Apparatus and method for providing flow of breathing gas

Abstract

The invention relates to a device (10) for providing a breathing gas flow (AS) for a breathing appliance (30), having a first inlet (1) and a second inlet (2). The invention is characterized in that the fourth gas line (7) has a third volumetric flow rate sensor (S3) for measuring the total volumetric flow rate (SV3), and in that a control and regulation unit (15) is provided, which is designed to control the total volumetric flow rate (SV3) by means of the third volumetric flow rate sensor (S3). The blower (8), the first metering unit (V1) and the second metering unit (V2) are controlled taking into account the measured values (SV1, SV2, SV3) of the first (S1), second (S2) and third (S3), alone or in combination, the concentration value (M1) of the breathing gas flow (AS) and / or the pressure value (M2) for the pressure downstream of the mixing volume (11). The invention further relates to a method for providing a breathing gas flow (AS) and to a breathing appliance (30).

Description

Technical Field

[0001] The present invention relates to an apparatus and method for providing a breathing gas flow to a breathing apparatus, a breathing apparatus having such an apparatus, and the use of such an apparatus. Background Technology

[0002] Respiratory devices are used to support or take over a patient's breathing process. The goal is to provide the patient with adequate oxygen and facilitate the removal of carbon dioxide from the lungs. Devices used to provide the respiratory gas flow should be highly accurate relative to the characteristics of the respiratory gas flow (such as oxygen concentration, pressure, and volume) and have the ability to change these characteristics as quickly as possible.

[0003] In practice, two basic types of devices are common: compressed air-based devices and blower-based devices. Compressed air-based devices obtain breathing gases from an external source. This includes, for example, a central gas supply unit in a hospital. In contrast, blower-based devices primarily obtain breathing gases from the environment, with an internal blower drawing in ambient air. Additionally, if necessary for the patient's breathing, oxygen (e.g., from a gas cylinder) can be mixed with the ambient air. A disadvantage of compressed air-based devices is that their location is fixed or nearly fixed, thus limiting their place of use, especially while the device is in operation. This is particularly problematic if, for example, a patient is transferred to another ward in the hospital and must continue breathing there. Furthermore, compressed air-based devices typically have an external compressor that supplies breathing gases in case of a failure of the central gas supply unit. Such compressors require a lot of energy and are heavy, further restricting the location of use of the compressed air-based device. The disadvantages of blower-based devices are their louder operating noise compared to pressure-based devices, which can have a negative impact on patients, and limitations in breathing modes, as some breathing modes can only be achieved using a central gas supply unit and its higher breathing gas pressure.

[0004] Devices known in the prior art (e.g., from US5823186A) combine compressed air-based and blower-based devices, thus offering high flexibility regarding the location of use and breathing mode when the blower is operating. However, such prior art devices are costly and space-intensive, with the large internal volume in which the breathing gas flows negatively impacting the device's dynamics. Furthermore, these devices partially only offer the possibility of simultaneously utilizing up to two breathing gas sources. Also problematic is the fact that different breathing gas sources have different pressures, which must be adapted to suit the patient's needs in order to provide a suitable breathing gas flow. Therefore, adjustment to this design is particularly important, as it must accommodate different pressures on the one hand and react quickly to changes on the other, resulting in high device dynamism. Summary of the Invention

[0005] Starting from solutions known in the prior art and the problems previously described, the present invention aims to create a compact and cost-effective device for providing a breathing gas flow, which can combine various gas flows from different sources into a breathing gas flow on demand. It should be possible to flexibly use pressurized external sources and ambient air as sources for providing the breathing gas flow. Furthermore, the device should be highly dynamic in setting or changing the characteristics of the breathing gas flow, so that the setting or change of the characteristics of the breathing gas flow to be provided can be achieved as quickly as possible. Here, the main characteristics of the breathing gas flow are: breathing gas volume, breathing gas pressure, and breathing gas concentration, which can be at least partially set by the user.

[0006] The aforementioned task is accomplished by means of an apparatus for providing a breathing gas flow to a respiratory device having the features of claim 1, a method for providing a breathing gas flow to a respiratory device according to claim 11, a respiratory device according to claim 16, and the use of an apparatus according to claim 17. Further details of the invention are derived from the dependent claims, the description, and the drawings. Hereinafter, the features and details described in conjunction with the apparatus according to the invention and the respiratory device according to the invention are also applicable in conjunction with the method according to the invention, so that the disclosure of each aspect of the invention is always referred to, or more precisely, may be referred to, in relation to each other.

[0007] The device according to the invention for providing a breathing gas flow to a respirator includes a first inlet and a second inlet, respectively for connecting to an external gas source, particularly to a central gas supply unit (ZGV). Here, the first inlet is fluidly connected to a mixing volume for mixing the gas flow via a first gas line and the second inlet via a second gas line. The first gas line has a first dispensing unit with a first volumetric flow sensor disposed downstream of the first dispensing unit. The second gas line has a second dispensing unit with a second volumetric flow sensor disposed downstream of the second dispensing unit. Furthermore, the device includes a third inlet, which is fluidly connected to the mixing volume via a third gas line. The third gas line has a blower and a check valve disposed downstream of the blower and upstream of the mixing volume. The blower is configured to draw in ambient air from outside the device through the third inlet and to deliver ambient air in the direction of the check valve. Additionally, the device includes a fourth gas line establishing a fluid connection between the mixing volume and an outlet, at which a breathing gas flow is provided. The device is characterized in that the fourth gas line has a third volumetric flow sensor for measuring the total volumetric flow rate of the breathing gas flow, and is equipped with a control and regulation unit configured to control the blower, the first dosing unit, and the second dosing unit. Here, the measurements of the first, second, and third volumetric flow sensors, individually or in combination, are considered, along with the concentration value of the breathing gas flow and / or the pressure value downstream of the mixing volume. The concentration value indicates the concentration of the breathing gas components in the breathing gas flow, particularly the oxygen concentration in the breathing gas flow.

[0008] External gas sources should be understood, for example, as ZGVs, gas cylinders, or external compressors in hospitals. Typically, these external gas sources have high pressure, particularly in the range of 2.7 to 6 bar, and supply air or specific breathing gases, such as oxygen, or specific therapeutic gases, such as nitric oxide, for the patient's breathing.

[0009] Within the scope of this invention, "patient" is understood to refer to both humans and animals, wherein the patient is to be supplied with a mechanically provided respiratory gas flow, and is particularly a person under medical supervision, such as, for example, an infant, child, or adult. Air, ambient air, and respiratory and therapeutic gases are to be understood as respiratory gas components whose gas flows can contribute to the respiratory gas flow provided by the device according to the invention.

[0010] A blower (also called a compressor or turbine) belonging to the device according to the invention draws in ambient air through a third inlet and further guides it downstream along a check valve and then into a mixing volume via a third gas line. The blower is electronically connected to a control and regulation unit. This unit changes the blower's operating parameters, such as, for example, the blower's rotational speed, so that ambient air is drawn into the device as needed, generating a defined pressure and volumetric flow rate downstream of the blower.

[0011] A check valve upstream of the mixing volume and downstream of the blower directs the gas flow (in this case, ambient air) through the blower in only one direction along the mixing volume. This prevents the gas flow (e.g., air or oxygen) from escaping from the unit through the permeable blower and the third inlet. This is especially true when the blower is off and the gas flow is directed into the unit through the first and / or second inlets.

