Device for supplying breathing gas

Abstract

The invention relates to a breathing gas supply device having at least one breathing gas line for conducting a breathing gas mixture, wherein the breathing gas line comprises at least one outlet via which the breathing gas mixture can be at least partially, at least periodically, discharged, wherein the breathing gas line comprises an inspiratory branch which is designed to conduct breathing gas to a connection for a patient interface, wherein the breathing gas line comprises an expiratory branch which is designed to conduct breathing gas between the connection for a patient interface and the outlet, characterised in that at least one shut-off valve is arranged in the breathing gas line, which is designed and arranged to at least periodically establish a breathing-gas-conducting connection from the expiratory branch to the inspiratory branch.

Description

[0001]Device for respiratory gas supply The invention relates to a device for anesthesia and / or ventilation. Anesthesia workstations are typically designed so that the respiratory gases are fed into a circuit, and used gases such as oxygen (O2) are added, and carbon dioxide (CO2) is removed from the circuit. In such a circuit, volatile anesthetics can be added and removed in a controlled manner. A respiratory gas source and check valves ensure that the gases flow in a defined direction. The inspired air is supplied to the patient via the inspiratory branch of the respiratory gas circuit. After inspiration, the patient's exhaled air reenters the circuit system via the expiratory branch. CO2 is then separated from the exhaled air, the respiratory gas is mixed with new fresh gases, and then returned to the patient. Typically, the CO2 is added to the respiratory gas mixture using a chemical CO2 absorber.withdrawn. The object of the present invention is to provide a device that can be used for the application of volatile anesthetics as well as for ventilation or respiratory support and that is simple, flexible, and yet safe to operate. This object is achieved with a device according to claim 1. Further developments and advantageous embodiments are the subject of the subclaims. Further advantages and features emerge from the general description and the description of the exemplary embodiments. It should be noted that the features listed individually in the claims can be combined with one another in any technically reasonable manner and show further embodiments of the invention. The description further characterizes and specifies the invention, particularly in conjunction with the figures. The subclaims relate to various independent, advantageous developments of theThe present invention relates to a device for supplying respiratory gas, comprising at least one respiratory gas line for conducting a respiratory gas mixture, wherein the respiratory gas line comprises at least one outlet via which the respiratory gas mixture can be discharged at least partially, at least temporarily, wherein the respiratory gas line comprises an inspiratory branch which is designed to conduct respiratory gas to a connection for a patient interface, wherein the respiratory gas line comprises an expiratory branch which is designed to conduct respiratory gas between the connection for a patient interface and the outlet, characterized in that at least one check valve is arranged in the respiratory gas line, which is designed and configured to at least temporarilyEstablish a connection from the expiratory branch to the inspiratory branch. In some embodiments, the device is characterized in that the device comprises at least one reservoir for the respiratory gas mixture and at least one blower configured to provide conveying energy for the respiratory gas mixture, wherein the reservoir and blower are arranged in or on the inspiratory branch. P580 In some embodiments, the device is characterized in that the blocking valve is designed as a check valve and is configured to establish the respiratory gas-conducting connection in a flow direction from the expiratory branch to the inspiratory branch. In some embodiments, the device is characterized in that the blocking valve is designed as a blockable check valve and is configured to at least temporarily block the respiratory gas line in both flow directions. In some embodiments, the devicecharacterized in that the device comprises a control device and at least one power source. In some embodiments, the device is characterized in that the shut-off valve is configured to block the respiratory gas line in both flow directions when energized by the at least one power source. In some embodiments, the device is characterized in that the shut-off valve is configured to prevent the respiratory gas-conducting connection from the expiratory branch to the inspiratory branch when energized. In some embodiments, the device is characterized in that the respiratory gas mixture can be completely discharged from the expiratory branch via the outlet when the shut-off valve is energized. In some embodiments, the device is characterized in that the inspiratory branch and the expiratory branch form at least one first circuit without energization of the shut-off valve, in which theA breathing gas mixture