Supply assembly and method for supplying a gas mixture to a patient-side coupling unit

Abstract

The invention relates to an assembly and a method for supplying a gas mixture comprising two different gas components to a patient-side coupling unit. A first gas component is guided from a first source through a first pressure reducer and a first channel to a mixing point, and a second gas component is guided from a second source through a second pressure reducer and a second channel to the mixing point. Each pressure reducer comprises a pre-pressure inlet, a back-pressure outlet, a control pressure chamber and a control pressure actuator, respectively. The control pressure actuators control the pressure in the control pressure chambers, and the pressure at the back-pressure outlets depends on the pressure in the control pressure chambers. From a predetermined nominal share of the gas components, a nominal ratio between the volume flow through the first channel and the volume flow through the second channel is derived. The two control pressure actuators are manipulated with control targets or regulation targets such that the actual ratio of the two volume flows equals the derived nominal ratio.

Description

Technical Field

[0001] The present invention relates to a supply assembly and a method for supplying a gas mixture comprising two different gas components to a coupling unit on the patient side. Background Technology

[0002] The supply assembly according to the invention can be used, for example, for artificial respiration of a patient. A patient-side coupling unit, such as a breathing mask, catheter, or tube, is disposed inside or on the patient's body. To perform artificial respiration on the patient, a gas mixture is delivered to the patient-side coupling unit. This gas mixture includes oxygen and another component, and is therefore not pure oxygen. Preferably, the ventilator performs a series of breathing cycles and delivers a certain amount of the gas mixture to the patient-side coupling unit in each breathing cycle.

[0003] It is possible to use breathing air as a gas component. It is often desirable that the oxygen content in the gas mixture delivered to the coupling unit on the patient side is greater than the oxygen content in the breathing air. To achieve this, a gas mixture comprising breathing air and pure oxygen is generated. The present invention can be used to generate such a gas mixture. It is also possible that the gas mixture contains an anesthetic. Summary of the Invention

[0004] The objective of this invention is to provide a supply assembly and a method capable of supplying a gas mixture comprising two gas components to a patient-side coupling unit, wherein the temporal variation curves of the volumetric flow rate and / or pressure of the supplied gas mixture in the fluid connection with the patient-side coupling unit can be well adjusted.

[0005] The present invention is achieved by a supply component having the features of claim 1 and a method having the features of claim 13. Advantageous designs are described in the dependent claims. Wherever meaningful, the advantageous designs of the supply component are also advantageous designs of the method according to the invention, and vice versa.

[0006] The supply assembly and method according to the invention are capable of supplying a gas mixture comprising oxygen to the coupling unit on the patient side. This gas mixture comprises a first gas component, particularly air, and a second gas component, particularly pure oxygen. These two gas components are chemically distinct from each other. It is possible that the two gas components comprise the same components, for example, both comprising oxygen. It is also possible that one gas component comprises an anesthetic. It is possible that one gas component is itself a gas mixture, such as breathing air or a mixture of an anesthetic and a carrier gas.

[0007] The patient-side coupling unit is connected to or can be connected to the patient. Specifically, the patient-side coupling unit is disposed within or on the patient's body, or can be disposed there. Tubes, catheters, and breathing masks are examples of coupling units used for the patient side.

[0008] Next, we will use the concept of a "channel." A channel is a component that guides fluid, especially a gas or gas mixture, along a pre-defined path and ideally prevents the fluid from deviating from that path. Hose and pipe are examples of channels. Typically, the desired purpose of a channel is that the fluid is always, or at least temporarily, guided through the channel in the same direction, rather than being guided in the opposite direction through a pipe.

[0009] Furthermore, the following discussion concerns establishing a fluid connection between two components. This means that fluid can flow from one component to the other, ideally without leakage into the environment. It is possible that the two components are directly connected to each other. It is also possible that a gap exists between the two components and a fluid guiding unit, such as a hose and / or channel as described above, connects the two components to each other. It is also possible that fluid temporarily flows from the first component to the second component via the fluid connection and temporarily, in turn, from the second component to the first component via the fluid connection. The fluid connection can be established permanently or only temporarily.

[0010] Furthermore, the concept of "source" will be used hereafter. In the context of this invention, a source is capable of providing fluid, particularly the gaseous components of the gas mixture to be produced, persistently or at least temporarily. A source is in particular a fixed supply connection or a movable source, such as a container filled with fluid, particularly a compressed air cylinder. It is also possible that a fluid delivery unit, such as a pump or blower of a respirator, acts as a source for the fluid. It is possible to use two different sources for the same gaseous component, particularly a fixed source and a movable source.

[0011] The supply assembly according to the invention includes a first pressure reducer and a second pressure reducer. Each pressure reducer includes a pre-pressure inlet, a back pressure outlet, and a controllable pressure control actuator. A pressure reducer is a component that receives gas with a pre-pressure at its pre-pressure inlet, which is a gas component in this context, and supplies this gas at a back pressure at its back pressure inlet, wherein the back pressure is less than or equal to the pre-pressure. Typically, the back pressure varies over time, and the pre-pressure also varies over time. The pressure reducer guides the gas from the pre-pressure inlet through its interior to the back pressure outlet, at least temporarily.

[0012] The two pressure reducers can be constructed identically or differently from each other. The two pressure reducers are connected in parallel, which will be explained in more detail below.

[0013] According to the invention, the first pressure reducer provides a first gas component at its back pressure outlet, and the second pressure reducer provides a second gas component at its back pressure outlet. The pressure control actuators of the pressure reducers are capable of controlling the pressure at which the pressure reducers provide the corresponding gas component at their back pressure outlets. Typically, the pressure at the back pressure outlet varies over time. The two pressure control actuators are preferably able to set and change the corresponding pressure at the back pressure outlets independently of each other.

[0014] A fluid connection, or at least a temporary fluid connection, is established between the pre-pressure inlet of the first pressure reducer and the first source. The first source is capable of providing a first gas component.

[0015] A fluid connection, or at least a temporary fluid connection, is established between the pre-pressure inlet of the second pressure reducer and the second source. The second source is capable of providing a second gas component.

[0016] The first channel is connected to the back pressure outlet of the first pressure reducer and guides the first gas component from this back pressure outlet to the mixing point. The second channel is connected to the back pressure outlet of the second pressure reducer and guides the second gas component from this back pressure outlet to the mixing point. At the mixing point, the two gas components mix with each other or spontaneously mix with each other. After mixing, they form a gas mixture or a component of a gas mixture, which is then delivered to the coupling unit on the patient side.

[0017] The inhalation channel connects the mixing point to the coupling unit on the patient side. The inhalation channel guides the gas mixture generated, being generated, or already generated at the mixing point to the coupling unit on the patient side.

[0018] Therefore, according to the invention, the first and second channels lead into a mixing point, and the intake channel begins at the mixing point. In its simplest case, the mixing point is a purely mechanical component that connects the three channels to each other in a Y-shaped configuration. Alternatively, the mixing point may be implemented using a gas mixer that mixes two gas components with an optional third gas component to form an ideally homogeneous gas mixture.

[0019] The control device (controller, control unit) for processing signals of the supply component can operate both the control pressure actuator of the first pressure reducer and the control pressure actuator of the second pressure reducer, thereby changing not only the pressure at the back pressure outlet of the first pressure reducer but also the pressure at the back pressure outlet of the second pressure reducer. The control device can independently control the two actuators and thereby independently change the two pressures.

[0020] The predetermined proportion of the first gas component in the gas mixture is specified. As an alternative or supplementary option, the predetermined proportion of the second gas component is also specified. This predetermined proportion can be constant over time or vary over time. The control device derives a rated ratio, i.e., the rated ratio between the volumetric flow rate through the first channel and the volumetric flow rate through the second channel, from this predetermined rated proportion.

[0021] Because the two channels lead to the same mixing point, the ratio of the two actual volumetric flow rates through the two channels determines or at least affects the proportion of the first gas component in the gas mixture and the proportion of the second gas component in the gas mixture, which flows from the mixing point to the patient side of the coupling unit in the inhalation channel.

[0022] The control device is designed to operate two control pressure actuators with the following control or adjustment objective: the actual ratio of the two volumetric flow rates should equal the derived rated ratio. In practice, at least temporarily, an adjustment deviation usually exists, meaning that the actual proportion of the gas components deviates from the rated proportion.

[0023] The method according to the invention is implemented using this supply component. The method includes the following steps:

[0024] - The first source provides the first gaseous components.

[0025] - The second source provides the second gas component.

[0026] - The first gas component is guided from the first source to the pre-pressure inlet of the first pressure reducer.

[0027] - The first gas component flows at least temporarily from the pre-pressure inlet through the first pressure reducer to the back pressure outlet of the first pressure reducer.

[0028] - The first channel guides the first gas component from the back pressure outlet of the first pressure reducer to the mixing point.

[0029] - The second gas component is guided from the second source to the pre-pressure inlet of the second pressure reducer.

[0030] - The second gas component flows at least temporarily from the pre-pressure inlet through the second pressure reducer to the back pressure outlet of the second pressure reducer.

[0031] - The second channel guides the second gas component from the back pressure outlet of the second pressure reducer to the mixing point.

[0032] - At the mixing point, the two gas components mix to form a gas mixture.

[0033] - The inhalation channel will guide the gas mixture generated at the mixing point to the coupling unit on the patient side.

[0034] Additionally, the method includes the following steps:

[0035] - For example, the rated proportions of the first gas component and / or the second gas component in the gas mixture to be produced are pre-defined by the user in a computer-measurable form.

[0036] - The rated ratio between the volumetric flow rate through the first channel and the volumetric flow rate through the second channel is automatically derived using the pre-given rated share.