[0012] A mixing volume, fluidly connected at the inlet to the first, second, and third gas lines and at the outlet to the fourth gas line, is used to mix the introduced gas flow. The shape, size, and structure of the mixing volume are conceivable in various variations. In particular, the size of the mixing volume affects the dynamics of the breathing apparatus into which the device according to the invention is integrated. Generally, a larger volume within the breathing apparatus negatively impacts its dynamics, making it less responsive to, for example, the setting or changing of breathing parameters (e.g., oxygen concentration). For this reason, a smaller mixing volume is preferred. As will be explained in more detail later, the device according to the invention has a smaller mixing volume. This is particularly true because the dosage of the breathing gas components upstream of the mixing volume is achievable according to the invention, since the mixing volume, for example, does not serve the function of a buffer volume for absorbing breathing gas flows at higher pressures, where dosage must also be performed downstream of the buffer volume. Such a buffer volume is significantly larger than the mixing volume of the device according to the invention.

[0013] The first, second, and fourth gas lines each have a volumetric flow sensor, wherein a third volumetric flow sensor in the fourth gas line measures the total volumetric flow rate downstream of the mixing volume and upstream of the device outlet. The total volumetric flow rate relates to the breathing gas flow provided by the device, i.e., the breathing gas flow consisting of various gas flows entering the device through the inlet. The third volumetric flow sensor is preferably arranged near the mixing volume, thus eliminating the need to compensate for the dynamic effects of the mixing volume, and allowing for accurate acquisition of the volumetric flow rate of the breathing gas flow, and enabling precise setting of the breathing gas flow to be provided by means of a control and regulation unit. Furthermore, according to the invention, it is advantageous to arrange the third volumetric flow sensor downstream of the mixing volume, as this eliminates the need for an additional volumetric flow sensor downstream of the blower and upstream of the mixing volume. The volumetric flow rate downstream of the blower and upstream of the mixing volume can be determined based on the total volumetric flow rate and the volumetric flow rates of the first and / or second volumetric flow sensors.

[0014] In contrast, in solutions known from the prior art, a volumetric flow sensor is typically positioned downstream of and near the blower. Since the blower also produces a small supply of ambient air that should be drawn in, this volumetric flow sensor must be highly accurate. Due to these requirements, such a volumetric flow sensor is associated with high cost. Therefore, it is advantageous to eliminate the need for a particularly accurate and expensive volumetric flow sensor near the blower, thereby resulting in a device according to the invention with lower manufacturing costs and a smaller structural footprint.

[0015] The device according to the invention is designed to be flexible by means of its ability to be matched to the corresponding conditions of the operating location and the user's settings. Here, the user settings follow the patient's needs and breathing patterns. The device can operate in different operating modes, wherein the respiratory gas flow to be provided can be generated by means of different combinations of sources. The device can operate using a ZGV in a first operating mode, using a ZGV and a blower in a second operating mode, using a partial ZGV and a blower in a third operating mode, and using a blower in a fourth operating mode. The respiratory gas flow provided by the device can therefore be combined from up to three sources. These different combination possibilities provide maximum possible flexibility and are made possible advantageously by the design of the device according to the invention. Flexibility includes, in particular, the possibility of matching to the patient's needs, but also takes into account the device's fail-safe nature, where if the ZGV fails, for example due to a defect, such as activating the blower. In this case, a switch occurs from the first operating mode to the fourth operating mode.

[0016] Combining more than three sources is conceivable, with the device correspondingly having more than three inlets. For example, a fourth inlet for additional connection to an external gas source (such as a ZGV), and a fifth gas line correspondingly designed with a dosing unit and a volumetric flow sensor based on the first or second gas line. Thus, additional therapeutic gases can be combined, or, for fail-safe purposes, an additional oxygen source can be fluidly connected to the device, alternatively using oxygen from the ZGV.

[0017] Depending on the operating mode, the respiratory gas components are dispensed upstream of the mixing volume via a blower, a first dispensing unit, and / or a second dispensing unit, wherein the first and second dispensing units and the blower are controlled by a control and regulation unit. That is, no dispensing is performed downstream of the mixing volume. This is advantageous because it eliminates the need for a dispensing valve located close to the patient, i.e., near the outlet. A low respiratory gas pressure, suitable for patient breathing, is required at the device outlet, for example, 30 mbar. Using a patient-closed dispensing valve for such a low pressure range is associated with high cost. Therefore, with the device according to the invention, these costs and the additional structural space required for such a valve are advantageously eliminated. Furthermore, eliminating the patient-closed dispensing valve reduces the device's energy consumption. This is particularly advantageous in situations where the device and respiratory apparatus are transported and powered by the respiratory apparatus's energy storage. The storage is thus less burdened, and a longer operating time for the respiratory apparatus is achieved.

[0018] The dosage of the breathing gas components is achieved in the flow direction through first and second dosing units and / or a blower into the mixing volume. Known technical solutions partially involve the dosing of at least one breathing gas component from the dosing unit to the blower, particularly when oxygen is the breathing gas component. Disadvantages of this are that, for example, in the case of oxygen, a breathing gas flow containing pure oxygen cannot be provided. On the one hand, the blower draws in air in addition to the dosed oxygen, thereby reducing the oxygen concentration; on the other hand, the pressure is insufficient for this breathing pattern. Furthermore, additional volume is typically required when dosing the breathing gas components into the blower, which negatively impacts dynamics. The advantageous design of the device according to the invention therefore offers high dynamics and the possibility of flexible use.

[0019] The control and regulation unit affects the characteristics of the provided respiratory gas flow, such as, for example, pressure, volumetric flow rate, and / or oxygen concentration. Here, it is at least electronically connected to the first and second dosing units, the blower, and the first, second, and third volumetric flow sensors.

[0020] Depending on the operating mode, the control and regulation unit controls the actuators, namely the first dosing unit, the second dosing unit, and / or the blower. In the first operating mode, the actuators are controlled such that the first and second dosing units contribute to the breathing gas flow. In the second operating mode, the actuators are controlled such that the first dosing unit, the second dosing unit, and the blower contribute to the breathing gas flow. In the third operating mode, the actuators are controlled such that the blower and the first or second dosing unit (depending on which gas is required from the ZGV) contribute to the breathing gas flow. In the fourth operating mode, the actuators are controlled such that only the blower contributes to the breathing gas flow. When controlling the actuators, the control and regulation unit considers, individually or in combination, at least one measurement from the first, second, and third volumetric flow sensors, as well as the concentration value of the breathing gas flow and / or the pressure value used for the pressure downstream of the mixing volume.

[0021] Here, it is conceivable that the concentration value is determined by an additional sensor downstream of the mixing volume, which may involve sensors inside the device or external sensors, such as in the area of ​​the breathing mask. Alternatively or additionally, the concentration value may be determined by a control and regulation unit using the value of a measured volumetric flow rate. The concentration value relates to the concentration of the breathing gas, such as oxygen or Heliox (a mixture of helium and oxygen), determined in the breathing gas flow.

[0022] Furthermore, it is conceivable to determine the pressure value of the respiratory gas flow via an additional sensor, wherein the sensor is fluidly connected to, for example, a breathing mask, so that the pressure of the respiratory gas flow near the patient can be measured by the sensor. Alternatively, an external sensor for measuring the pressure value is conceivable, for example, in the area of ​​the breathing mask, wherein the pressure value can be electronically transmitted to a control and regulation unit. It is also conceivable to calculate the pressure value, wherein, for example, an additional pressure sensor measures the inspiratory pressure of a fourth gas line. Using the inspiratory pressure value, the volumetric flow rate, and the resistance value stored for the fourth gas line, the pressure value (i.e., the pressure near the patient) can be determined.

[0023] In a preferred embodiment of the device, the control and regulation unit has a multi-parameter regulator with a single-loop blower regulation loop. The multi-parameter regulator is characterized by having at least two guide parameters. Thus, the interdependence of multiple guide parameters, such as, for example, the pressure and volumetric flow rate of the breathing gas, can be taken into account during regulation. The single-loop blower regulation loop should be understood as a regulation loop for the blower without a lower-level regulation loop. Lower-level regulation loops can be found, for example, in cascade regulators.