can be conducted, wherein the breathing gas mixture can be at least partially discharged via the outlet. In some embodiments, the device is characterized in that the device comprises at least one controllable pressure regulating valve. In some embodiments, the device is characterized in that the pressure regulating valve is configured to regulate an inspiratory pressure Pinsp and / or an expiratory pressure Pexsp. In some embodiments, the device is characterized in that the pressure regulating valve is manually and / or electrically adjustable. In some embodiments, the device is characterized in that the device comprises an APL valve for regulating the inspiratory pressure Pinsp. In some embodiments, the device is characterized in that the breathing gas mixture can be discharged via the outlet when the pressure in the breathing gas line exceeds the inspiratory pressure Pinsp. In someIn some embodiments, the device is characterized in that the APL valve is configured as a controllably loaded check valve. In some embodiments, the device is characterized in that the APL valve comprises a stepper motor, via which the APL valve can be adjusted. In some embodiments, the device is characterized in that the valve position of the APL valve is set and / or maintained under energization. In some embodiments, the device is characterized in that the valve position of the APL valve remains at the last set value without energization. In some embodiments, the device is characterized in that the APL valve can be adjusted manually and / or electrically. P580 In some embodiments, the device is characterized in that the device comprises a pressure control valve for regulating the expiratory pressure Pexsp. In some embodiments, theDevice characterized in that the pressure control valve is arranged in the expiratory branch. In some embodiments, the device is characterized in that the pressure control valve is configured to regulate an end-expiratory expiratory pressure PEEP. In some embodiments, the device is characterized in that the pressure control valve is configured to passively regulate to a preset expiratory pressure Pexsp without energization. In some embodiments, the device is characterized in that the preset expiratory pressure Pexsp of the pressure control valve is 3 hPa to 10 hPa, for example 5 hPa. In some embodiments, the device is characterized in that the respiratory gas mixture contains fresh gas and / or oxygen O2 and / or volatile anesthetics. In some embodiments, the device is characterized in that the device has at least one anesthetic supply line forIntroduction of volatile anesthetics into the breathing gas line. In some embodiments, the device is characterized in that a first pressure is present in the breathing gas line and that a second pressure is present in the anesthetic supply line, wherein the first pressure is lower than the second pressure. In some embodiments, the device is characterized in that the second pressure is at least 100 kPa, preferably at least 180 kPa. In some embodiments, the device is characterized in that the first pressure is less than 100 kPa, preferably less than 50 kPa, particularly preferably less than 10 kPa. In some embodiments, the device is characterized in that the first pressure is less than 8 kPa, preferably less than 5 kPa, particularly preferably less than 3 kPa. In some embodiments, the device is characterized in that the device is operable at room temperature. In some embodimentsThe device is characterized in that the volatile anesthetics are selected from the group: isoflurane, sevoflurane, desflurane, halothane, enflurane, methoxyflurane. In some embodiments, the device is characterized in that the volatile anesthetics in the anesthetic supply line can be conducted in liquid form to the breathing gas line. In some embodiments, the device is characterized in that the volatile anesthetics evaporate when introduced into the breathing gas line at an evaporation rate of 0 to 2 l / min. In some embodiments, the device is characterized in that the evaporated volatile anesthetics mix with the breathing gas mixture in the breathing gas line. In some embodiments, the device is characterized in that the device comprises at least one safety valve that is designed and configured to block the supply of volatile anesthetics. In some embodiments, theDevice characterized in that the safety valve is designed as a switching valve. In some embodiments, the device is characterized in that the safety valve is electrically P580 and / or manually adjustable. In some embodiments, the device is characterized in that the safety valve is designed as an electrically operated switching valve, wherein the safety valve is configured, without energization, to block the introduction of volatile anesthetics into the respiratory gas mixture. In some embodiments, the device is characterized in that the outlet comprises at least one filter. In some embodiments, the device is characterized in that the filter is replaceable. In some embodiments, the device is characterized in that respiratory gas mixture discharged via the outlet completely passes through the filter. In some embodiments, the device is characterized in thatcharacterized in that the filter is an absorbent and / or