[0037] - The two control pressure actuators of the two pressure reducers are operated according to the rated ratio derived from the two volumetric flow rates. This operation controls the pressure at the two back pressure outlets of the two pressure reducers.

[0038] The two control pressure actuators are operated with the following control or adjustment objective: the actual ratio of the two volumetric flow rates should be equal to the derived rated ratio.

[0039] The control device is capable of automatically performing the corresponding steps. Preferably, the control device determines the pre-given rated components by reading access.

[0040] This invention allows for the supply of a gas mixture to the coupling unit on the patient side. The proportions of the first gas component and / or the second gas component in the gas mixture can be predetermined. This proportion is, for example, predetermined as Vol-%. In particular, the oxygen and / or anesthetic proportions of the gas mixture can be predetermined.

[0041] The two sources provide two gaseous components. Due to the two pressure regulators, it is possible for the two sources to provide these gaseous components at pressures higher than the pressure the gas mixture in the inspiratory channel should have. The two pressures at the two sources can be different from each other and can be changed independently of each other. Due to the pressure regulators, it is not necessary to match the pressure at which the sources provide the gaseous components to the pressure the gas mixture in the inspiratory channel should have, or even to regulate this pressure. More precisely, the two pressure regulators decouple the two sources from the three channels on one hand and from the coupling unit on the patient side on the other. In many cases, due to decoupling, existing sources for the gaseous components can be used relatively easily, such as two fixed sources in a hospital or vehicle supply network. At least one source can also be a fluid delivery unit, such as a pump or blower in a ventilator.

[0042] The two sources each provide a gas component. This gas component flows from the source through a pressure reducer to a mixing point. The gas mixture flowing from the mixing point to the patient-side coupling unit should have a predetermined proportion of the first gas component and / or the second gas component. Due to the invention, the volumetric flow rates of the two components are controlled or regulated through two channels leading to the mixing point. The objective in such control (open-loop control) or regulation (closed-loop control) is that the actual ratio of the two volumetric flow rates equals a predetermined nominal ratio. The actual ratio between the two volumetric flow rates determines the actual proportion of the first gas component and / or the second gas component in the gas mixture flowing to the patient-side coupling unit. Therefore, the control or regulation according to the invention generally ensures that the gas mixture actually has the predetermined proportion of the gas components, except for unavoidable measurement errors and other deviations. This effect is often desired for implementing specific medical treatments.

[0043] It is possible, but not necessary, for the present invention to control or regulate the volumetric flow rate of the source used to provide the gaseous components. More precisely, it is possible that the source provides the gaseous components at a pressure that is constant over time or also fluctuates randomly, and therefore the volumetric flow rate from the first and / or second source to the first or second channel depends on the load downstream of the source. Due to the two pressure regulators and the adjustment of the volumetric flow rate ratio, the gas mixture flowing to the coupling unit on the patient side still has the desired proportion.

[0044] It is possible, but not necessary, of the present invention to control or regulate the volumetric flow rate of the first gas component flowing through the first channel or to regulate the volumetric flow rate of the second gas component flowing through the second channel. It is sufficient to adjust the ratio of the two volumetric flow rates. Therefore, a controllable actuator capable of controlling the volumetric flow rate through the first and / or second channels is not required. However, the present invention can be used in conjunction with at least one such actuator, particularly with a proportional valve, wherein the actuator controls the volumetric flow rate through the intake channel.

[0045] The pressure in the two channels leading to the mixing point is changed by means of the pressure at the back pressure outlets of the two pressure reducers. In many cases, this feature allows the use of two pressure reducers with relatively simple mechanical construction.

[0046] In many cases, the volumetric flow rate of the gas mixture flowing through the inspiratory channel to the coupling unit on the patient side should be adjusted. The goal of this adjustment is that the temporal variation curve of the actual volumetric flow rate to the coupling unit on the patient side follows a pre-defined temporal nominal variation curve. For example, the volumetric flow rate from the mixing point to the coupling unit on the patient side should be synchronized with the patient's own respiratory activity. If the patient is no longer performing their own respiratory activity and is completely anesthetized, the volumetric flow rate of the gas mixture through the inspiratory channel should often reliably replace their own respiratory activity.

[0047] The volumetric flow rates of the two sources supplying the two gas components can vary over time. Conversely, the actual proportion of the gas components in the gas mixture should be equal to a predetermined proportion and is generally constant over time. This correct proportion of the gas components is achieved by controlling or adjusting the ratio between the volumetric flow rates according to the invention. The invention eliminates the need for an actuator capable of altering the proportion of the gas components in the gas mixture flowing through the intake channel. The invention also eliminates the need for an actuator capable of controlling the volumetric flow rate of the gas components through the respective channels. However, the invention can be used in conjunction with such an actuator for the channel leading to the mixing point.

[0048] According to the invention, the gas mixture is guided from the mixing point to the coupling unit on the patient side. This gas mixture contains oxygen. Preferably, at least one of the two gas components is oxygen or includes oxygen. The oxygen content in the gas mixture depends on...

[0049] - The oxygen content in the first gas component.

[0050] - The oxygen content in the second gas component, and

[0051] - The proportion of the two volumetric flow rates flowing to the mixing point through two channels, as per the present invention, is controlled or regulated.

[0052] It is generally known what oxygen content the two gaseous components supplied by the two sources have. Of course, it is also possible that the sources supply gaseous components with no oxygen content.

[0053] At least one of the two gas components can include at least one anesthetic. For example, one gas component is breathing air, and the other gas component is a mixture of at least one anesthetic and a carrier gas.

[0054] In another design, oxygen or breathing air is guided to the coupling unit on the patient side via a third conduit.

[0055] In a preferred design, at least one pressure reducer includes a control pressure chamber. Preferably, both pressure reducers each include a control pressure chamber. The control pressure actuator of this pressure reducer is capable of controlling the pressure in the control pressure chamber. The pressure used by this pressure reducer to supply the gaseous component at its back pressure outlet depends on the pressure in the control pressure chamber as follows: the higher the pressure in the control pressure chamber, the higher the pressure at the back pressure outlet.

[0056] In many cases, the design with a control pressure chamber allows the control pressure actuator, or at least each mechanical component of the actuator, to be fully housed within the control pressure chamber. Therefore, this chamber, or each of the other chambers of the pressure reducer, does not contain an actuator. The control pressure chamber provides a degree of protection for the actuator against external mechanical influences.

[0057] In one implementation of this design, the pressure reducer includes a back pressure chamber in addition to the control pressure chamber. This back pressure chamber is fluidly connected to the back pressure outlet. A movable wall separates the control pressure chamber from the back pressure chamber. The control pressure actuator can move this movable wall, thereby changing the volume of the control pressure chamber. Due to the movable wall, the two chambers are coupled to each other as follows: if the volume of the control pressure chamber is increased, the volume of the back pressure chamber decreases, and thus the pressure in the back pressure chamber increases. If the volume of the control pressure chamber is decreased, the opposite occurs.

[0058] According to the invention, each pressure reducer includes a pre-pressure inlet and a back-pressure outlet and at least temporarily directs the gaseous component from the pre-pressure inlet to the back-pressure outlet. The pressure at the pre-pressure inlet is greater than or equal to the pressure at the back-pressure outlet. In one design, at least one pressure reducer, preferably two pressure reducers, each includes a pre-pressure chamber and a back-pressure chamber. This design can be combined with the design described above, which includes at least one pressure reducer with a control pressure chamber, but it can also be implemented without a control pressure chamber.

[0059] The pre-pressure chamber is connected to the pre-pressure inlet, and the back-pressure chamber is connected to the back-pressure outlet. A partition wall fluidly seals these two chambers apart. An opening is milled into this partition wall. A closure member can move back and forth between a release position and a closed position. In the release position, the closure member releases the opening, thereby establishing a fluid connection between the pre-pressure chamber and the back-pressure chamber. When a pressure differential is present, the gas component flows from the pre-pressure chamber to the back-pressure chamber due to pressure compensation. In the closed position, the closure member closes this opening, such that the fluid connection is interrupted and the pressure differential does not cause pressure compensation. The pressure regulator's control pressure actuator can preferably mechanically connect to move this closure member back and forth between the two positions.

[0060] In a preferred design, the supply assembly includes a first volumetric flow sensor and a second volumetric flow sensor. The first volumetric flow sensor measures the volumetric flow rate through a first channel, and the second volumetric flow sensor measures the volumetric flow rate through a second channel. For example, each volumetric flow sensor measures the pressure difference between two points in the channel. The signals from the two volumetric flow sensors are transmitted to a control device. This design enables the regulation of the two volumetric flow rates. By evaluating the transmitted measurements, the control device determines the actual ratio between the two volumetric flow rates, i.e., measures the regulation parameter during regulation.

[0061] It is possible that, due to interference, the proportions of the first and / or second gaseous components in the gas mixture may deviate from the nominal proportions downstream of the mixing point, even though the ratio of the two volumetric flow rates is rapidly adjusted, i.e., the adjustment deviation is quickly reduced. For example, the proportions of gaseous components in the gas supplied from the source may fluctuate, or leaks may occur in the channel. Therefore, in one design, a concentration sensor measures the amount of the first and / or second gaseous components in the gas mixture flowing through the intake channel. This concentration sensor is preferably also arranged downstream of a controllable actuator capable of changing the volumetric flow rate through the intake channel. If this concentration sensor detects an excessively high or low proportion of the gaseous components in the gas mixture, the volumetric flow rate flowing through the channel to the mixing point is preferably increased or decreased accordingly. This design at least partially compensates for the effects of interference.