[0024] A multi-parameter regulator with a single-loop blower regulating circuit is particularly advantageous for the second and third operating modes of the device according to the invention, wherein the breathing gas flow consists of ambient air from the blower and gas flow (e.g., oxygen from the ZGV) from the first and / or second gas lines.

[0025] The blower, as also used in the device according to the invention, physically represents a pressure source. However, it can also be used as a volumetric flow rate source relative to regulation, where regulation is implemented as dynamic volumetric flow rate regulation. In known technical solutions, cascade regulation is utilized for this purpose, where the external pressure regulation loop is stabilized by a lower regulation loop (e.g., a lower volumetric flow rate regulation loop and a lower speed regulation loop). The reason for using cascade regulation is the simplicity of the design of some regulation loops. In cascade regulation with nested regulation loops, the lower regulation loop (or also called the internal regulation loop) must be faster than the corresponding upper regulation loop in order to achieve stable guide parameter behavior. However, since the pressure and speed of the blower are dynamically equivalent, and the lower speed regulation loop must be faster than the external pressure regulation loop, the overall dynamics of the cascade regulator are thus slowed down.

[0026] Multi-parameter regulators with a single-loop blower regulation circuit do not exhibit this slowdown, thus enabling better dynamics, i.e., faster regulation, in an advantageous manner. This is achieved by utilizing the slightly more dynamic response of volumetric flow regulation using the first and / or second metering units compared to pressure regulation using the blower. The first and / or second metering units thus provide their gas fraction (in this case, ambient air) for pressure increase shortly before the blower provides its gas fraction by increasing its rotational speed. This small time difference leads to decoupling of the actuators of the multi-parameter regulator (i.e., the first and second metering units and the blower). Based on its pressure source characteristics, the blower replenishes the missing gas fraction according to the guide parameters of the multi-parameter regulator. The blower is selected such that the aforementioned dynamic differences with respect to the first and / or second metering units are minimized. For example, the blower's mass inertia, motor, and fan wheel are considered here. Therefore, the balancing of dynamic differences can be advantageously eliminated, where the faster first and / or second metering units are matched to the slower blower, resulting in improved dynamics of the device.

[0027] According to a preferred embodiment of the device, the total volumetric flow rate, concentration value, and pressure value can be transmitted as actual values ​​to the multi-parameter controller. Furthermore, the multi-parameter controller, taking into account the actual values ​​and at least one theoretical concentration, theoretical pressure, and / or theoretical volume value stored as theoretical values, generates a blower controller signal for controlling the blower and / or generates a first control parameter for a first theoretical volumetric flow rate and / or a second control parameter for a second theoretical volumetric flow rate.

[0028] Theoretical concentration, theoretical pressure, and theoretical volume are the guide parameters of a multi-parameter regulator. They can be set by the user, for example, via the input unit of the breathing apparatus. It is also conceivable that the guide parameters are stored in the breathing apparatus or transmitted to it. Different combinations of guide parameters are required depending on the breathing mode. Theoretical pressure and theoretical concentration are particularly needed for pressure-controlled breathing, while theoretical volume and theoretical concentration are particularly needed for volume-controlled breathing. Furthermore, combinations of theoretical concentration, theoretical pressure, and theoretical volume are also necessary, for example, for volume-controlled breathing with breathing pressure limitations. In addition to theoretical volume, the theoretical volumetric flow rate used for the respiratory gas flow to be provided can also be a guide parameter.

[0029] Depending on the operating mode of the device, a multi-parameter regulator can generate corresponding control parameters using the corresponding actual values ​​and guide parameters. In the first operating mode, a first control parameter for a first theoretical volumetric flow rate and a second control parameter for a second theoretical volumetric flow rate are generated. Here, the first control parameter is used to control the first dispensing unit, and the second control parameter is used to control the second dispensing unit. It is conceivable that only one of the control parameters is generated if only a single external gas source contributes to the breathing gas flow at the first or second inlet. Furthermore, the corresponding control parameter is suitable for directly controlling the corresponding dispensing unit, or as an input parameter for further adjustment of the volumetric flow rate, especially as an input parameter for the volumetric flow rate regulator. In the second operating mode, the first control parameter, the second control parameter, and a blower regulator signal for controlling the blower are generated. In the third operating mode, a blower regulator signal and either the first or second control parameter are generated, depending on which external gas source contributes to the breathing gas flow. In the fourth operating mode, a blower regulator signal is generated. The blower regulator signal is suitable for controlling the blower. Here, it may involve, for example, a preset rotation speed or voltage.

[0030] Therefore, multi-parameter regulators can advantageously account for the physical coupling of different actuators. This is especially true when multiple actuators are used, where they contribute to the breathing gas flow as well as to pressure build-up and volumetric flow rate. Furthermore, multiple actuators also affect the oxygen concentration in the breathing gas flow. The actuators include a first dosing unit, a second dosing unit, and a blower.

[0031] In the first operating mode and volume-controlled breathing, a multi-parameter regulator generates first and second control parameters for the first and second dosing units using theoretical volume and theoretical concentration. The dosing units generate first and second partial respiratory gas flows, which are merged upstream of or within the mixing volume, resulting in a respiratory gas flow downstream of the mixing volume. Here, the first and second control parameters determine the distribution of theoretical volume and theoretical concentration to the first and second dosing units. The dosing units preferably have high regulation accuracy, thereby enabling accurate dosing of partial respiratory gas flows. In this case, the first and second dosing units are directly controlled using the first and second control parameters. Alternatively or additionally, it is conceivable to supply the first and second control parameters to another regulator unit, which takes these control parameters into account and generates another control parameter for controlling the first and / or second dosing units. This other regulator unit, in the form of a volumetric flow rate regulator, will be described in more detail later in the specification.

[0032] In the second and third operating modes, i.e., when the blower and at least one dosing unit contribute to the generation of the respiratory gas flow, the multi-parameter regulator generates a blower regulator signal in addition to the first and / or second control parameters as described above. Through the dynamic decoupling of the actuators already mentioned, the regulator component for the blower can be designed separately. This regulator component is preferably designed as a PID regulator, where the I-component is calculated, for example, once per respiratory stroke. The regulation deviation of this PID regulator is here the difference between the theoretical pressure and the pressure value, where the pressure is measured, for example, close to the patient.

[0033] In a preferred embodiment of the device, the control and regulation unit includes a volumetric flow rate regulator. The volumetric flow rate regulator is capable of receiving a first control parameter for a first theoretical volumetric flow rate and a measured value from a first volumetric flow rate sensor, and a second control parameter for a second theoretical volumetric flow rate and a measured value from a second volumetric flow rate sensor as input values. Furthermore, the volumetric flow rate regulator, taking the input values ​​into account, generates a first dosage regulator signal for controlling a first dosage unit and / or a second dosage regulator signal for controlling a second dosage unit. This may involve a single volumetric flow rate regulator, or preferably two volumetric flow rate regulators, wherein the first volumetric flow rate regulator is capable of receiving the first control parameter and the measured value from the first volumetric flow rate sensor as input values, and the second volumetric flow rate regulator is capable of receiving the second control parameter and the measured value from the second volumetric flow rate sensor as input values. In this case, the first volumetric flow rate regulator generates the first dosage regulator signal and / or the second volumetric flow rate regulator generates the second dosage regulator signal.

[0034] The corresponding control parameters for the theoretical volumetric flow rate from the multi-parameter regulator are the guide parameters for the corresponding volumetric flow rate regulator. The volumetric flow rate regulator compares the corresponding control parameters with the measured values ​​of the corresponding volumetric flow rate sensor and generates a corresponding dosing regulator signal. With the aid of the first and second volumetric flow rate regulators, the inaccuracies of the first and second dosing units can be advantageously compensated for, at least partially, in a way that allows for accurate dosing of a portion of the volumetric flow rate and the generation of a prescribed respiratory gas flow.

