causes a force at the closing element 12 in the direction of the closed position 320):

[0128] AK*PEIN+AM*PAW-AM*PS=0 (force balance),

[0129] By transforming this formula we get:

[0130] PAW=PS-PEIN*AK / AM

[0131] PEIN=50 mbar, which results from the formula as an exemplary theoretical variable for the respiratory tract pressure PAW=17 mbar.

[0132] Advantageously, the control device 150 can be designed to quickly equalize the airway pressure PAW at such a setpoint variable for the airway pressure PAW. Accordingly, the control device 150 can be designed to adjust the control pressure PS by means of a control so that a predefined airway pressure PAW (depending on the setpoint variable) is set for the patient 200. The setpoint variable can vary greatly during the course of the breathing cycle, possibly also through interaction with the patient 200. This also results in the need to control the regulation of these disturbance variables.

[0133] The acquisition of the second sensor 122 provided in the example shown provides the sum of the airway pressure PAW+actual pressure difference dP (ie PAW+dP). Here, the actual pressure difference dP can be positive during inspiration (volume flow to the patient) and negative during exhalation.

[0134] exist Figures 8 to 10 In order to further illustrate, an exemplary regulation is shown in each case. Here, the time course of the control pressure PS (with respect to time t) is shown in each case, which is generated in the inhalation valve 10 by the pump 130. In addition, the time course of another control pressure PS' is shown, which is used to control the exhalation valve 20. In addition, the time course of the airway pressure PAW (for example: as the actual value of the airway pressure PAW acquired by the first sensor 121) and the flow rate as a function of the actual pressure difference dP are shown. The time axis includes, for example, a time range of 0 to 12 seconds, wherein 3-second intervals are indicated by vertical dotted lines. In addition, the inhalation phases EP1, EP2 are shown again, which alternate periodically with the exhalation phases AP1, AP2 also shown. In addition, the sub-phases Ph3 to Ph6 are indicated corresponding to Tables 1a, 1b:

[0135] - Subphase Ph3 - the beginning of inspiration,

[0136] - Subphase Ph4 - Regulation of inspiration,

[0137] - Subphase Ph5 - the beginning of exhalation, and

[0138] - Subphase Ph6 - Control / regulation of exhalation.

[0139] exist Figure 8 An exemplary control is described in , in which a control pressure PS for the inhalation valve 10 and a further control pressure PS′ for the exhalation valve 20 are adjusted without feeding back the airway pressure PAW to the control device 150 .

[0140] When control is used instead of regulation, the first and second sensors 122 and possibly also the auxiliary pressure chamber 140 may not be required.

[0141] The time profile of the control pressure PS at the intake valve 10 can be selected as follows: in the intake phases EP1 , EP2 to, for example, 20 mbar, and in the exhalation phases AP1 , AP2 to, for example, 0 mbar.

[0142] When using control (open loop), the time profile of the additional control pressure PS′ at the exhalation valve 20 can be selected as follows: in the inhalation phases EP1 , EP2 to, for example, 25 mbar and in the exhalation phases AP1 , AP2 to, for example, 4 mbar.

[0143] The shown time profile of the volume flow indicated in the actual pressure difference dP is not relevant for control (open loop) if applicable.

[0144] exist Fig. 9 An exemplary regulation is described in which the control pressure PS for the inhalation valve 10 and the further control pressure PS′ for the exhalation valve 20 are adjusted without the airway pressure PAW being fed back to the control device 150. However, unlike in Figure 8 In the example shown in , a so-called "flow compensation" can be used within the scope of the regulation. In this case, the actual pressure difference dP is regulated by the control device 150. Accordingly, the actual pressure difference dP is regulated by the control device 150. Figure 8 The superposition of the “controlled” profile (visually shown in ) and the control portion results in the time profile of the control pressure PS at the intake valve 10 .

[0145] Furthermore, this superposition can result in a maximum value of the control pressure PS at the beginning of the inhalation phases EP1, E2P, which is, for example, above 25 mbar, and in which the inhalation valve 10 opens particularly widely in order to quickly reach an airway pressure PAW of 25 mbar. During the exhalation phases AP1, AP2, the control pressure PS can continue to be at 0 mbar in order to actuate the inhalation valve 10.