[0062] According to the invention, the two channels for the two gas components lead to the same mixing point. Thus, in many cases, pressure equilibrium occurs upstream of the mixing point, i.e., in both channels, and downstream of the mixing point, i.e., in the intake channel. In one design, this uniform pressure is controlled or regulated. Therefore, the pressure applied at the mixing point from at least three sides (from the three channels) is controlled and / or regulated. The objective of this regulation is that the temporal variation curve of the actual pressure at the mixing point follows a predetermined temporal nominal pressure variation curve. A specific case of this regulation objective is that the pressure at the mixing point remains constant over time and should be equal to a predetermined nominal pressure value.

[0063] In one design, the adjustment objective of regulating the actual pressure at the mixing point is an additional control objective in the manipulation of the control pressure actuators. The control device manipulates the two control pressure actuators of the two pressure reducers such that not only the time-varying curves of the actual pressure at the back pressure outlet of the first pressure reducer but also the time-varying curves of the actual pressure at the back pressure outlet of the second pressure reducer follow a predetermined time-varying curve of the pressure at the mixing point. The control device thus manipulates the two control pressure actuators to achieve the additional adjustment objective. The pressure difference between the two channels is rapidly reduced.

[0064] One application of this additional adjustment target is as follows: as already mentioned, the actual volumetric flow rate of the coupling unit flowing towards the patient side should often be adjusted. Therefore, a controllable actuator, particularly a controllable proportional valve, capable of changing the volumetric flow rate is arranged in the inspiratory passage. This actuator can be operated by the control device of the supply assembly according to the invention or other signal processing control device. In one implementation, a pre-pressure occurs at the inlet side and a back pressure occurs at the outlet side of the actuator. The pressure at the mixing point determines the pre-pressure for this actuator, and the back pressure caused by the actuator affects the volumetric flow rate of the coupling unit flowing towards the patient side. If the pre-pressure at the actuator follows a pre-given nominal variation curve, especially if it is constant over time, the volumetric flow rate of the coupling unit flowing towards the patient side can be adjusted more easily. The design just described achieves this.

[0065] In one design, each pressure reducer includes a control pressure chamber, and the control pressure actuator of the pressure reducer is capable of setting, changing, and thereby controlling the control pressure in this control pressure chamber. In one implementation of this design, each pressure reducer includes a controllable fluid guiding unit, such as a pump or piston-cylinder unit. This fluid guiding unit is capable of not only delivering fluid to the control pressure chamber but also discharging fluid from the control pressure chamber. The control device is capable of independently operating the two fluid guiding units and thereby independently changing the control pressure in the two control pressure chambers.

[0066] In a preferred design, each pressure reducer additionally includes a back pressure chamber and a movable wall. The movable wall limits the back pressure chamber. The back pressure chamber of the pressure reducer is connected to a back pressure outlet. The pressure in the back pressure chamber determines the pressure at the back pressure outlet and thereby determines the pressure in the connected first or second channel.

[0067] The movable wall is movable relative to the housing of the pressure reducer, for example, in two opposite directions. The pressure control actuator is capable of moving the movable wall. The pressure control actuator moves the movable wall, thereby changing the pressure in the back pressure chamber and thus changing the pressure at the back pressure outlet.

[0068] The design with movable walls eliminates the need to install the actuator within the back pressure chamber. More precisely, the pressure control actuator can be located entirely outside the back pressure chamber.

[0069] In one design, the movable wall separates the back pressure chamber from the control pressure chamber. This results in pressure compensation, or even pressure balance, between the pressure in the back pressure chamber and the pressure in the control pressure chamber. Preferably, the movable wall fluidly seals the two chambers apart, preventing fluid from flowing from one chamber to the other. The control device can change the pressure in the control pressure chamber and thus change the pressure in the back pressure chamber.

[0070] In a preferred design, a characteristic curve is pre-defined or empirically determined. This characteristic curve is stored in a form that can be measured by a computer. The characteristic curve depicts how the pressure in the back pressure chamber and thus the pressure at the back pressure outlet of the pressure reducer depends on the pressure in the control pressure chamber. Preferably, such a characteristic curve is pre-defined or empirically determined for each pressure reducer and stored in a computer-measurable form in the data memory of the connecting component. The control device can read this data memory and use this characteristic curve to calculate, based on the pressure to be obtained at the back pressure outlet, what control pressure actuator should generate, particularly in the optional control pressure chamber. Based on this control pressure to be generated, the control device calculates the regulatory intervention for controlling the pressure actuator. This design with two characteristic curves eliminates the need to use two pressure reducers with completely identical structures. More precisely, the characteristic curves compensate to some extent for differences in structural type between the two pressure reducers. However, it is also possible, especially when the two pressure reducers have identical structures, for the control device to use the same characteristic curve for both pressure reducers.

[0071] In an extended embodiment of this design, each pressure reducer includes a pre-pressure chamber in addition to a back pressure chamber, and a wall between the back pressure chamber and the pre-pressure chamber. The wall can be rigid or flexible. The pre-pressure chamber is connected to a pre-pressure inlet. An opening is inserted into the wall. This opening establishes a fluid connection between the pre-pressure chamber and the back pressure chamber. A movable closure can optionally close or release this opening. If the closure releases the opening, the gas component can flow from the first or second source through the pre-pressure inlet, pre-pressure chamber, opening, back pressure chamber, and back pressure outlet into the first or second channel. If the pressure in the pre-pressure chamber is greater than the pressure in the back pressure chamber, the pressure difference results in the gas component flowing from the pre-pressure chamber to the back pressure chamber. If the closure closes the opening, the gas component cannot flow from the source into the channel, and the pressure difference is not eliminated.

[0072] In one design, this implementation is associated with a design in which the pressure reducer includes a movable wall. A mechanical action connection is established between the movable wall and the closure, preferably comprising a lever. This mechanical action connection transmits the movement of the movable wall to the closure. This design achieves both short and long lever arms in many cases, thus requiring the control pressure actuator to exert less force than if it were to act directly on the movable wall.

[0073] In many cases, combining the aforementioned control pressure chamber can achieve the following effect: a pressure balance is achieved between the control pressure chamber and the back pressure chamber through pressure compensation. This pressure balance causes a specific position of the movable wall. Based on this position and thus on the pressure balance, the closure is positioned in a specific location and the opening is opened or closed.

[0074] Due to this design, a larger ratio between the two lever arms can be achieved in many cases, especially when the mechanical action connection includes a connecting element capable of rotating around a rotation axis. The actuator moves the movable wall and thereby moves the longer lever arm. The connecting element of the mechanical action connection results in a shorter lever arm between the rotation axis and the closure. Thus, the control pressure actuator only needs to apply a relatively small force to move the closure. In particular, the closure can move in the pre-pressure chamber with a smaller force overcoming a larger force.

[0075] According to the invention, the supply assembly includes two pressure control actuators. In one design described below, the supply assembly includes at least one additional actuator arranged outside the two pressure reducers.

[0076] According to the design scheme with additional actuators, an aerodynamic drag is arranged in at least one channel that guides one of the gas components to the mixing point. Preferably, the aerodynamic drag includes a narrow section, i.e., the region where the cross-sectional flow surface is smaller than in the rest of the channel. The aerodynamic drag value of this drag is variable, particularly by means of corresponding manipulation of the drag by a control device. Preferably, the cross-sectional flow surface can be varied. The aerodynamic drag value is preferably expressed as pressure per volumetric flow rate, for example, in [mbar / (l / min)].

[0077] Increasing the aerodynamic drag value typically reduces the volumetric flow rate through the channel. The drag actuator can change the aerodynamic drag value and, for example, move the element fitted into the channel. The control device can manipulate this drag actuator. The control or regulation objective in this manipulation is that the ratio between the two volumetric flow rates through the two channels equals a predetermined rated ratio. To achieve this control or regulation objective, the control device, according to this design, manipulates the control pressure actuator and additionally manipulates the drag actuator.

[0078] This design scheme is particularly capable of coarse adjustment and regulation of volumetric flow rate by means of a pressure control actuator and fine adjustment and regulation of volumetric flow rate by means of a resistance actuator. In many cases, the control or regulation target can be achieved faster and / or with greater reliability than with only one actuator for the channel.

[0079] It is possible to arrange the pneumatic drag and the controllable drag actuator in only one channel. However, it is preferable to arrange the pneumatic drag and the controllable drag actuator in two separate channels. In this design, the control device can independently operate the two drag actuators and thereby independently change the two pneumatic drag values.

[0080] According to the invention, each pressure reducer includes a control pressure actuator capable of changing the pressure at the back pressure outlet. In one design, the control pressure regulating mechanism changes the control pressure in an optional control pressure chamber. In one implementation of this design, the two control pressure actuators are adjusted such that they each induce an initial control pressure in the control pressure chamber. Particularly preferred is that the two control pressure actuators are configured such that if the two control pressure actuators induce their respective initial control pressures and no gas flows through the pressure reducer, then the same pressure exists at the two back pressure outlets of the two pressure reducers.

[0081] This design compensates for potential design-related differences between the two pressure regulators. It eliminates the need to design and manufacture two pressure regulators that are precisely identical. Because the same pressure is applied at both back pressure outlets when there is no gas flow, pressure control or regulation is simpler in many situations.

[0082] In one design, the volumetric flow rate of the coupling unit flowing towards the patient side via the inspiratory channel is regulated. For this purpose, a controllable actuator, preferably a controllable proportional valve or other valve, is arranged in the inspiratory channel. The actuator is capable of changing the volumetric flow rate of the coupling unit flowing towards the patient side. A control device is capable of operating this actuator. A predetermined nominal variation curve over time for the volumetric flow rate of the coupling unit flowing towards the patient side is given. The control device controls the actuator with an adjustment target that the actual temporal variation curve of the volumetric flow rate of the coupling unit flowing towards the patient side follows the predetermined nominal variation curve.

[0083] In an extension of this design, a volumetric flow sensor measures a quantity of volumetric flow, such as differential pressure, used for coupling the actuator to the patient side.