[0035] According to a preferred embodiment of the device, the third gas line has a shut-off valve downstream of the blower and upstream of the mixing volume.

[0036] The shut-off valve can close the third gas line, thereby interrupting the fluid connection between the blower and the mixing volume. In this case, no fluid connection occurs upstream of the mixing volume via the third gas line.

[0037] In patient breathing (especially critical breathing), so-called "manipulation" is used to improve treatment. This manipulation, for example, is the P.O1 manipulator, which is used to measure the patient's airway pressure. Here, the airway pressure generated by the patient's inspiratory effort is measured over a period of 100 ms. During this time, respiratory gas components are not supplied through the ventilator, resulting in a low pressure corresponding to the patient's respiratory gas pressure. Furthermore, in so-called high-frequency breathing, which is a breathing mode of the ventilator, a low pressure occurs within the gas tubing of the ventilator.

[0038] Regarding the device and P0.1 operation, the first and second dosing units should be shut off. Due to the low pressure generated during P0.1 operation or high-frequency breathing, the supply of breathing gas through the third gas line must be interrupted, as the vented blower and check valve allow ambient air into the device whenever low pressure exists downstream of the check valve. By closing the shut-off valve, ambient air is advantageously prevented from reaching the mixing volume in the event of low pressure downstream of the shut-off valve. After operation or high-frequency breathing, the shut-off valve is reopened, and the supply of breathing gas through the device resumes.

[0039] Preferably, the shut-off valve is controllable by means of a computing unit (e.g., a control and regulation unit). Alternatively or additionally, the shut-off valve is manually operable and / or electronically controllable. Therefore, a user, for example in the case of high-frequency breathing (where the shut-off valve must remain closed), can manually close and reopen the shut-off valve. Thus, the operation of the shut-off valve can be adapted to different user needs.

[0040] The gate valve is preferably designed as a large-diameter gate valve. A large-diameter gate valve with a larger internal cross-section has lower flow resistance, resulting in only a smaller pressure drop when breathing gas components flow through it. This large-diameter design is particularly advantageous in the case of blowers (which generate only a relatively small maximum pressure).

[0041] In a preferred embodiment of the device, the control and regulation unit is configured to control the shut-off valve based on input and / or based on the operating mode of the breathing apparatus.

[0042] The input preferably involves manual electronic input, such as via the digital input unit of the breathing apparatus. Therefore, the state of the shut-off valve can be changed for the user. Alternatively or additionally, automatic matching of the shut-off valve state relative to a defined operating mode occurs, for example, in the previously described P.01 operation. The shut-off valve can be advantageously controlled manually and / or automatically, and the device is thus flexible in its use.

[0043] According to a preferred embodiment of the device, the mixing volume has a volume in the range of 50 ml to 300 ml. Preferably, the mixing volume has a volume of 150 ml, and particularly preferably, it has a volume of 200 ml.

[0044] In practice, mixing volumes for breathing apparatus are commonly found in the range of approximately 700 ml. This mixing volume ensures good mixing of different respiratory gas components by introducing a slowing of the gas flow and its gas exchange. The size of the mixing volume affects the dynamics of the breathing apparatus. Generally, the larger the volume, the lower the dynamics. This, in particular, prolongs the time required until a change in concentration (e.g., a change in oxygen concentration) is achieved in the breathing gas flow. Due to the recommended smaller mixing volume, very good dynamics can be achieved, and changes in the setting at the breathing apparatus can be implemented quickly. A mixing volume range of 50 ml to 300 ml is chosen such that at 1 l / min (1.667 * 10⁻⁶), the dynamics are optimal. -5 m 3 / s) to 180 l / min (0.003 m 3 Good dynamics and good mixing of the introduced gas flow can be achieved within a breathing range of 150 ml and especially 200 ml. It is conceivable that the mixing volume is a simple cavity, or preferably with added geometry that, for example, generates vortices within the mixing volume, which promotes mixing. With a mixing volume of 150 ml and especially 200 ml, particularly good dynamics with good mixing are determined throughout the breathing range.

[0045] In a preferred embodiment of the device, the fourth gas line has a concentration sensor for determining the concentration value. Preferably, this involves an electrochemical sensor for measuring oxygen concentration. Alternatively or additionally, the control and regulation unit is configured to determine the concentration value using measurements from a volumetric flow sensor.

[0046] As previously mentioned, the concentration value is determined by the appropriate sensor and / or by calculation. The combination of these two variations provides the possibility of checking either the sensor value or the calculated value, thus allowing for the detection of, for example, a faulty sensor. Furthermore, the separate calculation of the concentration value results in a cost-effective device with a smaller structural size, as the additional sensor is eliminated. Overall, the device thus offers exceptional flexibility in practical use and can be tailored to the user's needs.

[0047] According to a preferred embodiment, the device has a pressure sensor for determining pressure values. The sensor preferably measures the pressure of the provided respiratory gas flow near the patient. Here, the pressure sensor has, for example, a fluid-connected connection to a breathing mask. Furthermore, it is conceivable that the pressure values ​​are calculated using inspiratory pressure values, expiratory pressure values, measured volumetric flow rates, and the resistance value of the device's tubing system. Here, the inspiratory pressure value is determined by a pressure sensor fluidly connected to a fourth gas line, and the expiratory pressure value is determined by another pressure sensor fluidly connected to the expiratory line of the breathing apparatus. The resistance value of the device's tubing system is preset and used by a calculation unit (e.g., a control and regulation unit) to calculate the pressure values.

[0048] In a preferred embodiment of the device, a fourth inlet for an external medium-pressure gas source is connected to the first or second dispensing unit in a fluid-connected manner.

[0049] The medium-pressure gas source should be understood as a source that supplies respiratory gas components at a medium pressure, such as in the range of 300 mbar to 700 mbar. The external medium-pressure gas source preferably supplies oxygen at a pressure of 500 mbar and can be, for example, a so-called oxygen concentrator. This concentrator draws in ambient air, compresses it, and filters out the nitrogen contained within using a filter membrane or molecular sieve. The oxygen concentrator thus supplies nearly pure oxygen, which can be used to enrich the respiratory gas stream with oxygen. Here, the external medium-pressure gas source is fluidly connected to the first or second dosing unit via a fourth inlet. It is conceivable that the fourth inlet is fluidly connected to a first gas line upstream of the first dosing unit, thus creating fluid communication with the first dosing unit. Furthermore, it is conceivable that the fourth inlet is fluidly connected to a second gas line upstream of the second dosing unit, thus creating fluid communication with the second dosing unit.

[0050] As previously described, the first and second inlets, and therefore the first and second metering units, are suitable for high pressures, such as from a ZGV with pressures ranging from 2.7 bar to 6 bar. This preferred embodiment of the device advantageously provides the possibility of metering gas streams with both high and medium pressures. Furthermore, it is possible to meter a high-pressure gas stream from the ZGV using the first metering unit and a lower-pressure gas stream from an external medium-pressure source using the second metering unit, or vice versa. For this fourth input, it is advantageously possible to eliminate the need for additional metering units and additional volumetric flow sensors, thereby saving cost and structural space.

[0051] Furthermore, the present invention relates to a method for providing a breathing gas flow to a breathing apparatus using a device designed according to one of the foregoing embodiments. The method comprises the following steps: - Receive at least one theoretical value of theoretical concentration, theoretical pressure and / or theoretical volume; - Considering at least one theoretical value, turn on the first and / or second dispensing unit and / or activate the blower; - Determine the total volumetric flow rate; - Determine the concentration value of the breathing gas flow and / or the pressure value of the fourth gas line; - The first dosing unit, the second dosing unit, and / or the blower are controlled by a control and regulation unit, taking into account at least one theoretical value, based on the total volumetric flow rate, concentration value, and / or pressure value.