comprises an absorbent and is designed and configured to absorb at least volatile anesthetics and / or their metabolites. In some embodiments, the device is characterized in that the filter comprises activated carbon. In some embodiments, the device is characterized in that a double filter system with a first filter and a second filter is arranged at the outlet, wherein the second filter is arranged downstream of the first filter in the flow direction. In some embodiments, the device is characterized in that the device comprises at least one sensor arranged in or at the outlet. In some embodiments, the device is characterized in that the sensor is designed and configured to detect the concentration of volatile anesthetics and / or their metabolites and to transmit it to the control device. InIn some embodiments, the device is characterized in that the concentration of volatile anesthetics and / or their metabolites can be detected in the flow direction at least upstream and / or downstream of the first filter and transmitted to the control device. In some embodiments, the device is characterized in that the control device is configured to generate an alarm if the concentration of volatile anesthetics and / or their metabolites exceeds a limit value. In some embodiments, the device is characterized in that the device comprises a separating agent configured to separate at least CO2 from the respiratory gas mixture. In some embodiments, the device is characterized in that the separating agent is a chemical separating agent and / or a mechanical separating agent. In some embodiments, the device is characterized in that the chemical separating agent comprises at least oneContains a CO2-binding absorbent selected from the group consisting of calcium hydroxide, sodium hydroxide, potassium hydroxide, barium hydroxide, and soda lime. In some embodiments, the device is characterized in that the chemical separating agent can be permeated by expiratory respiratory gas exsp when the inspiratory branch and the expiratory branch form the circuit. In some embodiments, the device is characterized in that the mechanical separating agent is arranged in the expiratory branch. In some embodiments, the device is characterized in that the mechanical separating agent is adjacent to the connection for a patient interface. In some embodiments, the device is characterized in that the separating agent comprises at least one diffusion filter configured as a semipermeable membrane and permeable at least to CO2 molecules. In some embodiments, the device ischaracterized in that the diffusion filter is impermeable at least to volatile anesthetics. In some embodiments, the device is characterized in that the separating means is designed as a two-chamber system comprising at least a first chamber and at least a second chamber, wherein the first chamber and the second chamber are gas-conducting and are separated from each other by the diffusion filter. In some embodiments, the device is characterized in that the first chamber is configured to receive expiratory breathing gas exsp and that the second chamber is configured to receive a sweep gas, wherein the sweep gas has at least a lower CO2 concentration than the expiratory breathing gas exsp. In some embodiments, the device is characterized in that the first chamber is configured to guide the expiratory breathing gas exsp in the direction of a main flow, wherein the second chamber is configuredto guide the sweep gas in the direction of a sweep gas flow, wherein the flow direction of the main flow is opposite to the flow direction of the sweep gas flow. In some embodiments, the device is characterized in that the CO2 concentration of the sweep gas upon introduction into the second chamber is below 10%, preferably below 5%, particularly preferably 0%. In some embodiments, the device is characterized in that the device comprises at least one sweep gas supply line for providing sweep gas for the mechanical separating agent, wherein the sweep gas supply line comprises at least one valve for dosing sweep gas. In some embodiments, the device is characterized in that the flow rate of the sweep gas is greater than or equal to the flow rate of the expiratory breathing gas exsp. In some embodiments, the device is characterized in that the flow rate of the sweep gas is 0 to 20 l / min, preferably 0to 10 l / min. In some embodiments, the device is characterized in that the flow rate of the sweep gas is adjusted in relation to the minute volume. In some embodiments, the device is characterized in that the flow rate of the sweep gas is 1.1 to 2 times the minute volume, preferably 1.2 to 1.5 times the minute volume. In some embodiments, the device is characterized in that the device comprises at least one valve for dosing fresh gas and / or oxygen O2. In some embodiments, the device is characterized in that the device comprises at least one valve for dosing volatile anesthetics. In some embodiments, the device is characterized in that the dosing valves are selected from the group: needle valve, proportional valve, switching valve, orifice, throttle valve. In some embodiments, the device is characterized in that theDosing valves are designed as needle valves. In some embodiments, the device is