[0084] The present invention also relates to a system capable of providing a gas mixture to a patient-side coupling unit. The system includes a supply assembly according to the invention, a first source, and a second source. The first source is capable of providing a first gas component, and the second source is capable of providing a second gas component. A fluid connection is at least temporarily established between the pre-pressure inlet of the first pressure reducer and the first source. A fluid connection is also at least temporarily established between the pre-pressure inlet of the second pressure reducer and the second source. A fluid connection is also at least temporarily established between the inhalation channel and the patient-side coupling unit. Attached Figure Description

[0085] The invention will now be described with the aid of embodiments. Here:

[0086] Figure 1 The diagram schematically illustrates how a gas mixture consisting of breathing air and pure oxygen is supplied to the patient-side coupling unit, using two pressure reducers with two operable actuators.

[0087] Figure 2 The curves showing the time-varying volumetric flow rate and pressure of the gas mixture flowing to the patient are presented;

[0088] Figure 3 A pneumatic pressure reducer with a controlled actuator is schematically shown in the control pressure chamber.

[0089] Figure 4 A pneumatic pressure reducer with a controlled actuator is schematically shown in a back pressure chamber;

[0090] Figure 5 An exemplary correlation between the obtained back pressure and volumetric flow rate is shown;

[0091] Figure 6An exemplary correlation between the obtained back pressure and the applied control pressure is shown;

[0092] Figure 7 An illustrative example shows how a balance of two volumetric flow rates can occur after adjusting two control pressures in two pressure reducers;

[0093] Figure 8 Another illustration shows Figure 7 Examples;

[0094] Figure 9 An alternative implementation is shown, in which two operable actuators are used for two variable pneumatic drags in two channels.

[0095] Figure 10 Exemplary illustration in regulation Figure 9 How can the balance of two volumetric flow rates occur after two aerodynamic resistances? Detailed Implementation

[0096] In this embodiment, the present invention is used to perform artificial respiration on a patient, Pt. The coupling unit 9 on the patient side, such as a breathing mask, tube, or catheter, is secured to or inside the patient's body.

[0097] The ventilator 100, shown only schematically, performs a series of breathing cycles and delivers a certain amount of gas mixture to the coupling unit 9 on the patient side and thereby to the patient Pt in each breathing cycle. This gas mixture contains a certain proportion (Vol-%) of oxygen, which is predetermined by the user. This oxygen proportion can be higher than the oxygen proportion in breathing air. To increase the oxygen proportion compared to the proportion in breathing air, a gas mixture consisting of breathing air and pure oxygen is generated in this embodiment. The gas mixture can additionally contain an anesthetic, thereby sedating or anesthetizing the patient Pt.

[0098] The supply component according to the invention is part of or constitutes the respirator 100. The supply component according to the invention will be indicated by reference numeral 100 in the accompanying drawings.

[0099] The user pre-determines the desired oxygen content in the gas mixture. For example, the user manually sets the desired oxygen content on knob 30.

[0100] Figure 1The supply assembly is schematically shown for generating this gas mixture with a high oxygen content and delivering it to the patient-side coupling unit 9. The two components of the gas mixture, namely air and pure oxygen (O2), are provided in two channels K.1 and K.2, wherein the first channel K.1 provides air and the second channel K.2 provides pure oxygen, and wherein the two channels K.1 and K.2 converge at a mixing point 8. An inhalation channel K.3, such as a flexible inhalation tube and optionally a double-lumen tube, guides from this mixing point 8 to the patient-side coupling unit 9. This inhalation channel K.3 guides the mixture of air and pure oxygen from the mixing point 8 to the patient-side coupling unit 9.

[0101] A controllable actuator in the form of a valve 4 is arranged in the inspiratory passage K.3, which is a proportional valve in a preferred design. This proportional valve 4 has a pre-pressure on the inlet side and a back pressure on the outlet side and is capable of controlling the volumetric flow rate to the coupling unit 9 on the patient side, and divides the inspiratory passage K.3 into a section 41 between the mixing point 8 and the proportional valve 4 and a section 42 between the proportional valve 4 and the coupling unit 9 on the patient side.

[0102] Because these two channels K.1 and K.2 lead to the same mixing point 8, and because the intake channel K.3 begins at this mixing point 8, the same pressure P exists in these two channels K.1 and K.2 upstream of the mixing point 8, and in section 41 of the intake channel K.3. This pressure P should be between 20 mbar and 100 mbar. This value represents the overpressure relative to ambient pressure. In one design, this pressure P should be constant over time. The pressure P is the pre-pressure at the proportional valve 4.

[0103] Volumetric flow rate Vol' Pt (t), that is, the flow rate of gas through section 42 of the inhalation channel K.3 to the coupling unit 9 on the patient side per unit time, should follow a pre-defined time-varying curve. The pressure in section 42 also varies with time. Figure 2 The volumetric flow rate (Vol') is shown above. Pt An exemplary curve showing the required change over time is provided, and the pressure (P) is shown below. pt An exemplary time-varying curve of the gas mixture is shown. The values ​​above the x-axis represent the flow rate of the gas mixture towards the patient Pt (inhalation), while the values ​​below the x-axis represent the flow rate away from the patient Pt (exhalation).

[0104] The time-varying curve of the actual volumetric flow rate of coupling unit 9 flowing towards the patient side (Vol') Pt (t) should follow the pre-given time-dependent variation curve Vol'Pt,Soll (t). This rated variation curve Vol' Pt,Soll (t) may depend on the patient Pt's own respiratory activity. For example, each inhalation by the patient Pt triggers a respiratory stroke. Therefore, the control device 3, which processes the signal, automatically adjusts the volumetric flow rate Vol'. Pt (t) Implement regulation (closed-loop control). The actual time-varying volumetric flow rate Vol' in section 42. Pt (t) is the adjustment parameter, and the nominal change curve Vol' over a predetermined time. Pt,Soll (t) is the command parameter. The control device 3 manipulates the proportional valve 4 in the intake channel K.3 so as to use the time-varying curve Vol' of the actual volumetric flow rate. Pt (t) equals the nominal change curve Vol' over time. Pt,Soll (t) This adjustment target is used to change the volumetric flow rate through section 42.

[0105] In this embodiment, the breathing stroke is achieved by providing two gas components under overpressure, and the control device 3 actuates the proportional valve 4, which in turn changes the volumetric flow rate through section 42 of the inspiratory passage K.3. The gas mixture should have a constant oxygen fraction over time. While the proportional valve 4 can control the volumetric flow rate, it cannot control the oxygen fraction. Therefore, despite the variable volumetric flow rate, the oxygen content throughout the inspiratory passage K.3 should remain constant.

[0106] The volumetric flow rate Vol'(t) from mixing point 8 to proportional valve 4 through intake channel K.3 is the sum of the volumetric flow rate Vol'[1](t) of breathing air through first channel K.1 to mixing point 8 and the volumetric flow rate Vol'[2](t) of pure oxygen (O2) through second channel K.2 to mixing point 8. A first volumetric flow sensor 6.1 measures the volumetric flow rate Vol'[1](t) through first channel K.1, and a second volumetric flow sensor 6.2 measures the volumetric flow rate Vol'[2](t) through second channel K.2. In the example shown, a first pneumatic resistance 5.1 is arranged in first channel K.1, and a second pneumatic resistance 5.2 is arranged in second channel K.2. The resistance value of the first pneumatic resistance 5.1 is represented by R1, and the resistance value of the second pneumatic resistance 5.2 is represented by R2. The flow cross-sectional area of ​​the aerodynamic drag rings 5.1 and 5.2 is smaller than that of the rest of the channels K.1 and K.2. This smaller flow cross-sectional area is constant in one design scheme and variable in another, as will be described below.

[0107] The first volumetric flow sensor 6.1 measures the pressure difference ΔP.1 at the first aerodynamic resistance 5.1 and derives the volumetric flow rate Vol'[1](t) through the first channel K.1 from the measured pressure difference. The second volumetric flow sensor 6.2 measures the pressure difference ΔP.1 at the second aerodynamic resistance 5.2 and derives the volumetric flow rate Vol'[2](t) through the second channel K.2 from the measured pressure difference. The control device 3 obtains signals from the two volumetric flow sensors 6.1 and 6.2 respectively and derives the actual time-varying volumetric flow rate Vol'(t) through the section 41 of the intake channel K.3 and the two volumetric flow rate ratios Vol'[1](t) / Vol'[2](t).

[0108] Pressure sensor 7 measures the actual pressure in the inspiratory passage K.3. The signal from pressure sensor 7 is also transmitted to control device 3. The signal from pressure sensor 7 is used for pressure regulation as described below. The signal from pressure sensor 7 may additionally, generally together with signals from other sensors, be used to at least approximately determine a measure of the patient Pt's own respiratory activity, such as pressure in the airway.

[0109] In this embodiment, a fixed supply connector 20 located in the wall W provides breathing air, and a fixed supply connector 21 provides pure oxygen. The supply connectors 20 and 21 provide air or oxygen with a pressure between 3 bar and 8 bar. However, the consistent pressure in the two channels K.1 and K.2 should be between 20 mbar and 100 mbar. Therefore, a first pneumatic pressure reducer 1 is arranged between the supply connector 20 and the first channel K.1, and a second pneumatic pressure reducer 2 is arranged between the supply connector 21 and the second channel K.2. The first pressure reducer 1 includes a pre-pressure inlet V.1 and a back pressure outlet H.1, and the second pressure reducer 2 includes a pre-pressure inlet V.2 and a back pressure outlet H.2. The pre-pressure inlet V.1 is connected to the supply connector 20 via a supply line 22, and the pre-pressure inlet V.2 is connected to the supply connector 21 via a supply line 23. A check valve 24 is arranged in the supply line 22 to prevent breathing air from flowing back to the supply connector 20. The corresponding check valve 25 is arranged in the supply line 23.