[0146] The time profile of the additional control pressure PS′ at the exhalation valve 20 corresponds in particular to the time profile of the inhalation phases EP1, EP2 according to Figure 8 The shown course is due to the fact that the control continues to exist. However, in the exhalation phase AP1 or AP2, the control of the exhalation valve 20 is superimposed on the regulation of the actual pressure difference dP, wherein a minimum value occurs in the course of the actual pressure difference dP. In order to adjust the actual pressure difference dP to a value of 0 mbar as quickly as possible during exhalation, the exhalation valve 20 can be opened more strongly by pressure relief than is predefined by the control (open loop) alone. This results in a pressure increase for the additional control pressure PS' from a value of 0 mbar to 4 mbar which increases approximately linearly.

[0147] The temporal course of the volume flow, which is indicated in the actual pressure difference dP, is as follows: In the inspiration phases EP1, EP2, the actual pressure difference dP rises rapidly to a maximum value 612, from which it then decreases approximately linearly again to an actual pressure difference dP of 0 mbar at the end of the respective inspiration phase EP1, EP2. In the expiration phases AP1, AP2, the volume flow or gas flow reverses and is now directed away from the patient 200. The reversal of direction is manifested in a change in the sign of the actual pressure difference dP, which therefore rapidly reaches a minimum value 616 at the beginning of the expiration phases AP1, AP2, in order to then increase approximately linearly, also with the support of the control, to a value of 0.

[0148] exist Fig.10 An exemplary regulation is described in which a control pressure PS for the inhalation valve 10 and a further control pressure PS' for the exhalation valve 20 are adjusted with the airway pressure PAW fed back to the control device 150. In this case, a flow compensation can also be provided by the control device 150. The temporal course of the airway pressure PAW is superimposed with a pressure increase, which can occur, for example, due to a coughing event (see peak in the course in the subphase Ph4). Regulation has the advantage over control that such a pressure increase can be introduced in an improved manner.

[0149] The pressure increase of the airway pressure PAW may also lead to an increase in the chamber pressure PK in the pressure chamber 110. The control device 150 may be designed to carry out regulation with regard to the pressure increase as follows:

[0150] - the volume flow according to the actual pressure difference dP suddenly reverses, so that a minimum occurs in the intake phase EP1 (in the subphase Ph4). The control is adjusted accordingly depending on the result of the acquisition of the second sensor 122 and a pressure drop is generated at the minimum of the control pressure SP for the control pressure chamber 15 (also in the subphase Ph4), which causes the intake valve 10 to close more, which causes the flow 301 to be throttled and thus also causes a pressure relief in the pressure chamber 110, and / or

[0151] - The first sensor 121 also detects the pressure increase in the airway pressure PAW caused by the coughing event during inhalation. The control is correspondingly regulated by reducing the further control pressure PS' to a minimum value (in the subphase Ph4) and thereby opening the exhalation valve 20, which causes a faster pressure relief in the pressure chamber 110.

[0152] It can be seen that cough events can be reliably controlled in this way in a closed loop control.

[0153] The above explanations of the embodiments describe the present invention only within the scope of examples. As long as it makes sense in technology, it is obvious that the individual features of the embodiments can be combined freely with each other without leaving the scope of the present invention.