characterized in that the dosing valves each comprise at least one stepper motor, via which the dosing valves can be adjusted. In some embodiments, the device is characterized in that the valve position of the dosing valves is set and / or maintained under current supply. In some embodiments, the device is characterized in that the valve position of the dosing valves remains at the last set value without current supply and / or falls to an open basic setting. In some embodiments, the device is characterized in that the device comprises at least one sensor for detecting at least one ventilation-specific parameter. In some embodiments, the device is characterized in that the ventilation-specific parameters comprise at least one of the following parameters:Inspiratory patient pressure, inspiratory patient flow, inspiratory tidal volume, inspiratory minute volume, inspiratory respiratory rate, inspiratory O concentration, inspiratory CO concentration, inspiratory NO concentration, inspiratory anesthetic gas concentration; expiratory patient pressure, expiratory patient flow, expiratory tidal volume, expiratory minute volume, expiratory respiratory rate, expiratory O concentration, expiratory CO concentration, expiratory NO concentration, expiratory anesthetic gas concentration; gas temperature, gas humidity, fresh gas flow, leakage. In some embodiments, the device is characterized in that the device comprises at least one storage unit that is configured and designed to store at least the ventilation-specific parameters detected during the respiratory gas supply. In some embodiments, the device is characterized in thatcharacterized in that the storage unit is configured to store patient parameters, wherein the patient parameters include at least one of the following parameters: age, weight, height, body mass index (BMI), pre-existing conditions. In some embodiments, the device is characterized in that the flow rate of the sweep gas is dynamically adaptable to the ventilation-specific parameters and / or to the patient parameters. In some embodiments, the device is characterized in that the respiratory gas line comprises a bypass that branches off from the inspiratory branch and opens into the expiratory branch between the mechanical separating means and the outlet. In some embodiments, the device is characterized in that the bypass is configured to at least temporarily establish a respiratory gas-conducting connection from the inspiratory branch to the expiratory branch such that a second circuit is formed, inthrough which the respiratory gas mixture can be conducted. In some embodiments, the device is characterized in that the second circuit corresponds at least partially to the first circuit, wherein the connection for a patient interface is arranged only in the first circuit. In some embodiments, the device is characterized in that the mechanical separating means is arranged only in the first circuit. P580 In some embodiments, the device is characterized in that the bypass comprises at least one bypass shut-off valve. In some embodiments, the device is characterized in that the bypass shut-off valve is designed as a check valve and is configured to at least temporarily establish the respiratory gas-conducting connection in a flow direction from the inspiratory branch to the expiratory branch. In some embodiments, the device is characterized in that the bypass shut-off valve is designed as a lockable check valveis designed and configured to at least temporarily block the bypass in both flow directions. In some embodiments, the device is characterized in that the bypass blocking valve is configured to block the bypass in both flow directions when energized by the at least one power source. In some embodiments, the device is characterized in that the respiratory gas mixture can be conducted at least partially in the second circuit without energizing the blocking valve and the bypass blocking valve. In some embodiments, the device is characterized in that the respiratory gas mixture in the first circuit can be conducted with the main flow and that the respiratory gas mixture in the second circuit can be conducted with a bypass flow. In some embodiments, the device is characterized in that the main flow depends on the breathing phases of a patient to be ventilated. In some embodiments, the devicecharacterized in that the bypass flow is independent of the breathing phases of a patient to be ventilated. In some embodiments, the device is characterized in that at least the bypass flow of the second circuit is directed through the PEEP valve. In some embodiments, the device is characterized in that the device is operable in different operating modes. In some embodiments, the device is characterized in that the device is operable in automatic operating modes in which the blower supplies the conveying energy for the respiratory gas mixture. In some embodiments, the device is characterized in that the device is operable in manual operating modes in which the reservoir supplies the conveying energy for the respiratory gas mixture. In some embodiments, the device is characterized in that the reservoir is designed as a hand bag. In some embodiments,The device is characterized in that the device is operable