[0110] As already mentioned, Vol'(t) = Vol'[1](t)+Vol'[2](t) applies. Here

[0111] - Vol'(t) is the volumetric flow rate that varies over time through section 41 of the intake channel K.3.

[0112] - Vol'[1](t) is the time-varying volumetric flow rate of the breathing air through the first channel K.1, and

[0113] - Vol'[2](t) is the time-varying volumetric flow rate of pure oxygen through the second channel K.2.

[0114] The two volumetric flow rates Vol'[1](t) and Vol'[2](t) through the two channels K.1 and K.2 depend on the adjustment of the proportional valve 4, wherein this adjustment determines the volumetric flow rate Vol'(t) through section 41 and the volumetric flow rate Vol' through section 42. Pt (t).

[0115] The oxygen content Vol-%[O2_K3] in the inhalation channel K.3 at time t (more precisely at the mixing point 8) is

[0116] .

[0117] In this case, Vol-%[O2_Luft] is the volume percentage of oxygen in the breathing air supplied by the supply connector 20, and this percentage is approximately 21%. The supply connector 21 supplies pure oxygen. In one application, the required oxygen content Vol-%[O2_K.3] in the gas mixture reaching the coupling unit 9 on the patient side is predetermined, along with the time-constant rated pre-pressure P at the proportional valve 4 and the actual volumetric flow rate Vol'. Pt The nominal variation curve of (t) Vol' Pt,Soll (t).

[0118] The required nominal ratio between the two volumetric flow rates Vol'[1](t) and Vol'[2](t) through the two channels K.1 and K.2 is generated from the required oxygen content Vol-%[O2_K.3]. In one design, the corresponding oxygen content in the gas or gas mixture supplied by the two supply connectors 20 and 21 is considered to be known and constant. In another design, variation over time is taken into account. An optional concentration sensor 37 measures the actual oxygen content in the gas mixture through the intake channel K.3.

[0119] The oxygen content Vol-%[O2_K.3] and the resulting ratio Vol'[1](t) / Vol'[2](t) should generally be constant over time. The control device 3 automatically adjusts the volumetric flow rates in the two channels K.1 and K.2. The objective of this adjustment is to keep the ratio between the two volumetric flow rates Vol'[1](t) and Vol'[2](t) in the two channels K.1 and K.2 constant, and more precisely, even if the volumetric flow rate Vol'(t) in section 41 of the inhalation channel K.3 changes.

[0120] In one variant, the possibility that the oxygen content in the gas from supply connectors 20 and 21 may deviate from the rated oxygen content is considered. To compensate for this deviation, the control device 3 increases or decreases the volumetric flow rate through one of the channels K.1 or K.2 according to whether the oxygen content should be increased or decreased.

[0121] Another adjustment objective of the control device 3 is as follows: as already mentioned, the pressure in section 41 of the intake channel K.3, located between the mixing point 8 and the proportional valve 4, is consistent with the pressure in the section of the first channel K.1 between the pneumatic resistance 5.1 and the mixing point 8, and with the pressure in the section of the second channel K.2 between the pneumatic resistance 5.2 and the mixing point 8. This consistent pressure P should remain constant over time or follow a predetermined time-varying curve.

[0122] To achieve these two regulation objectives, the two pressure reducers 1 and 2 each include a controllable actuator, referred to as a control pressure actuator. The result of manipulating these control pressure actuators is to change the back pressure reached at the back pressure outlets H.1 or H.2, respectively. If the pressure at the back pressure outlet H.1 increases or decreases while the pressure at the back pressure outlet H.2 remains the same, then the volumetric flow rate Vol'[1](t) through the first channel K.1 increases or decreases. This applies accordingly to the back pressure outlet H.2. The control pressure actuators of the two pressure reducers 1 and 2 will be described below.

[0123] Figure 3 and Figure 4 Two exemplary design schemes for the first pressure reducer 1 are shown. The same reference numerals have the same... Figure 1 The same meaning as in [the previous sentence]. The second pneumatic pressure reducer 2 can be used with [the following text is incomplete and likely refers to a different context]. Figure 3 or Figure 4 The configuration is exactly the same as shown.

[0124] A rigid housing 19 surrounds the interior of the first pressure reducer 1. (According to...) Figure 3In the design scheme, three rooms are formed inside, that is...

[0125] - The pre-pressure chamber Ka.1 is fluidly connected to the supply line 22 via the pre-pressure inlet V.1.

[0126] - Back pressure chamber Ka.2, which is fluidly connected to the first channel K.1 via back pressure outlet H.1, and

[0127] - Control pressure chamber Ka.3.

[0128] The partition wall 15 in the pressure reducer 1 separates the back pressure chamber Ka.2 from the pre-pressure chamber Ka.1. Preferably, the partition wall 15 is rigid. The opening 26 is milled into the partition wall 15. The spring-loaded closure 13 is oriented in two opposite directions relative to the partition wall 15 (in... Figure 3 It can move linearly (vertically upwards and downwards) and can release or close this opening 26.

[0129] The movable wall 12 is fastened inside the housing 19 of the pressure reducer 1 and separates the control pressure chamber Ka.2 and the back pressure chamber Ka.3. Therefore, the back pressure chamber Ka.3 is defined by the partition wall 15, the movable wall 12, and the housing 19 of the pressure reducer 1. In this embodiment, the movable wall 12 is in the form of a flexible diaphragm. In one design, the diaphragm 12 includes a center-arranged fixed plate. The movable wall 12 can also be in the form of a rigid plate, which is vertically movable relative to the housing 19 in two directions. Preferably, the movable wall 12 separates the two chambers Ka.2 and Ka.3 from each other in a fluid-tight manner, except for unavoidable non-sealing.

[0130] Lever 14 is rotatable about the rotation axis DA and is positioned above the movable wall 12, optionally above the fixed plate. The closure 13 is positioned above the lever 14. (As in...) Figure 3 As can be seen, a short lever arm is formed between the support point of the rotating shaft DA and the closure 13, and a long lever arm is formed between the rotating shaft DA and the support point of the lever 14 on the diaphragm 12.

[0131] The pressure in the back pressure chamber Ka.2 acts on the movable wall 12 from one side, while the pressure in the control pressure chamber Ka.3 and the control pressure actuator described below in the control pressure chamber Ka.3 act on the movable wall 12 from the other side. Therefore, a force and thus a pressure act on the movable wall 12 from both sides. Because the wall 12 is movable, a balance is achieved between the two forces and therefore the two pressures. This balance results in a specific position for the movable wall 12. This position is transmitted to the closure 13 via the lever 14, causing the closure 13 to move.

[0132] In the illustrated implementation, the mechanical or pneumatic spring 16 in the control pressure chamber Ka.3 is part of the control pressure actuator that acts from the control pressure chamber Ka.3 onto the movable wall 12. The spring 16 is connected to the movable wall 12 on one side and to a connecting element 18 on the other. An actuated actuator 17, such as a hydraulic pump or piston-cylinder unit, is supported on the housing 19 of the pressure reducer 1 and acts on the connecting element 18 from one side. The actuator 17 can change the distance between the connecting element 18 and the housing of the pressure reducer 1, and thus also change the force of the spring 16. The closer the connecting element 18 is to the movable wall 12, the greater the spring force of the spring 16. The movement of the actuator 17 changes the force and thus changes the control pressure present in the control pressure chamber Ka.3 and acting on the movable wall 12.

[0133] In the illustrated implementation, the spring 16 and the actuator 17 are connected in series. Alternatively, the spring 16 and the actuator 17 may be connected in parallel, and the actuator 17 may therefore act directly on the diaphragm 12.

[0134] In an alternative design (not shown), the spring 16 in the control pressure chamber Ka.3 is omitted. The manipulated actuator 17 acts directly on the movable wall 12.

[0135] according to Figure 4 The pressure reducer 1 does not include the back pressure chamber and the moving wall. The same reference numerals have the same... Figure 3 The same meaning applies. The control pressure actuator 17 is located in the back pressure chamber Ka.2 and is mechanically connected to the closure 13 via the connecting element 18. The control pressure actuator 17 can directly move the closure 13 in two opposite vertical directions, thereby moving the closure 13 to the release position or the closed position.

[0136] Ideally, the pre-pressure chamber Ka.1 contains the same pressure as that in the supply line 22, preferably between 3 bar and 8 bar, and thus several times higher than the consistent pressure in the two channels K.1 and K.2. Pressure is generated in the back pressure chamber Ka.2, and the first channel K.1 uses this pressure to supply breathing air. Therefore, the pressure in the first channel K.1 is equal to the pressure in the back pressure chamber Ka.2, at least in the section downstream of the back pressure outlet H.1.

[0137] As described above, the control device 3 is capable of manipulating the actuator 17, which performs operations according to... Figure 3The design scheme alters the pressure in the control pressure chamber Ka.3. This pressure is hereinafter referred to as the control pressure. After the control pressure is changed, a start-up phase typically occurs until the pressures in the back pressure chamber Ka.3 and the control pressure chamber Ka.2 are back in equilibrium. Depending on the position of the movable wall 12, the closure 13 opens or closes the opening 26 in the partition wall 15, thereby allowing or preventing breathing air from the supply line 22 from flowing through the first pressure reducer 1 into the first channel K.1. When the pressure in the back pressure chamber Ka.2 is sufficiently high, the movable wall 12 causes the closure 13 to close the opening 26.