[0052] The method is suitable for implementation by the aforementioned apparatus. Here, in the first method step, theoretical values ​​are received, wherein the form of the breathing pattern (e.g., based on compressed air or based on volume) determines which theoretical values ​​are at least necessary. As previously stated, for a compressed air-based breathing pattern, at least theoretical pressure and theoretical concentration are required, and for volume-based breathing, at least theoretical volume and theoretical concentration are required. Furthermore, it is conceivable that all three theoretical values ​​are required, especially in the case of a volume-based breathing pattern with pressure limitations.

[0053] Theoretical values, for example, are settable via the input unit of the breathing apparatus or are already stored in the breathing apparatus's data memory, thus enabling them to be transmitted to the regulation and control unit. It is conceivable that the theoretical values ​​are digitally transmitted to the breathing apparatus and then forwarded to the regulation and control unit.

[0054] In the second method step, the actuator is turned on or activated according to the operating mode. Here, for example, an initial dosage is performed through the corresponding actuator based on theoretical values. In the first operating mode, the first and second dosage units are at least partially turned on; in the second operating mode, the first and second dosage units are at least partially turned on, and the blower is activated. Here, the activated blower draws in ambient air and forwards it. In the third operating mode, the blower is activated, and either the first or second dosage unit (depending on which external air source should contribute to the breathing gas flow) is at least partially turned on. In the fourth operating mode, the blower is activated.

[0055] In the subsequent third method step (where the initial breathing gas flow is available), its volumetric flow rate and total volumetric flow rate are determined. Here, in the first operating mode (where only an external source (e.g., ZGV) contributes to the breathing gas flow), the first volumetric flow rate value from the first volumetric flow rate sensor and the second volumetric flow rate value from the second volumetric flow rate sensor are added together. In this case, the total volumetric flow rate is thus calculated. Otherwise, the total volumetric flow rate is measured using a third volumetric flow rate sensor.

[0056] In the fourth method step, concentration and / or pressure values ​​are determined. These values ​​are needed for adjustment of the control and regulation unit, depending on the breathing pattern. Here, concentration and pressure values ​​can be determined by suitable sensors. Alternatively or additionally, the concentration value can be determined by calculation as previously described.

[0057] In the fifth method step, the breathing gas flow is regulated using theoretical values, total volumetric flow rate, and pressure and / or concentration values. As previously described, this is implemented by a control and regulation unit. Here, based on the operating mode and breathing mode, the total volumetric flow rate, concentration value, and pressure value are compared with theoretical values ​​to determine possible deviations, and control signals for the first dosing unit, the second dosing unit, and / or the blower are generated accordingly. The method can advantageously and suitably implement various operating modes and utilize various combinations of actuators.

[0058] According to a preferred improvement of the method, the control and regulation unit controls the first dosing unit, the second dosing unit, and / or the blower in such a way that the breathing gas flow has a low pressure level downstream of the mixing volume, which is in the range of 0 to 120 hPa.

[0059] Low pressure levels should be understood as the pressure range suitable for a patient's breathing. The recommended range of 0 to 120 hPa includes pressure values ​​suitable for a continuous breathing flow, as well as pressure values ​​suitable for specific breathing patterns (e.g., for treating obstructive airway diseases). Furthermore, it is conceivable to construct negative pressure downstream of the mixing volume, particularly in the range of -30 to 0 hPa, which is especially induced by external influences. Reasons for this could include, for example, spontaneous breathing by the patient connected to a ventilator.

[0060] The control of the corresponding actuators is performed according to the corresponding operating mode, as described above. Here, dispensing is only performed upstream of the mixing volume, thus eliminating the need for further dispensing downstream of the mixing volume via an additional dispensing unit, as is known in the prior art.

[0061] Therefore, it can cover a wide pressure range in a favorable manner, thus providing a breathing gas flow suitable for various breathing modes. Furthermore, the regulation of the breathing gas flow does not require an additional dosing unit downstream of the mixing volume, thereby saving cost and structural space.

[0062] According to a preferred improvement of the method, the control and regulation unit places the blower in a passive state so that it does not contribute to the breathing gas flow, wherein the blower is turned on and the inhaled ambient air is blocked by a check valve.

[0063] The passive state of the blower should be understood as follows: although the blower is running and drawing in ambient air, it does not contribute to the supply of breathing gas flow because the pressure generated here is less than the pressure required for the check valve to allow ambient air to pass through. Therefore, the drawn-in ambient air is not forwarded to the mixing volume in this situation because the check valve is blocked, i.e., impermeable to ambient air. The pressure limit at which the check valve becomes permeable downstream depends on the check valve itself and the environmental conditions. Here, the control and regulation unit, the blower, and the check valve are configured and / or adapted to induce this passive state of the blower.

[0064] It is conceivable that the pressure limits for the corresponding check valves are stored in the control and regulation unit, which then generates a control signal for the blower to achieve this passive state. Furthermore, it is conceivable that the control and regulation unit generates this control signal while taking into account the measured volumetric flow rate. This control signal is generated such that the blower contributes precisely to the total volumetric flow rate, with only the first and / or second dosing units contributing. This has the advantage of reliably achieving the passive state of the blower independent of changing environmental conditions.

[0065] The method thus allows the blower to be placed in a passive state, where it is already running but not contributing to the respiratory gas flow. The blower is therefore not completely shut off, and does not need to be restarted when it should contribute to the respiratory gas flow (e.g., in the second operating mode). The activation of the blower's function inherently requires a certain amount of time, as the blower must first be started or accelerated. This time is advantageously reduced by the passive state. Furthermore, the activation of the blower from the passive state affects the dynamics of the breathing apparatus, which are thereby further improved.

[0066] According to a preferred improvement of the method, the blower is activated when it is inactive and when insufficient pressure supply and / or insufficient volumetric flow rate supply is determined. The inactive state of the blower should be understood as a blower that is turned off and (e.g., in the first operating mode) does not contribute to the breathing gas flow.

[0067] If insufficient pressure and / or volumetric flow rate is determined, the blower is activated, i.e., turned on, to contribute to the respiratory gas flow. The determination of insufficient supply is preferably performed in the control and regulation unit. Here, for example, the current pressure value and / or the current total volumetric flow rate value is compared with corresponding threshold values. It is conceivable that one or more threshold values ​​are stored in the control and regulation unit, or that the control and regulation unit accesses them. Furthermore, it is conceivable that the current pressure value and / or the current total volumetric flow rate value is compared with corresponding theoretical values. If the current pressure value and / or the current total volumetric flow rate value is several times less than (e.g., more than five times less consecutively or less over a 30-second time period) the corresponding threshold value or the corresponding theoretical value, insufficient supply is determined and the blower is activated.

[0068] Especially when supplied via an external source (such as via ZGV in the first operating mode), supply failure may occur. In the worst case, this may result in the inability to provide a breathing gas flow. To avoid this, the control and regulation unit compares the pressure value with a pressure limit value and / or the total volumetric flow rate with a volumetric flow rate limit value. Depending on the breathing mode, as previously described, the limit values ​​are individually or collectively related. If it is determined that the pressure and / or volumetric flow rate supply is insufficient, it should be assumed that a defect exists as previously exemplified, and that the external source is at least partially not contributing to the breathing gas flow. In this case, the control and regulation unit adjusts the blower so that the blower contributes to the breathing gas flow. For example, this may result in an automatic switch from the first operating mode to the third or fourth operating mode. Thus, the breathing gas flow continues advantageously, even if at least one of the external sources does not contribute to the breathing gas flow unintentionally (e.g., due to a defect).