in working modes with the application of volatile anesthetics and / or in working modes without the application of volatile anesthetics, wherein the safety valve is configured to permit the introduction of volatile anesthetics into the respiratory gas mixture when energized and to block the introduction of volatile anesthetics into the respiratory gas mixture when energized. In some embodiments, the device is characterized in that the device is operable in a working mode selected from the group: anesthesia mode with volatile anesthetics; anesthesia mode with intravenously administered anesthetics (TIVA mode); ventilation mode with anesthetics; ventilation mode without anesthetics, O therapy mode, high-flow O therapy mode (HFOT mode), CPAP mode, bi-level mode, SIMV mode, emergency mode. In some embodiments, the device is characterized in that the working mode can be manually and / orcan be set automatically by the control unit. In some embodiments, the device is characterized in that the device can be operated in an emergency mode without a power supply and / or in a power-saving mode. In some embodiments, the device is characterized in that the emergency mode occurs automatically and / or can be set manually. In some embodiments, the device is characterized in that the emergency mode occurs automatically when the functions of the power source and / or the control device and / or the blower are restricted or fail. In some embodiments, the device is characterized in that the breathing gas mixture can be conducted in the emergency mode at least in the first circuit, wherein the breathing gas mixture can be at least partially discharged via the outlet. In some embodiments, the device is characterized in that the breathing gas mixture can be conducted in the second circuit in the emergency mode. InIn some embodiments, the device is characterized in that the delivery energy for the respiratory gas mixture in emergency mode is provided by the reservoir. In some embodiments, the device is characterized in that the APL valve regulates to the last set inspiratory pressure Pinsp in emergency mode. In some embodiments, the device is characterized in that the pressure control valve passively regulates the expiratory pressure Pexsp in emergency mode. In some embodiments, the device is characterized in that the chemical separating agent and / or the mechanical separating agent is active without energization. In some embodiments, the device is characterized in that the safety valve is closed in emergency mode, wherein the safety valve can be opened manually. In some embodiments, the device is characterized in that the metering valves are not energized in emergency mode, sothat the dosage of fresh gas and / or oxygen and / or volatile anesthetics and / or sweep gas is maintained at the last set value. In some embodiments, the device is characterized in that the valve for dosing sweep gas in emergency mode sets the sweep gas dosage to 1.2 to 2 times the last set minute volume, preferably to 1.5 times. In some embodiments, the device is characterized in that fresh gas and / or oxygen are supplied to the breathing gas mixture in emergency mode via the dosing valves. In some embodiments, the device is characterized in that the fresh gas and / or oxygen are each provided in at least one compressed gas cylinder, wherein the pressure of the compressed gas cylinders provides the delivery energy for the fresh gas and / or the oxygen. In some embodiments, the device is characterized in that the volatile anesthetics are eachat least one tank, wherein a pressure is present in the tanks. In some embodiments, the device is characterized in that the pressure in the tanks is at least 100 kPa, preferably at least 180 kPa. In some embodiments, the device is characterized in that the pressure in the tanks provides the conveying energy for the volatile anesthetic. In a further aspect, the invention relates to a method for introducing at least one volatile anesthetic into a breathing gas mixture, wherein the breathing gas mixture is conducted in a breathing gas line under a first pressure, characterized in that the volatile anesthetic is conducted in liquid form in an anesthetic supply line under a second pressure to the breathing gas line, wherein the first pressure is lower than the second pressure, wherein the volatile anesthetic is exposed to the first pressure upon entering the breathing gas line and becomes gaseous. In theThe device 100 according to the invention is described by way of example in the following exemplary embodiments. Further features and advantages of the present invention will become clear in the following descriptions of exemplary embodiments with reference to the figures. The invention is not limited to the illustrated exemplary embodiments. The device 100 is designed for supplying respiratory gas. The device 100 has a ventilation function and / or an anesthesia function. The device 100 can thus be used as a ventilator or as an anesthesia device. The device 100 can also be used as a ventilator and as an anesthesia device. Thus, using the device 100, a patient can be ventilated or assisted in breathing and, alternatively or additionally, can also be kept under anesthesia. A ventilator is understood to