[0138] The back pressure P generated by the pneumatic pressure reducer 1 at the back pressure outlet H.1 hin Ideally, it does not depend on the volumetric flow rate Vol'[1](t) downstream of the pressure reducer 1. Figure 5 An example is shown, in practice, the back pressure P generated. hin How it depends on the volumetric flow rate Vol'[1](t) entering the first channel K.1 from the pressure reducer 1. The volumetric flow rate Vol'[1] in [l / min] is plotted on the x-axis, and the back pressure P in [mbar] is plotted on the y-axis. hin [1]. Characteristic curve P auf This shows the back pressure P that depends on the volumetric flow rate Vol'[1] as the volumetric flow rate Vol'[1] increases. hin [1], characteristic curve P ab This shows the back pressure P that depends on the volumetric flow rate Vol'[1] as the volumetric flow rate Vol'[1] decreases. hin [1]. Therefore, the correlation describes a hysteresis. The control pressure, i.e., the pressure in the control pressure chamber Ka.3, remains constant. The two characteristic curves P auf and P ab Ideally they are horizontal, but in practice they decrease as the volumetric flow rate increases. This is due to the pressure loss inside the pressure reducer 1, which depends on the volumetric flow rate Vol'[1] in an approximately quadratic manner, and the fact that the stress and thus the force of the spring 16 decrease when a fluid connection is established between the pre-pressure inlet V.1 and the back pressure outlet H.1.

[0139] Figure 6 The back pressure P obtained when the volumetric flow rate Vol'[1] is constant is shown. hin [1] The control pressure P generated in the control pressure chamber Ka.2 of the first pressure reducer 1 is dependent on the control pressure P. con [1]. The control pressure P, in units of [mbar], is plotted on the x-axis. con [1] Plot the back pressure P in [mbar] on the y-axis.hin [1].

[0140] As already mentioned, the control device 3 is capable of manipulating the actuator 17 in the first pressure reducer 1 and the corresponding actuator in the second pressure reducer 2. This manipulation results in the control pressure in the control pressure chamber Ka.3 increasing when the volumetric flow rate increases and decreasing again when the volumetric flow rate decreases. This manipulation causes the back pressure to... Figure 6 The changes shown and to some extent compensated Figure 5 The correlation is shown.

[0141] Figure 7 This illustrates how equilibrium is achieved after control pressures have been set in the two control pressure chambers of the two pressure reducers 1 and 2, respectively. The volumetric flow rates Vol'[1] and Vol'[2] through the back pressure outlets H.1 or H.2 are plotted on the x-axis, and the pressure P at the back pressure outlets H.1 or H.2 is plotted on the y-axis. hin [1] and P hin [2]. In the example shown, the control pressure in the second pressure reducer 2 is greater than the control pressure in the first pressure reducer 1. P hin [1](Vol') represents the following characteristic curve, which depicts the back pressure at the back pressure outlet H.1 as a function of the volumetric flow rate through the back pressure outlet H.1. This characteristic curve is generated by the control pressure set in the first pressure reducer 1. P hin [2](Vol') correspondingly represents the characteristic curve of the back pressure at the back pressure outlet H.2.

[0142] Due to the higher control pressure, the pressure at back pressure outlet H.2 is greater than the pressure at back pressure outlet H.1, assuming the same volumetric flow rate. The two pressures P at the two back pressure outlets H.1 and H.2 are... hin [1] and P hin [2] is the same because the two channels K.1 and K.2 lead to the same mixing point 8. As a result, the volumetric flow rate in the second channel K.2 is greater than the volumetric flow rate in the first channel K.1. The two generated volumetric flow rates Vol'(1) and Vol'(2) ​​through the two back pressure outlets H.1 and H.2 are shown.

[0143] Figure 8 This balance is illustrated in another diagram. The corresponding volumetric flow rate is plotted on the x-axis and the corresponding back pressure on the y-axis. However, the x-axis for the volumetric flow rate Vol'[2] through the back pressure outlet H.2 extends from right to left. Characteristic curve P hin [2](Vol') correspondingly decreases from right to left. The two characteristic curves Phin [1](Vol') and P hin [2] The intersection point S of (Vol') represents the uniform pressure P generated. hin [1]=P hin [2] and the two generated volumetric flow rates Vol'[1] and (Vol')[2].

[0144] The following describes, exemplarily, the adjustment of the ratio of the two volumetric flow rates, Vol'[1](t) / Vol'[2](t), and the pressure P in section 41, see [link to relevant documentation]. Figure 1 In this example, the pressure in the region between the two pneumatic resistances 5.1 and 5.2 on one hand and the proportional valve 4 on the other hand should be maintained constant over time at P0 in [mbar]. This pressure P0 can also be referred to as the pre-pressure for the proportional valve 4. Furthermore, the maximum achievable volumetric flow rate Vol' through the intake passage K.3 is predetermined. max The volumetric flow rate varies from the rated flow rate curve Vol' Soll,Pt It is generated in (t).

[0145] The two springs 16 in the two control pressure chambers Ka.3 of the pressure reducers 1 and 2 are capable of generating control pressure without the support of an actuator, which causes a consistent back pressure P0 in [mbar]. Feder The two controllable actuators 17 can increase the obtained back pressure to a maximum P0. Stell (t) (in [mbar]). The spring 16 and actuator 17 are thus adjusted to achieve the desired pressure P0 for both. Feder and P0 Stell (t) applies to:

[0146] and .

[0147] Through the design of the supply component 100, the total resistance value R1 of the two pneumatic components is obtained. fix and R2 fix It is known. The total aerodynamic drag values ​​depend on the volumetric flow rate Vol'[1](t) or Vol'[1](t) through the first channel K.1 or through the second channel K.2, and are preferably expressed in [mbar / (l / min)]. The total drag value R1 fix This includes the resistance value of the pneumatic resistance element 5.1, the internal pneumatic resistance of the pressure reducer 1, and other pneumatic resistances between the back pressure outlet K.2 and the proportional valve 4. This applies accordingly to the total resistance value R2. fix .

[0148] As described above, the user pre-determines the desired proportion of pure oxygen in the gas mixture, Vol-%[O2_K.3], which flows through the inhalation channel K.3 to the coupling unit 9 on the patient side. A nominal ratio Vol'[1](t) / Vol'[2](t) is generated from this desired oxygen proportion, Vol-%[O2_K.3]. Two volumetric flow sensors, 6.1 and 6.2, measure the volumetric flow rates Vol'[1](t) and Vol'[2](t).

[0149] By manipulating the actuator 17 in the first pressure reducer 1 in this way, the resulting control pressure causes back pressure.

[0150]

[0151] This back pressure should be equal to the pre-given pre-pressure P0 used for proportional valve 4.

[0152] As is generally known from the design of the pressure reducer 1, the back pressure P at the back pressure outlet H.1 is... hin [1] How this depends on the control pressure in the control pressure chamber Ka.3, see [link to relevant documentation]. Figure 6 Based on this correlation, the control device 3 derives control commands for the actuator 17. Furthermore, the volumetric flow sensor 6.1 measures the actual volumetric flow rate Vol'[1](t) through the first channel K.1, the pressure sensor 7 measures the pressure in the intake channel K.3, and the control device 3 changes the operation of the actuator 17 and thereby changes the volumetric flow rate Vol'[1](t) through the first channel K.1 when necessary.

[0153] This correspondingly applies to the operation of the actuator 17 in the second pressure reducer 2. The obtained back pressure is

[0154]

[0155] And it should be equal to the prepressure P0 on the proportional valve 4.

[0156] According to the design scheme just described, the two pressure reducers 1 and 2 each include an actuator that can change the pressure in the control pressure chamber. Figure 9 It shows according to Figure 1 A variation of the design scheme. According to this variation, the supply assembly 100 includes two additional actuators 27.1 and 27.2. These additional actuators 27.1 and 27.2 are arranged outside the two pressure reducers 1 and 2.

[0157] The drag actuator 27.1, for example a dual-function piston-cylinder unit, can change the cross-sectional area of ​​the pneumatic drag 5.1 in the first channel K.1 and thus change its pneumatic drag value R1. The control device 3 can operate the actuator 27.1. If the cross-sectional area is changed, the volumetric flow rate Vol'[1](t) through the pneumatic drag 5.1 and through the first channel K.1 is also changed. The smaller the cross-sectional area, the greater the pneumatic drag and the smaller the volumetric flow rate Vol'[1](t). The drag value actuator 27.2 can correspondingly change the cross-sectional area of ​​the pneumatic drag 5.2 in the second channel K.2 and thus change its pneumatic drag value R2. The control device 3 can also operate the drag value actuator 27.2.

[0158] Figure 10 Show how to follow Figure 9 A balance was achieved in the design scheme. The chosen scheme... Figure 7 The display format. In this design, adjustments are performed before first use. After such adjustments, the two control pressures of the two pressure reducers 1 and 2 are set such that if the volumetric flow rates Vol'[1](t) and Vol'[2](t) through the two back pressure outlets H.1 and H.2 are both equal to the reference back pressure, for example, equal to zero, then the same back pressure appears at the two back pressure outlets H.1 and H.2. This initial adjustment compensates for possible differences between the two pressure reducers 1 and 2 caused by their structural types. Figure 10 The diagram is generated by the following adjustments: the actuator 27.1 adjusts the pneumatic resistance 5.1 in the first channel K.1 to a resistance value R1, and the actuator 27.2 adjusts the pneumatic resistance 5.2 in the second channel K.2 to a resistance value R2. R1 is greater than R2. As a result, the volumetric flow rate Vol'[1](t) through the first channel K.1 is smaller than the volumetric flow rate Vol'[2](t) through the second channel K.2.