[0069] According to a preferred improvement of the method, a third gas line between the check valve and the mixing volume is shut off, depending on the input and / or the operating mode of the device.

[0070] As mentioned earlier, manipulation of a patient's breathing (especially in critically ill patients) may be necessary. This includes, for example, examining the patient's inspiratory effort, which produces a measured low pressure.

[0071] However, this low pressure can only be generated when the device is sealed (i.e., no gas flow reaches the device during operation). Based on the fact that the blower is permeable, even when the blower is not running, the third gas line is shut off during this operation. Therefore, no gas flow passes through the third inlet and the blower when the low pressure is generated. This is achieved, for example, using the previously described shut-off valve, which is closed in this case. During operation, the first and second dosing units are also shut off. Furthermore, as previously mentioned, low pressure may be generated inside the device during high-frequency breathing, therefore the third gas line is shut off even during high-speed breathing.

[0072] Here, closure is achieved via an input, which can be performed manually or automatically (i.e., by means of an electronic control device). The shut-off valve can be manually operated, or closed and opened, for example, via a signal from the input unit of the breathing apparatus. Furthermore, automatic closure and unlocking of the third gas line is conceivable, where, for example, a control and regulation unit automatically controls the shut-off valve according to the operating mode (in this case, the execution of manipulation).

[0073] Furthermore, the present invention relates to a breathing apparatus having a device designed according to one of the foregoing embodiments, and / or a method that can implement at least one of the foregoing designs.

[0074] The proposed respiratory apparatus includes a device and preferably includes an input unit and a signal transmission unit, wherein the input unit and the signal transmission unit are connected to the control and regulation unit of the device for data exchange. The device is designed according to one of the foregoing embodiments. The input unit may be a touch screen or a display with operating elements. The signal transmission unit may have an acoustic and / or optical signal generator, and / or be capable of generating and forwarding digital signals.

[0075] The respiratory apparatus can be used flexibly and advantageously in various operating modes. Furthermore, due to the aforementioned advantages of the device, it has a small structural size and is easy to transport. Therefore, for example, transferring a patient to another ward while continuing breathing can be accomplished in a simple manner. The respiratory apparatus also has a lower cost due to its small structural size and fewer components (e.g., by omitting the dispensing unit located downstream of the mixing volume).

[0076] Furthermore, the present invention relates to the use of an apparatus according to one of the foregoing embodiments, wherein the control and regulation unit of the apparatus has a multi-parameter regulator with a single-loop blower regulation circuit.

[0077] As previously mentioned, a multi-parameter regulator is characterized by having at least two guide parameters. Therefore, the interdependence of multiple guide parameters, such as the pressure and volumetric flow rate of the breathing gas, can be considered during regulation. As previously mentioned, a single-loop blower regulation loop should be understood as a blower regulation loop without a lower-level regulation loop. Lower-level regulation loops can be found, for example, in cascade regulators.

[0078] As mentioned earlier, multi-parameter regulators with a single-loop blower regulation circuit have advantageous dynamic behavior, enabling particularly fast regulation. Attached Figure Description

[0079] Further features, objectives, and effects of the invention will become apparent from the following description and accompanying drawings of specific embodiments. Embodiments of the invention are described without limiting the general inventive concept.

[0080] In the attached diagram: Figure 1 A schematic block diagram of one embodiment of the device according to the invention is shown. Figure 2 A flowchart of one embodiment of the method according to the present invention is shown. Figure 3 A schematic block diagram of a breathing apparatus with a device according to an embodiment of the invention is shown, and Figure 4 A schematic control architecture of one embodiment of the device according to the invention is shown.

[0081] Embodiments of the present invention will now be described in detail with reference to the accompanying drawings. Here, similar components in the various drawings are given the same reference numerals. Detailed Implementation

[0082] Figure 1A preferred embodiment of the device 10 according to the invention is shown in a schematic block diagram, the device having a first inlet 1, a second inlet 2, and a third inlet 3. The first inlet 1 is fluidly connected to a mixing volume 11 via a first gas line 4. The first gas line 4 includes a first metering unit V1 and a first volumetric flow sensor S1 arranged downstream of the first metering unit V1 and upstream of the mixing volume 11. The second inlet 2 is fluidly connected to the mixing volume 11 via a second gas line 5. The second gas line 5 includes a second metering unit V2 and a second volumetric flow sensor S2 arranged downstream of the second metering unit V2 and upstream of the mixing volume 11. The third inlet 3 is fluidly connected to the mixing volume 11 via a third gas line 6. The third gas line 6 includes a blower 8 and a check valve 9 arranged downstream of the blower 8 and upstream of the mixing volume 11, wherein the flow direction of the check valve 9 is in the flow direction from the blower 8 to the mixing volume 11. The mixing volume 11 is connected to the outlet 18 in a fluid communication manner via the fourth gas line 7, wherein the fourth gas line 7 includes a third volumetric flow sensor S3.

[0083] The first and second inlets 1 and 2 are fluidly connected to a central gas supply unit (ZGV) (not shown), wherein in this embodiment, the first inlet 1 is connected to the oxygen supply unit and the second inlet 2 is connected to the air supply unit. The third inlet 3 is fluidly connected to the ambient air of the device. The outlet 18 provides a breathing gas flow AS for the patient 19's breathing. The first dispensing unit V1, the first volumetric flow sensor S1, the second dispensing unit V2, the second volumetric flow sensor S2, the blower 8, and the third volumetric flow sensor S3 are electronically connected to the control and regulation unit 15 for data acquisition and / or manipulation, such as via... Figure 1 As indicated by the dashed lines in the diagram. The control and regulation unit 15 includes at least one computing unit (which may be a microprocessor) for data acquisition, control, and regulation. Here, the first and / or second dosing units V1, V2 and / or the blower 8 are controlled such that a prescribed breathing gas flow AS is prepared at the outlet 18 of the device 10. The prescribed breathing gas flow AS should be understood as a breathing gas flow AS whose characteristics are preset by the user. The control of the control and regulation unit 15 occurs taking into account the measured values ​​SV1, SV2, SV3 of the first, second, and third volumetric flow sensors S1, S2, S3, the concentration value M1 of the breathing gas flow AS, and the pressure value M2 relative to the pressure downstream of the mixing volume 11. Here, the control of the corresponding actuators V1, V2, 8 and the consideration of the corresponding values ​​depend on the operating mode of the device 10.

[0084] The device 10 can operate in four different operating modes, each differing in the composition of the breathing gas flow AS. In the first operating mode, the breathing gas flow AS is formed by two external gas sources (i.e., oxygen and air from the ZGV). In the second operating mode, the breathing gas flow AS is constructed by two external sources and a blower 8. This operating mode is particularly meaningful when the ZGV supplies oxygen and another breathing gas component (e.g., Heliox), so that these two breathing gas components from the ZGV and the ambient air drawn in through the blower 8 contribute to the breathing gas flow AS. In the third operating mode, the breathing gas flow AS is formed by the external gas source and the blower 8 (i.e., oxygen and ambient air). In the fourth operating mode, the breathing gas flow AS is formed by the blower 8 (i.e., ambient air).

[0085] Based on the operating mode and theoretical values ​​F1, F2, F3, the control and regulation unit 15 manipulates actuators V1, V2, 8, namely the first dispensing unit V1, the second dispensing unit V2, and / or the blower 8. Here, the total volumetric flow rate SV3 of the third volumetric flow sensor S3, the volumetric flow rate SV1 of the first volumetric flow sensor S1, and / or the volumetric flow rate SV2 of the second volumetric flow sensor S2, as well as the pressure value M2 and / or the concentration value (in this case, the oxygen concentration value M1) are considered.