[0154] Reference numerals list

[0155] 1 Assembly, valve assembly

[0156] 2 Valve block

[0157] 10 Suction valve

[0158] 11 Inhalation opening

[0159] 12 Closure element

[0160] 13 Transfer device, diaphragm

[0161] 14 Connecting elements

[0162] 15 Control pressure chamber

[0163] 16 Enter the Ministry

[0164] 17 Retaining element

[0165] 18 Closed Edge

[0166] 20 Exhalation valve

[0167] 21 20 connection

[0168] 22 20 closure

[0169] 23 20 chamber wall

[0170] 24 Exhale Opening

[0171] 26 Discharge section

[0172] 100 Respiratory systems, respiratory equipment

[0173] 110 Pressure chamber

[0174] 120 sensor assembly

[0175] 121 120 first sensor,

[0176] 122 120 second sensor,

[0177] 123 First fluid pipeline

[0178] 124 Second fluid pipeline

[0179] 125 Third fluid pipeline

[0180] 130 Control pressure source, pump

[0181] 131 Pump hose

[0182] 140 Auxiliary pressure chamber

[0183] 141 Breathing Opening

[0184] 142 Throttle opening

[0185] 150 Control Device

[0186] 151 150 first control unit

[0187] 152 150 Second control unit

[0188] 200 patients

[0189] 250 Gas Source

[0190] 300 Breathing Gas

[0191] 301 Flow

[0192] 310 Open position

[0193] 320 Close position

[0194] 401 First Coordinate System

[0195] 402 Second Coordinate System

[0196] 403 The third coordinate system

[0197] 404 20 closed location

[0198] 405 20 open positions

[0199] dP Actual pressure difference

[0200] PAW Airway Pressure

[0201] PK chamber pressure

[0202] PS Control Pressure

[0203] AP1 First outgoing phase

[0204] AP2 Second outgoing phase

[0205] EP1 First Inhalation Phase

[0206] EP2 Second inhalation phase

[0207] S1 first side

[0208] S2 Side 2

[0209] S3 Closed element surface

[0210] PS' Additional control pressure.

Claims

1. An assembly (1) with an inhalation valve (10) for a breathing system (100), comprising: an inhalation opening (11) of the inhalation valve (10) for the passage (301) of breathing gas (300) into the pressure chamber (110) in order to provide the breathing gas (300) in the pressure chamber (110) for breathing of the patient (200), a closing element (12) of the intake valve (10), which is movably arranged to close the intake opening (11) for the throughflow (301) in a closed position (320) and to at least partially open it in an open position (310), a transmission device (13) of the inhalation valve (10), which is connected to the closure element (12) via a connecting element (14) in order to hold the closure element (12) in the closed position (320) in the initial position of the transmission device (13), thereby providing the inhalation valve (10) as a normally closed inhalation valve (10) for the breathing system (100), a control pressure source (130) for providing a control pressure (PS) in a control pressure chamber (15) to the transmission element (13), so as to move the transmission element (13) from the initial position by means of the control pressure (PS), in, The transmission device (13) is designed to be a force-transmitting connection between the pressure chamber (110) and the closing element (12), so that when the chamber pressure (PK) in the pressure chamber (110) increases, the closing element (12) is moved outside the initial position of the transmission device (13) and in the direction of the closed position (320) against the control pressure (PS).

2. The assembly (1) according to claim 1, characterized in that The transmission device (13) furthermore has: a first surface (S1) for being loaded with a chamber pressure (PK) from the pressure chamber (110) in order to transmit the increase in the chamber pressure (PK) into an increased force for moving the closure element (12) in the direction of the closed position (320), a second surface (S2) for being loaded with a control pressure (PS) from the control pressure chamber (15) in order to transmit an increase in the control pressure (PS) into an increased force for moving the closure element (12) in the direction of the open position (310).

3. The assembly (1) according to claim 2, characterized in that The closure element (12) has a closure element surface (S3) for closing the intake opening (11) in the closed position (320), wherein the area ratio of the closure element surface (S3) to the first surface (S1) is in the range of 0.25 to 1.

4. The assembly (1) according to any one of claims 2 or 3, characterized in that The area of ​​the second surface (S2) corresponds to the area of ​​the first surface (S1) or differs therefrom by a maximum of 10%.

5. Assembly (1) according to any one of claims 1 to 3, characterized in that The transmission device (13) is fixedly connected to the closing element (12) via the connecting element (14) so ​​that when the chamber pressure (PK) increases, the closing element (12) moves from the open position (310) to the closed position (320) and remains closed in the closed position (320) after the movement and / or in the initial position of the transmission device (13).

6. Assembly (1) according to any one of claims 1 to 3, characterized in that The transmission device (13) is designed in the form of a diaphragm (13) so as to provide a movement of the closing element (12) by mechanically deflecting the diaphragm (13) as a function of an increase in the control pressure (PS) and / or the chamber pressure (PK), wherein the diaphragm (13) is connected to the closing element (12) via the connecting element (14) in order to transmit the deflection to the closing element (12).

7. Assembly (1) according to any one of claims 1 to 3, characterized in that The transmission means (13) is designed to provide the functionality of a normally closed intake valve in the initial position when the control pressure (PS) disappears.

8. Assembly (1) according to any one of claims 1 to 3, characterized in that The control pressure source (130) is designed as a piezoelectric pump in order to adjust the control pressure (PS) in the range of 0 mbar to 3 mbar during the exhalation of the patient (200).