[0159] Therefore, according to Figure 9 The design provides a combination of two actuators for each channel K.1 and K.2, namely an actuator that changes the control pressure in the control pressure chamber Ka.3 and an actuator that changes the aerodynamic resistance values ​​R1 and R2. In some cases, this combination allows for faster adjustment of the volumetric flow rates Vol'[1](t) and Vol'[2](t) through the two channels K.1 and K.2. Thus, the volumetric flow rate Vol' generated by the gas mixture through the intake channel K.3 can also be adjusted more quickly. Pt (t). Furthermore, in some cases, multiple regulation objectives can be achieved with greater reliability and / or smaller regulation deviations, particularly the following two:

[0160] - The ratio between the actual volumetric flow rate Vol'[1](t) through the first channel K.1 and the actual volumetric flow rate Vol'[2](t) through the second channel K.2 remains constant, and

[0161] -The two pressures P at the back pressure outlets H.1 and H.2 hin [1] and P hin [2] Keep constant or follow a predetermined time-varying curve.

[0162] List of reference numerals:

[0163] 1 The first pressure reducer for the first channel K.1 includes a pre-pressure inlet V.1 and a back pressure outlet H.1. 2 The second pressure reducer for the second channel K.2 includes a pre-pressure inlet V.2 and a back pressure outlet H.2. 3 The control equipment processes the signals, obtains measured values ​​from sensors 6.1, 6.2, and 7, and controls the proportional valve 4. 4 The proportional valve changes the volumetric flow rate in the intake channel K.3 and is controlled by the control device 3. 5.1 The constant aerodynamic drag in the first channel K.1 5.2 The constant aerodynamic drag in the second channel K.2 6.1 The volumetric flow sensor measures the pressure difference ΔP.1 at the aerodynamic drag 5.1 and derives the volumetric flow rate through the first channel K.1. 6.2 A volumetric flow sensor measures the pressure difference ΔP.2 at the aerodynamic drag 5.2 and derives the volumetric flow rate through the second channel K.2. 7 Pressure sensor, measures the pressure in the intake channel K.3 8 A mixing point, into which the two channels K.1 and K.2 converge, and where a third channel K.3 begins. 12 The movable wall in the form of a diaphragm in pressure reducer 1 separates chambers Ka.2 and Ka.3 from each other. 13 A closure element that selectively opens or closes the opening 26 in the partition wall 15 between the two chambers Ka.1 and Ka.2. 14 The lever, connected to the movable wall 12 and the closure 13, can rotate around the rotation axis DA. 15 The partition wall separating the two chambers Ka.1 and Ka.2 in the pressure reducer 1 has an opening 26 that can be closed by a closure member 13. 16 The spring is connected to the movable wall 12 and to the connecting element 18. 17 The actuator, which moves the connecting element 18 and thereby changes the force of the spring 16, is controlled by the control device 3 and acts as a control pressure actuator. 18 Mechanical connection element between actuator 17 and spring 16 19 The rigid housing of pressure reducer 1 surrounds three chambers Ka.1, Ka.2, and Ka.3. 20 The supply connector in wall W provides breathing air at a pressure between 3 bar and 8 bar. 21 The supply connector in wall W provides pure oxygen at a pressure between 3 bar and 8 bar. 22 The air supply line for breathing runs from supply connector 20 to pre-pressure inlet V.1 23 The supply line for pure oxygen runs from supply connector 21 to the pre-pressure inlet V.2. 24 Check valve in supply line 22 25 Check valve in supply line 23 26 The opening in the separable 15 can be closed by the closure 13. 27.1 A controllable drag actuator that changes the cross-sectional area of ​​the pneumatic drag valve 5.1 and thereby changes the aerodynamic drag value R1. 27.2 A controllable drag actuator that changes the cross-sectional area of ​​the pneumatic drag valve 5.2 and thereby changes the aerodynamic drag value R2. 30 The user can turn the knob to pre-determine the required oxygen content in the gas mixture delivered to the coupling unit 9 on the patient side. 37 Optional concentration sensor in inhalation channel K.3 41 The first section of the intake passage K.3 leads from the mixing point 8 to the proportional valve 4. 42 The second section of the inspiratory passage K.3 connects to the coupling unit 9 on the patient side via the proportional valve 4. 100 A supply assembly (100) that guides a gas mixture consisting of air and pure oxygen to a coupling unit 9 on the patient side includes pressure reducers 1 and 2, channels K.1, K.2 and K.3, actuators for pneumatic resistance devices 5.1 and 5.2, 27.1 and 27.2, sensors 6.1, 6.2 and 7, and supply lines 22 and 23. H.1 Back pressure outlet of the first pressure reducer 1 H.2 Back pressure outlet of the second pressure reducer 2 K.1 The first channel guides breathing air from the back pressure outlet H.1 to the mixing point 8. K.2 The second channel guides pure oxygen from the back pressure outlet H.2 to the mixing point 8. K.3 The inspiratory channel guides a gas mixture consisting of breathing air and pure oxygen to the patient-side coupling unit 9. Ka.1 The pre-pressure chamber in pressure reducer 1 is connected to the supply line 22 via the pre-pressure inlet V.1. Ka.2 The back pressure chamber in pressure reducer 1 is connected to the first channel K.1 via the back pressure outlet H.1. Ka.3 The control pressure chamber in pressure reducer 1 generates control pressure. P pressure P0 The prepressure applied to proportional valve 4 should be kept constant over time. <![CDATA[P0 Feder ]]> Back pressure, which is caused by the control pressure generated by spring 16 in the control pressure chamber Ka.3. <]]> A time-variable back pressure, caused by a control pressure generated by a controllable actuator 17 in the control pressure chamber Ka.3. <![CDATA[P ab ]]> Correlation between back pressure P and volumetric flow rate Vol' as the volumetric flow rate Vol' decreases <![CDATA[P auf ]]> Correlation between back pressure P and volumetric flow rate Vol' as volumetric flow rate Vol' increases <![CDATA[P con [1]]]> The control pressure generated in the control pressure chamber Ka.3 <![CDATA[P hin ]]> back pressure <![CDATA[P hin [1]]]> Back pressure at back pressure outlet H.1 <![CDATA[P hin [2]]]> Back pressure at back pressure inlet H.2 <]]> The characteristic curve, which depicts the back pressure at the back pressure outlet H.1 as a function of the volumetric flow rate through the back pressure outlet H.1, illustrates the back pressure at the back pressure outlet H.1. <]]> The characteristic curve, which depicts the back pressure at the back pressure outlet H.2 as a function of the volumetric flow rate through the back pressure outlet H.2, illustrates the back pressure at the back pressure outlet H.2. ΔP.1 The pressure difference at the aerodynamic drag valve 5.1, measured by sensor 6.1. ΔP.1 The pressure difference across the aerodynamic drag valve 5.2 is measured by sensor 6.2. Pt The patient receiving artificial respiration is connected to the coupling unit 9 on the patient side. R1 The aerodynamic drag value of the first aerodynamic drag resistor 5.1 <![CDATA[R1 fix ]]> Total aerodynamic drag value of the first channel K.1 R2 The aerodynamic drag value of the second aerodynamic drag element 5.2 <![CDATA[R2 fix ]]> The total aerodynamic drag value of the second channel K.2 S < and P hin [2](Vol’)]]> V.1 The pre-pressure inlet of the first pressure reducer 1 V.2 The pre-pressure inlet of the second pressure reducer 2 Vol'(t) The time-variable volumetric flow rate of section 41 from intake channel K.3 to proportional valve 4 is equal to Vol'[1](t)+Vol'[2](t). Vol'[1](t) The time-variable volumetric flow rate through the first channel K.1 Vol'[2](t) The time-variable volumetric flow rate through the first channel K.2 <![CDATA[Vol’ Pt (t)]]> The volumetric flow rate is adjusted by means of the proportional valve 4 via the time-variable volumetric flow rate of the section 42 from the proportional valve 4 to the patient-side coupling unit 9. <![CDATA[Vol’ Pt,Sol l (t)]]> <![CDATA[For a predefined rated variation curve of the volumetric flow Vol’ Pt (t) through section 42]]> W The wall has two fixed supply connectors 20 and 21.

Claims

1. A supply assembly (100) for supplying a gas mixture to a patient-side coupling unit (9), the gas mixture comprising a first gas component and a second gas component, wherein the patient-side coupling unit (9) being connected or at least temporarily connectable to a patient (Pt), wherein the supply assembly (100) comprises - a first channel (K.1), - a second channel (K.2), - a mixing point (8), - an inhalation channel (K.3), - a first pressure reducer (1), - a second pressure reducer (2), and - a control device (3) for processing signals, wherein each pressure reducer (1, 2) comprises - a pre-pressure inlet (V.1, V.2), - a back-pressure outlet (H.1, H.2), and - a control pressure actuator (16, 17), wherein the first pressure reducer (1) is designed for providing the first gas component at its back-pressure outlet (H.1), wherein the second pressure reducer (2) is designed for providing the second gas component at its back-pressure outlet (H.2), wherein the control pressure actuators (16, 17) of the pressure reducers (1, 2) are designed for controlling a pressure at which the pressure reducers (1, 2) provide the respective gas component at their back-pressure outlets (H.1, H.2), wherein a fluid connection (22) between the pre-pressure inlet (V.1) of the first pressure reducer (1) and a first source (20), i.e. a source for the first gas component, is established or at least temporarily establishable, wherein the first channel (K.1) is designed for guiding the first gas component from the back-pressure outlet (H.1) of the first pressure reducer (1) to the mixing point (8), wherein a fluid connection (23) between the pre-pressure inlet (V.2) of the second pressure reducer (2) and a second source (21), i.e. a source for the second gas component, is established or at least temporarily establishable, wherein the second channel (K.2) is designed for guiding the second gas component from the back-pressure outlet (H.2) of the second pressure reducer (2) to the mixing point (8), wherein the inhalation channel (K.3) is designed for guiding the gas mixture generated at the mixing point (8) to the patient-side coupling unit (9), wherein the control device (3) is designed for automatically deriving a target ratio between a volume flow (Vol'[1]) through the first channel (K.1) and a volume flow (Vol'[2]) through the second channel (K.2) depending on a predefined target share of the first gas component and / or the second gas component in the gas mixture to be generated, controlling the control pressure actuators (16, 17) of the first pressure reducer (1) and thereby the pressure at the back-pressure outlet (H.1) of the first pressure reducer (1) depending on the derived target ratio of the two volume flows (Vol'[1], Vol'[2]), and controlling the control pressure actuators (16, 17) of the second pressure reducer (2) and thereby the pressure at the back-pressure outlet (H.2) of the second pressure reducer (2) depending on the derived target ratio of the two volume flows (Vol'[1], Vol'[2]). ​ - actuating the control pressure actuator of the second pressure reducer (2) and thereby controlling the pressure at the back pressure outlet (H.2) of the second pressure reducer (2), and The actuation of the two control pressure actuators is carried out with the control target or regulation target that the actual ratio of the two volume flows is equal to the derived nominal ratio.