mean all devices that support a user or patient in natural breathing and / or ventilation.of a user or patient and / or serve for respiratory therapy and / or otherwise influence the breathing of a user or patient. The term "ventilation" as used herein encompasses, within the meaning of the invention, all forms of ventilation, respiratory support, or respiratory therapy. The term "ventilation" also sometimes includes anesthesia, namely always in the event that volatile anesthetics or anesthetic gases are added to the respiratory gas. A user or patient can be connected to the device 100 via a patient interface 91. Within the meaning of the invention, a patient interface 91 is understood to be any peripheral device designed for interaction with an individual. The patient interface 91 can be designed as a tracheal tube or tracheostomy cannula. The patient interface 91 can also be designed as a breathing mask, nasal mask, nasal cushion mask, nasal cannula or oxygen cannula, full-face or total-face mask.The patent interface 91 is preferably configured and designed such that a leak-free supply and / or discharge of a respiratory gas mixture from the device 100 to the patient and / or from the patient to the device 100 can be carried out. P580 The figures show exemplary embodiments of the device according to the invention. They show: Figure 1 shows a schematic structure of the device in a first exemplary embodiment. Figures 1A to 1G show the operation of the device in various operating modes using the first exemplary embodiment as an example, where - Figure 1A shows the device in a first operating mode for manual ventilation with the application of volatile anesthetics; - Figure 1B shows the device in a second operating mode for automatic ventilation with the application of volatile anesthetics; - Figure 1C shows the device in a third operating mode for manual ventilation without the application of volatile anesthetics; - Figure 1D shows the device in a fourthWorking mode for automatic ventilation without application of volatile anesthetics; - Figure 1E shows the device in a fifth working mode for manual ventilation in a battery and / or error mode; - Figure 1F shows the device in a sixth working mode for a constant flow (HFOT), wherein volatile anesthetics can optionally be applied; - Figure 1G shows the device in a seventh working mode, which represents a service mode; Figure 2 schematically shows an exemplary structure of the supply lines. Figure 3 schematically shows a section of the breathing gas line in which the evaporation element is arranged, which is connected to the anesthetic module via the anesthetic supply line. Figure 4 shows a schematic structure of the device in a second exemplary embodiment. Figure 5 shows a schematic structure of the mechanical separating means with diffusion filter. Figure 1 shows a schematic structure of the device 100 in a first exemplary embodiment.The device 100 according to the invention is designed for supplying respiratory gas and comprises at least one respiratory gas line 4 for conducting a respiratory gas mixture 5, wherein the respiratory gas line 4 comprises at least one outlet 14-A, via which the respiratory gas mixture 5 can be at least partially, at least temporarily, discharged, wherein the respiratory gas line 4 comprises an inspiratory branch 1, which is designed to conduct respiratory gas to a connection 93 for a patient interface, wherein the respiratory gas line 4 comprises an expiratory branch 2, which is designed to conduct respiratory gas between the connection 93 for a patient interface and the outlet 14-A. The device 100 is characterized in that at least one check valve 28 is arranged in the respiratory gas line 4, which is designed and configured to at least temporarily establish a respiratory gas-conducting connection from the expiratory branch 2 to the inspiratory branch 1. The device 100 according to the invention can be aAnesthesia workstation. The device 100 can be configured to ventilate and / or anesthetize a living being. For this purpose, the device 100 can be configured to provide and / or conduct and / or prepare and / or dispose of a respiratory gas mixture or an anesthetic gas mixture. The device P580 100 is configured and designed to mechanically and / or manually ventilate or anesthetize a living being. For this purpose, the device 100 comprises at least one respiratory gas line 4 and at least one discharge system 14. The device 100 has at least one blower unit 3. The blower unit 3 is configured and designed to generate a respiratory gas flow for ventilating and / or anesthetizing a patient and, if necessary, to convey it towards the patient. The blower unit 3 can be used to convey a respiratory gas mixture 5 for ventilation and / or anesthesia. The blower unit 3 can thus supply the conveying energy forsupply the breathing gas mixture 5. The breathing gas mixture 5 can be normal breathing air from the environment or pure oxygen O2 or breathing air enriched with oxygen O2. In particular, the breathing gas mixture 5 can also contain at least one anesthetic A. The breathing gas mixture 5 can thus also be an anesthetic gas. The breathing gas flow can be supplied from the ambient air and / or from compressed gas cylinders and / or from a central gas system (CGS) of the hospital (not shown). The blower unit 3 is preferably designed as at least one blower 3, which can comprise at least one fan wheel for generating a breathing gas flow. In some embodiments, several blowers 3 can also be connected in series or in parallel. In alternative embodiments, the device 100 can also have another technical unit instead of the blower, which can generate a breathing work or a conveying energy for the breathing gas mixture.In such a case, the blower unit 3 can, for example, comprise at least one driven bellows or at least one piston motor. In an alternative embodiment, the device 100 can thus also be operated with a piston motor with, for example, several pistons and corresponding valves (not shown). In preferred embodiments, the blower unit 3 is designed as at least one blower 3. From now on, for the sake of simplicity, the blower unit 3 will sometimes be referred to simply as blower 3 - this does not exclude the above-mentioned embodiments with several blowers, technical units, bellows, or piston motors. To operate the blower 3, the device 100 can comprise at least one electric drive (not shown). The device 100 can be supplied with power via at least one power source 103, 104 shown here. Preferably, the device can be powered via a primary power source 103 and alternatively via at leasta secondary power source 104. For this purpose, the device 100 can have a mains plug and accumulators and / or capacitors arranged inside the device. The device 100 can be connected to the mains supply via a mains plug and thus supplied with energy. The mains plug and mains supply can then serve as the primary power source 103. Alternatively or additionally, the device can be supplied with energy via the accumulators / capacitors. The accumulators / capacitors can then serve as the secondary power source 104. Thus, the device 100 can be operated in mains operation and / or in battery operation. P580 The device 100 can comprise at least one display device (not shown). The display device can be configured as a monitor, for example, a touchscreen for displaying and / or entering medical data. The arrangement of multiple monitors is also possible.Device 100 comprises at least one control device 101 and at least one memory unit 102. The blower 3 is controlled by the control device 101. As a rule, the control device 101 controls the blower 3 according to the configurations stored in the memory unit 102. For example, the control device 101 sets a specific speed of the fan wheel or regulates the fan speed to a target value. In this way, the blower 3 can specify a flow and / or a pressure and / or a volume of respiratory gas. In a preferred embodiment, the blower 3 can generate a defined flow. In a particularly preferred embodiment, the blower 3 can generate a pressure-independent flow. Flow and pressure can be specified decoupled from one another, so that the flow can be generated independently of the pressure. This offers the advantage that, when the required flow is specified, different pressure-controlled breathing patternscan be constructed. For example, the setpoint of the flow can be adjusted based on therapy specifications and / or sensor signals. The device 100 is in particular set up and designed to provide the respiratory gas mixture 5 in the form of a patient flow. The patient flow serves to supply the patient with respiratory gas. The patient flow can be dependent on the patient's breathing phases. Alternatively or additionally, the device 100 is set up and designed to provide a permanent byflow. The byflow can exist independently of the patient's breathing phases. Patient flow and byflow can be formed parallel to one another in the respiratory gas line 4. The device 100 comprises at least one sensor 15, 16, 17, 18, 19, 20, 39. In a preferred embodiment, the device 100 comprises a plurality of sensors 15, 16, 17, 18, 19, 20, 39 (see below). The blower 3 can be controlled adaptively. An adaptive control can, for example,based on ventilation parameters determined and analyzed during ventilation. The storage unit 102 is configured to store ventilation-relevant parameters. These ventilation-relevant parameters can be ventilation-specific parameters 110 recorded during the respiratory gas supply and / or patient parameters 111 stored in the storage unit 102. The patient parameters 111 can be determined in advance. The patient parameters 111 can also be determined during ventilation. The stored patient parameters 111 can be selected from the group: age, gender, weight, height, previous illnesses, body fat percentage, body mass index (BMI), ideal body weight (BWI), state of health, nutritional status, patient metabolism, tidal volume, indirect calorimetry, and the like. P580 The blower 3 comprises at least one blower outlet 3a. The blower 3 discharges the respiratory gas mixture 5 via the blower outlet 3a into the at leasta breathing gas line 4. The breathing gas mixture 5 is conveyed via the breathing gas line 4. The blower 3 sets a main flow S of the breathing gas mixture 5, the direction of which is indicated in Figure 1 by dashed lines. The breathing gas line 4 comprises an inspiratory branch 1. In addition, the breathing gas line 4 can comprise