[0086] The theoretical values ​​(i.e., theoretical oxygen concentration F1, theoretical pressure F3, and theoretical volume F2) are transmitted to the control and regulation unit 15 via an input unit (not shown). The pressure value M2 and the oxygen concentration value M1 relate to the respiratory gas flow AS.

[0087] In the first operating mode, actuators V1, V2, and 8 are controlled such that the first and second dosing units V1, V2 contribute to the breathing gas flow AS. In the second operating mode, dosing devices V1, V2, and 8 are controlled such that the first and second dosing units V1, V2, and blower 8 contribute to the breathing gas flow AS. In the third operating mode, actuators V1, V2, and 8 are controlled such that blower 8 and the first dosing unit V1 contribute to the breathing gas flow AS. In the fourth operating mode, actuators V1, V2, and 8 are controlled such that only blower 8 contributes to the breathing gas flow AS.

[0088] Figure 2A flowchart illustrating one embodiment of the method according to the invention is shown. In the first method step 20, theoretical values ​​F1, F2, F3 are received via control and regulation unit 15. Which theoretical values ​​F1, F2, F3 are relevant depends on the type of breathing pattern. In the case of a compressed air-based breathing pattern, at least theoretical pressure F3 and theoretical oxygen concentration F1 are received. In the case of a volume-based breathing pattern, at least theoretical volume F2 and theoretical oxygen concentration F1 are received. The corresponding theoretical values ​​F1, F2, F3 are digitally transmitted to control and regulation unit 15, for example, by input unit 33 of breathing apparatus 30.

[0089] In step 21 of the second method, actuators V1, V2, and 8 are turned on or activated according to the operating mode. Here, for example, a first dispensing is performed through the corresponding actuators V1, V2, and 8 based on theoretical values ​​F1, F2, and F3. In the first operating mode, the first and second dispensing units V1 and V2 are at least partially turned on. In the second operating mode, the first and second dispensing units V1 and V2 are at least partially turned on, and the blower 8 is activated. Here, the activated blower 8 draws in ambient air and further guides it into the mixing volume 11. In the third operating mode, the blower 8 is activated, and the first dispensing unit V1 is at least partially turned on. In the fourth operating mode, the blower 8 is activated.

[0090] In the subsequent third method step 22 (where the first breathing gas flow AS is provided), its volumetric flow rate SV3 is measured by means of a third volumetric flow sensor S3. Here, it relates to the total volumetric flow rate SV3.

[0091] In step 23 of the fourth method, the concentration value M1 is measured using the oxygen concentration sensor 31, and the pressure value M2 is measured using the pressure sensor 32.

[0092] In step 24 of the fifth method, the respiratory gas flow AS is regulated. This is performed by the control and regulation unit 15 as previously described. Here, the total volumetric flow rate SV3, concentration value M1, and pressure value M2 are compared with theoretical values ​​F1, F2, F3 according to the operating mode and breathing mode. If a deviation is determined, at least one control signal RV1, RV2, R3 is generated to control the first and second dosing units V1, V2 and / or the blower 8 and at least reduce the determined deviation.

[0093] Figure 3 A schematic block diagram of a breathing apparatus 30 with a device according to the invention is shown. Figure 3 In addition to the device Figure 1In addition to the device itself, the device also includes a shut-off valve V3, a fourth inlet 16, an oxygen concentration sensor 31 for measuring oxygen concentration M1, and a pressure sensor 32 for measuring pressure M2 near the patient. Here, the shut-off valve V3 is fluidly connected to the third gas line 6 and is located downstream of the check valve 9 and upstream of the mixing volume 11. The fourth inlet 16 is fluidly connected to the first dispensing unit. The oxygen concentration sensor 31 is fluidly connected to the fourth gas line 7 and is located downstream of the mixing volume 11 and upstream of the third volumetric flow sensor S3. The pressure sensor 32 is fluidly connected to the patient's breathing mask (not shown) and is capable of measuring pressure M2 near the patient. Furthermore, the breathing apparatus 30 includes an input unit 33 and a signal transmission unit 34. Here, the input unit 33 is configured as a touchscreen. The signal transmission unit 34 includes optical and acoustic signal transmission elements. The input unit 33 and the signal transmission unit 34 are electronically connected to the control and regulation unit 15 for data exchange.

[0094] and Figure 1 Compared to the additional shut-off valve V3, which is electronically connected to the control and regulation unit 15 and capable of closing the third gas line 6 between the check valve 9 and the mixing volume 11, the breathing apparatus 30 can perform so-called manipulation, as described above. Here, manipulation is initiated via the input unit 33, which then sends a digital signal to the regulation and control unit 15. The regulation and control unit 15 then closes the shut-off valve V3 and the first and second dosing units V1, V2, allowing manipulation (e.g., P.01 manipulation) to occur. After manipulation, the shut-off valve V3 is reopened, returning to the previously interrupted operating mode and continuing the regulation and control of the corresponding actuators V1, V2, 8.

[0095] Figure 4A schematic control architecture of one embodiment of the device 10 according to the present invention is shown. Theoretical values ​​F1, F2, F3—theoretical oxygen concentration F1, theoretical pressure F3, and theoretical volume F2—input into input unit 33 can be transmitted as guide parameters to the multi-parameter regulator 41 of control and signal unit 15. Furthermore, the oxygen concentration M1 measured by oxygen sensor 31, the pressure M2 measured by pressure sensor 32, and the volumetric flow rate (total volumetric flow rate SV3) measured by third volumetric flow rate sensor S3 can be transmitted to the multi-parameter regulator 41. Based on the operating mode and breathing mode, and considering the theoretical values ​​F1, F2, F3 and taking into account the measured oxygen concentration M1, measured pressure M2, and measured total volumetric flow rate SV3, the multi-parameter regulator 41 generates a first theoretical volumetric flow rate R1, a second theoretical volumetric flow rate R2, and a blower regulator signal R3. The blower 8 can be directly controlled using the blower regulator signal R3. The first theoretical volumetric flow rate R1 can be transmitted to the first volumetric flow rate regulator 42, and the second theoretical volumetric flow rate can be transmitted to the second volumetric flow rate regulator 43. The first volumetric flow rate regulator 42 generates a first dispensing regulator signal RV1 for the first dispensing unit V1 based on the first theoretical volumetric flow rate R1 and taking into account the first volumetric flow rate SV1 measured by the first volumetric flow rate sensor S1. The second volumetric flow rate regulator 43 generates a second dispensing regulator signal RV2 for the second dispensing unit V2 based on the second theoretical volumetric flow rate R2 and taking into account the second volumetric flow rate SV2 measured by the second volumetric flow rate sensor S2.

[0096] According to the operating mode, blower 8 generates a third volumetric flow rate VS3, first dosing unit V1 generates a first volumetric flow rate VS1, and second dosing unit V2 generates a second volumetric flow rate VS2. Volumetric flow rates VS1, VS2, and VS3 can be delivered to mixing volume 11 for mixing. The respiratory gas flow AS generated by at least one of volumetric flow rates VS1, VS2, and VS3 is provided to patient 19. Furthermore, oxygen concentration sensor 31 measures oxygen concentration M1, third volumetric flow rate sensor S3 measures total volumetric flow rate SV3, and pressure sensor 32 measures pressure M2 of respiratory gas flow AS.