2. The supply assembly (100) according to claim 1, characterized in that The first gas component is air and the second gas component is oxygen.

3. The supply assembly (100) according to claim 1 or 2, characterized in that at least one of the two pressure reducers (1, 2) additionally comprises a control pressure chamber (Ka.3), wherein the control pressure actuators (16, 17) of the pressure reducers (1, 2) are designed for controlling the pressure in the control pressure chambers (Ka.3) of the pressure reducers (1, 2), wherein the pressure (P hin [1]、P hin [2]) at the back pressure outlet (H.1, H.2) of the pressure reducer (1, 2) depends on the pressure in the control pressure chamber (Ka.3) of the pressure reducer (1, 2), such that the greater the pressure in the control pressure chamber (Ka.3), the greater the pressure (P hin [1]、P hin [2])at the back pressure outlet (H.1, H.2).

4. The supply assembly (100) according to claim 1 or 2, characterized in that at least one of the two pressure reducers (1, 2) additionally comprises - a pre-pressure chamber (Ka.1) which is connected to a pre-pressure inlet (V.1, V.2) of the pressure reducer (1, 2), - a back pressure chamber (Ka.2) which is connected to a back pressure outlet (H.1, H.2) of the pressure reducer (1, 2), - a partition wall (15) between the pre-pressure chamber (Ka.1) and the back pressure chamber (Ka.2), - an opening (26) in the partition wall (15), and - a closure (13) for the opening (26), wherein the closure (13) can selectively release or close the opening (26) in the partition wall (15), wherein a fluid connection between the pre-pressure chamber (Ka.1) and the back pressure chamber (Ka.2) is established when the opening (26) is released, wherein the fluid connection is interrupted when the opening (26) is closed, and wherein the control pressure actuators (16, 17) of the pressure reducers (1, 2) can move the closure (13) back and forth between a released position and a closed position.

5. The supply assembly (100) according to claim 1 or 2, characterized in that the supply assembly (100) is designed such that - the pressure in the first channel (K.1), - the pressure in the second channel (K.2), and - the pressure at the mixing point (8) are identical, and the control device (3) is designed for - the time curve of the actual pressure (P hin [1] ) at the back pressure outlet (H.1 ) of the first pressure reducer (1 ) follows a predefined time curve of the pressure at the mixing point (8) as an additional regulation target, and the control pressure actuator (16, 17) of the first pressure reducer (1 ) is operated in accordance with this additional regulation target, and - the control pressure actuator of the second pressure reducer (2) is operated with an additional regulation objective that the time curve of the actual pressure (P hin [2] at the back pressure outlet (H.2) of the second pressure reducer (2) follows a predefined time curve of the pressure at the mixing point (8).

6. The supply assembly (100) according to claim 5, characterized in that the pre-specified nominal time profile of the pressure at the mixing point (8) is that the pressure at the mixing point (8) should be at least temporarily equal to a pre-specified nominal pressure value (P0), The control device (3) is able to actuate the control pressure actuator (16, 17) of the first pressure reducer (1) with an additional regulation target, which is that the actual pressure (P hin [1] at the back pressure outlet (H.1) of the first pressure reducer (1) is equal to the rated pressure value (P0), and The control device (3) is able to actuate the control pressure actuator of the second pressure reducer (2) with an additional regulation target, which is that the actual pressure (P hin [2] at the back pressure outlet (H.2) of the second pressure reducer (2) is equal to the rated pressure value (P0).

7. The supply assembly (100) according to claim 1 or 2, characterized in that at least one of the two pressure reducers (1, 2) additionally comprises respectively - a back pressure chamber (Ka.2), - a control pressure chamber (Ka.3), and - a movable wall (12), wherein the back pressure chamber (Ka.2) of the pressure reducer (1, 2) is connected to a back pressure outlet (H.1, H.2) of the pressure reducer (1, 2), wherein the pressure (P hin [1]、P hin [2]) depends on the pressure in the control pressure chamber (Ka.3) of the pressure reducer (1, 2), such that the greater the pressure in the control pressure chamber (Ka.3), the greater the pressure (P hin [1]、P hin [2])at the back pressure outlet (H.1, H.2). wherein the movable wall (12) separates the back pressure chamber (Ka.2) from the control pressure chamber (Ka.3) in such a way that a pressure compensation occurs between the pressure in the back pressure chamber (Ka.2) and the pressure in the control pressure chamber (Ka.3), and wherein a control pressure actuating mechanism (16, 17) of the pressure reducer (1, 2) is designed to move the movable wall (12) of the pressure reducer (1, 2).

8. The supply assembly (100) according to claim 7, characterized in that each pressure reducer (1, 2) additionally comprises - a pre-pressure chamber (Ka.1), - a wall (15) between the back pressure chamber (Ka.2) and the pre-pressure chamber (Ka.1), - an opening in the wall (15), - a closure (13) for the opening in the wall (15), and - a mechanical force connection (14) between the movable wall (12) and the closure (13), wherein the pre-pressure chamber (Ka.1) of the pressure reducer (1, 2) is connected to a pre-pressure inlet (V.1, V.2) of the pressure reducer (1, 2), wherein the closure (13) can selectively close or release the opening, and wherein the mechanical force connection (14) causes the closure (13) to close the opening when the pressure in the back pressure chamber (Ka.2) is greater than the pressure in the control pressure chamber (Ka.3) and to release the opening otherwise.

9. The supply assembly (100) according to claim 1 or 2, characterized in that a first aerodynamic resistor (5.1) with a changeable aerodynamic resistance value (R1) is arranged in the first channel (K.1), and the supply assembly (100) additionally comprises a first resistor actuating mechanism (27.1) designed to change the aerodynamic resistance value (R1) of the first aerodynamic resistor (5.1), wherein the control device (3) is designed to manipulate the first resistor actuating mechanism (27.1) and thereby adjust the aerodynamic resistance value (R1) of the first aerodynamic resistor (5.1) in accordance with the derived target ratio of the two volume flows (Vol'[1], Vol'[2]), and / or a second aerodynamic resistor (5.2) with a changeable aerodynamic resistance value (R2) is provided in the second channel (K.2), and the supply assembly (100) additionally comprises a second resistor actuating mechanism (27.2) designed to change the aerodynamic resistance value (R2) of the second aerodynamic resistor (5.2), wherein the control device (3) is designed to actuate the second resistor actuator (27.2) in accordance with the derived target ratio of the two volume flows (Vol'[1], Vol'[2]) and thereby to adjust the pneumatic resistance value (R2) of the second pneumatic resistor (5.2).

10. The supply assembly (100) according to claim 1 or 2, characterized in that , The two control pressure actuators (16, 17) are thus adjusted such that the same pressure occurs at the two back pressure outlets (H.1, H.2) of the two pressure reducers (1, 2) if no gas passes through the two pressure reducers (1, 2).

11. The supply assembly (100) according to claim 1 or 2, characterized in that An actuable valve (4) is arranged in the suction channel (K.3), wherein the control device (3) is designed to manipulate the valve (4) in such a way that the actual volume flow (Vol Pt ) to the patient-side coupling unit (9) is regulated with the regulation goal that the actual volume flow (Vol Pt,Soll ) to the patient-side coupling unit (9) is equal to a predefined time-dependent target profile (Vol Pt ) of the volume flow to the patient-side coupling unit (9). Pt,Soll Pt ​​ 12. A supply system for supplying a gas mixture to a patient-side coupling unit (9), the gas mixture comprising a first gas component and a second gas component, wherein the patient-side coupling unit (9) being connected or connectable to a patient (Pt), wherein the supply system comprises - a supply assembly (100) according to any one of the preceding claims, - a first source (20), i.e. a source for the first gas component, and - a second source (21), i.e. a source for the second gas component, wherein a fluid connection (22) is established between the pre-pressure inlet (V.1) of the first pressure reducer (1) and the first source (20), and wherein a fluid connection (23) is established between the pre-pressure inlet (V.2) of the second pressure reducer (2) and the second source (21).

13. The supply system of claim 12, wherein The first gas component is air and the second gas component is oxygen.

14. A patient supply system for supplying a gas mixture to a patient, wherein the gas mixture comprising a first gas component and a second gas component, wherein a patient-side coupling unit (9) is connected or at least temporarily connectable to a patient (Pt), wherein the patient supply system comprises - a supply assembly (100) according to any one of claims 1 to 11 or a supply system according to claim 12 or 13, and - a patient-side coupling unit (9), and wherein the suction channel (K.3) is connected to the patient-side coupling unit (9) and is designed to guide the gas mixture from the mixing point (8) to the patient-side coupling unit (9).

15. The patient supply system of claim 14, wherein, The first gas component is air and the second gas component is oxygen.

Images