9. Assembly (1) according to any one of claims 1 to 3, characterized in that The control device (150) is configured to automatically control and / or regulate the throughflow (301) in order to determine a control pressure (PS) for moving the closing element (12) in the direction of the open position (310), and to provide the control pressure (PS) in competition with a chamber pressure (PK) in the pressure chamber (110), so that the movement of the closing element (12) is related to the ratio of the control pressure (PS) to the chamber pressure (PK).

10. Assembly (1) according to claim 9, characterized in that An auxiliary pressure chamber (140) with a breathing opening (141) is provided for further guiding the provided breathing gas (300) to the patient (200), wherein the auxiliary pressure chamber (140) is fluidically connected to the pressure chamber (110) via a throttle opening (142), and wherein at least one sensor component (120) is provided for acquiring an actual pressure difference (dP) existing between the auxiliary pressure chamber (140) and the pressure chamber (110), wherein the control device (150) is implemented to determine a regulation deviation between a theoretical pressure difference (dP) between the auxiliary pressure chamber (140) and the pressure chamber (110) and the acquired actual pressure difference (dP) so as to determine the control pressure (PS) based on the regulation deviation.

11. Assembly (1) according to claim 1, characterized in that The control pressure source (130) is a pump.

12. Assembly (1) according to claim 2, characterized in that The first surface (S1) and the second surface (S2) are arranged opposite each other in order to transmit the increase of the chamber pressure (PK) and the control pressure (PS) into a mechanical deflection of the transmission means (13) in opposite directions.

13. Assembly (1) according to claim 3, characterized in that The area ratio of the closing element surface (S3) to the first surface (S1) is in the range of 0.3 to 0.

75.

14. Assembly (1) according to claim 13, characterized in that The area ratio of the closing element surface (S3) to the first surface (S1) is in the range of 0.5 to 0.

6.

15. Assembly (1) according to claim 5, characterized in that The transmission device (13) is fixedly connected to the closing element (12) via the connecting element (14) so ​​that in the event of a pressure increase in the respiratory tract pressure (PAW) occurring due to an exhalation process, the closing element (12) is moved from the open position (310) to the closed position (320) and remains closed in the closed position (320) after the movement and / or in the initial position of the transmission device (13).

16. Assembly (1) according to claim 6, characterized in that The transmission means (13) is designed in the form of a diaphragm (13) in order to provide the force-transmitting coupling by a mechanical deflection of the diaphragm (13) as a function of an increase in the control pressure (PS) and / or the chamber pressure (PK).

17. Assembly (1) according to claim 8, characterized in that The control pressure source (130) is designed as a piezoelectric pump in order to adjust the control pressure (PS) to 0 mbar during the exhalation process of the patient (200).

18. A breathing system (100) for allowing a patient (200) to breathe with the aid of a breathing gas (300), the breathing system comprising: - a gas source (250) for providing said breathing gas (300); - Assembly (1) with an air intake valve (10) according to any one of claims 1 to 17, wherein The air intake valve (10) is configured as a normally closed air intake valve (10); An exhalation valve (20) which is designed as a normally open exhalation valve (20).

19. A method for operating an inhalation valve (10) of a breathing system (100), in which the following steps are performed: - starting a flow (301) of breathing gas (300) through the inhalation opening (11) of the inhalation valve (10) into the pressure chamber (110) in order to provide the breathing gas (300) in the pressure chamber (110) for breathing of the patient (200); - providing a closing element (12) of the intake valve (10) which is movably arranged in order to close the intake opening (11) for the throughflow (301) in a closed position (320) and to at least partially open it in an open position (310); - providing a transmission device (13) of the inhalation valve (10), which is connected to the closure element (12) via a connecting element (14) in order to hold the closure element (12) in the closed position (320) in an initial position of the transmission device (13), thereby providing the inhalation valve (10) as a normally closed inhalation valve (10) for the breathing system (100); - providing a control pressure source (130) for providing a control pressure (PS) in a control pressure chamber (15) to the transmission device (13), so as to move the transmission device (13) from the initial position by the control pressure (PS); in, The transmission device (13) is designed to be a force-transmitting connection between the pressure chamber (110) and the closing element (12), so that when the chamber pressure (PK) in the pressure chamber (110) increases, the closing element (12) is moved outside the initial position of the transmission device (13) and in the direction of the closed position (320) against the control pressure (PS).

20. The method according to claim 19, characterized in that The inhalation valve (10) is designed according to an assembly (1) according to any one of claims 1 to 17 and / or according to a breathing system (100) according to claim 18.

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