[0097] Reference Symbol List 1 First Entrance 2 Second Entrance 3 Third Entrance 4 First gas pipeline 5 Second gas pipeline 6. Third gas pipeline 7. Fourth gas pipeline V1 First Measurement Unit V2 Second Dosing Unit 8. Blower 9. Check valve S1 First Volumetric Flow Sensor S2 Second Volume Flow Sensor S3 Third Volume Flow Sensor 10. Devices for providing a flow of breathing gases 11 Mixed Volume 15 Control and Regulation Units 16 Fourth Entrance 18 Exports 19 patients 20 First Method Steps 21. Second method steps 22 Third Method Steps 23. Fourth Method Steps 24. Fifth Method Steps 30. Respiratory equipment 31 Oxygen Concentration Sensor 32 Pressure Sensors 33 Input Unit 34 Signal Transmission Unit V3 shut-off valve 41 Multi-parameter regulator 42 First volumetric flow regulator 43 Second volumetric flow regulator F1 Theoretical Oxygen Concentration F2 Theoretical Volume F3 Theoretical Pressure M1 measures the oxygen concentration M2 pressure measurement SV1 measures the first volumetric flow rate. SV2 measures the second volumetric flow rate. SV3 measures the total volumetric flow rate. R1 is the control parameter for the first theoretical volumetric flow rate. R2 is the control parameter for the second theoretical volumetric flow rate. R3 Blower Regulator Signal RV1 First Quantity Regulator Signal RV2 Second Dosing Regulator Signal VS1 First Volumetric Flow Rate VS2 Second Volume Flow Rate VS3 Third Volumetric Flow Rate AS respiratory gas flow

Claims

1. A device (10) for providing a breathing gas flow (AS) to a breathing apparatus (30), the device having a first inlet (1) and a second inlet (2) for connection to an external gas source, wherein, The first inlet (1) is fluidly connected to the mixing volume (11) via a first gas line (4) and the second inlet (2) is fluidly connected to the mixing volume (11) via a second gas line (5). The first gas line (4) has a first metering unit (V1) with a first volumetric flow sensor (S1) disposed downstream of the first metering unit (V1). The second gas line (5) has a second metering unit (V2) with a second volumetric flow sensor (S2) disposed downstream of the second metering unit (V2). The device has a third inlet (3) fluidly connected to the mixing volume (11) via a third gas line (6). The third gas line (6) has a blower (8) and a check valve (9) disposed downstream of the blower (8) and upstream of the mixing volume (11). The blower (8) is configured to draw in ambient air through the third inlet (3). And is used to deliver the ambient air in the direction of the check valve (9), and the device has a fourth gas line (7) that establishes a fluid connection between the mixing volume (11) and the outlet (18) to provide the breathing gas flow (AS) at the outlet, characterized in that the fourth gas line (7) has a third volumetric flow sensor (S3) for measuring the total volumetric flow rate (SV3), and is provided with a control and regulation unit (15) configured to control the blower (8), the first dispensing unit (V1) and the second dispensing unit (V2) taking into account the measurements (SV1, SV2, SV3) of the first volumetric flow sensor (S1), the second volumetric flow sensor (S2) and the third volumetric flow sensor (S3) individually or in combination, the concentration value (M1) of the breathing gas flow (AS) and / or the pressure value (M2) for the pressure downstream of the mixing volume (11).

2. The apparatus (10) according to claim 1, characterized in that, The control and regulation unit (15) has a multi-parameter regulator (41) with a single-loop blower regulation circuit.

3. The apparatus (10) according to claim 2, characterized in that, The total volumetric flow rate (SV3), the concentration value (M1), and the pressure value (M2) can be transmitted to the multi-parameter regulator (41) as actual values ​​(SV3, M1, M2), and the multi-parameter regulator (41) generates a blower regulator signal (R3) for controlling the blower (8) and / or generates a first control parameter for the first theoretical volumetric flow rate (R1) and / or generates a second control parameter for the second theoretical volumetric flow rate (R2) after considering the actual values ​​(SV3, M1, M2) and at least one of the theoretical concentration (F1), theoretical pressure (F3), and / or theoretical volume (F2) stored as theoretical values.

4. The device (10) according to claim 3, characterized in that, It has a volumetric flow rate regulator (42, 43) that can transmit the first control parameter for the first theoretical volumetric flow rate (R1) and the measured value (SV1) of the first volumetric flow rate sensor (S1) and the second control parameter for the second theoretical volumetric flow rate (R2) and the measured value (SV2) of the second volumetric flow rate sensor (S2) as input values ​​(R1, SV1, R2, SV2). The volumetric flow rate regulator, taking into account the input values ​​(R1, SV1, R2, SV2), generates a first volumetric flow rate regulator signal (RV1) for controlling the first volumetric flow rate unit (V1) and / or generates a second volumetric flow rate regulator signal (RV2) for controlling the second volumetric flow rate unit (V2).

5. The apparatus (10) according to any one of the preceding claims, characterized in that, The third gas line (6) has a shut-off valve (V3) downstream of the blower (8) and upstream of the mixing volume (11).

6. The apparatus (10) according to claim 5, characterized in that, The control and regulation unit (15) is configured to control the shut-off valve (V3) based on input and / or based on the operating mode of the breathing apparatus (30).

7. The apparatus (10) according to any one of the preceding claims, characterized in that, The mixing volume (11) has a volume in the range of 50 ml to 300 ml.

8. The apparatus (10) according to any one of the preceding claims, characterized in that, The fourth gas line (7) has a concentration sensor (31) for determining the concentration value (M1), and / or the control and regulation unit (15) is configured to determine the concentration value by means of the measured values ​​(SV1, SV2, SV3) of the volumetric flow sensors (S1, S2, S3).

9. The apparatus (10) according to any one of the preceding claims, characterized in that, The device (10) has a pressure sensor (32) for determining the pressure value (M2).

10. The apparatus (10) according to any one of the preceding claims, characterized in that, The fourth inlet (16) for the external medium-pressure gas source is connected to the first dispensing unit (V1) or the second dispensing unit (V2) in a fluid-connected manner.

11. A method for providing a breathing gas flow (AS) to a breathing apparatus (10) having the means (10) according to any one of the preceding claims, Its characteristics include the following steps: - Receive at least one theoretical value (F1, F2, F3) of theoretical concentration (F1), theoretical pressure (F3) and / or theoretical volume (F2); - Taking into account the at least one theoretical value (F1, F2, F3), turn on the first dispensing unit (V1) and / or the second dispensing unit (V2) and / or activate the blower (8); - Determine the total volumetric flow rate (SV3); - Determine the concentration value (M1) of the respiratory gas flow (AS) and / or the pressure value (M2) of the fourth gas line (7); - The control and regulation unit (15) controls the first dosing unit (V1), the second dosing unit (V2), and / or the blower (8) based on the total volumetric flow rate (SV3), the concentration value (M1), and / or the pressure value (M2) while taking into account the at least one theoretical value (F1, F2, F3).

12. The method according to claim 11, characterized in that, The control and regulation unit (15) controls the first dosing unit (V1), the second dosing unit (V2) and / or the blower (8) in such a way that the breathing gas flow (AS) has a low pressure level downstream of the mixing volume (11), the low pressure level being in the range of 0 to 120 hPa.

13. The method according to claim 11 or 12, characterized in that, The control and regulation unit (15) puts the blower (8) into a passive state so that the blower does not contribute to the breathing gas flow (AS), wherein the blower (8) is turned on and the intake ambient air is blocked by the check valve (9).

14. The method according to any one of claims 11 to 13, characterized in that, In the inactive state of the blower (8), and in the case that the pressure supply and / or volume flow supply is insufficient, the blower (8) is activated.

15. The method according to any one of claims 11 to 14, characterized in that, According to the input and / or according to the operating mode of the device, the third gas line between the check valve (9) and the mixing volume (11) is closed.

16. A breathing apparatus (30) having a device (10) according to any one of claims 1 to 10.

17. Use of the device (10) according to claim 1 or any one of claims 3 to 10, wherein, The control and regulation unit (15) of the device (10) has a multi-parameter regulator (41) with a single-loop blower regulation circuit.

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