an expiratory branch 2. The breathing gas line 4 can also comprise a reservoir line 13. The inspiratory branch 1 can be designed to at least conduct breathing gas to a connection 93 for a patient interface. The expiratory branch 2 can be designed to at least conduct breathing gas between the connection 93 for the patient interface and at least one outlet 14-A. A patient interface can be connected to the connection 93, via which a connection to a patient 90 can be established. The reservoir line 13 can be considered a component of the inspiratory branch 1. Via the reservoir line 13The reservoir 12 is pneumatically connected to the respiratory gas line 4. Gases from the reservoir 12 can be introduced at at least one reservoir feed point 213. The respiratory gas line 4 can be pneumatically connected to the discharge system 14 for discharging the respiratory gas mixture 5. The respiratory gas line 4 with its inspiratory branch 1 and its expiratory branch 2 can be formed at least partially in the device. The respiratory gas line 4 with its inspiratory branch 1 and its expiratory branch 2 can also be formed at least partially outside the device, for example in a hose system. In the specific embodiment according to the figures, the respiratory gas line 4 comprises the reservoir line 13, the inspiratory branch 1, and the expiratory branch 2, which are pneumatically connected to one another. The respiratory gas line 4 is also pneumatically connected to the discharge system 14. For introducing the respiratory gases and / orAnesthetics To provide the respiratory gas mixture 5, the respiratory gas line 4 is pneumatically connected to at least one fresh gas supply line 7 and / or to at least one O2 flush supply line 11 and / or to at least one anesthetic supply line 9 and / or to a nitrogen oxide supply line 44. The supply lines 7, 9, 11, 44 generally open into the inspiratory branch 1 of the respiratory gas line 4. Respiratory gases and / or anesthetics are fed into the respiratory gas line 4 via the supply lines 7, 9, 11, 44. Check valves in the supply lines 7, 9, 11, 44 ensure that the respiratory gas mixture 5 cannot be discharged via the supply lines 7, 9, 11, 44. The blower 3 is preferably arranged in the inspiratory branch 1. The blower 3 is preferably arranged downstream of the expiratory branch 2. In the inspiratory branch 1, inspiratory breathing gas 5 is usually inspFresh gas and / or oxygen and / or anesthetics can be introduced into the inspiratory branch 1. At least the blower 3 can be arranged in the inspiratory branch to specify the respiratory gas flow S. The inspiratory respiratory gas 5 can be supplied via the inspiratory branch 1 P580. insp. via the patient interface to the patient 90. In the expiratory branch 2, expiratory breathing gas 5 is usually exsp The patient 90 can exhale 5 exsp. via the patient interface into the expiratory branch 2. The expiratory breathing gas 5 can be delivered via the expiratory branch 2 exsp. away from the patient. The expiratory breathing gas 5 can be diverted via the expiratory branch 2 exsp.to a device 40 for separating at least CO2. The expiratory branch 2 can extend at least from the patient interface to the separating means 40, 60. The main flow S of the respiratory gas mixture 5 can run from the blower outlet 3a along the inspiratory branch 1 to a connection 93 for a patient interface. From the connection 93, the respiratory gas mixture 5 can run along the expiratory branch 2 back to the inspiratory branch 1. For example, the respiratory gas mixture 5 can run along the expiratory branch 2 to the blower inlet of the blower 3 (not shown in detail here). The respiratory gas can thus remain in at least one - essentially - closed first circuit K1. Inspiratory branch 1 and expiratory branch 2 can thus form at least the first circuit K1, in which the respiratory gas mixture 5 can be conducted.In this case, the breathing gas mixture 5 can be at least partially discharged via the outlet 14-A. The breathing gas mixture 5 can be conducted in the first circuit K1 with the main flow S. In addition to a patient flow, a permanent byflow can advantageously also flow in the circuit K1. The byflow offers the advantage that the blower 3 does not have to be stopped during operation. The blower 3 always rotates at a minimum speed. The byflow ensures a permanent flow in the breathing gas line 4. A patient interface 91 can be connected to the connection 93, via which the patient is supplied with the breathing gas mixture 5. The breathing gas mixture 5 can be supplied to the patient 90 via the inspiratory branch 1. For this purpose, the device 100 has at least one interface for coupling a hose system 92. The breathing gas mixture 5 can be supplied to the patient 90 via the hose system 92.For this purpose, a patient interface 91 can be connected to the hose system 92. The hose system 92 can be a two-hose system and have at least one inspiration tube and at least one expiration tube. In this case, the patient 90 can be supplied with the breathing gas mixture 5 via the inspiration tube of the hose system 92 and the patient interface 91 and exhale via the expiration tube of the hose system 92. Thus, the exhalation gas can be returned to the device 100 via the expiration tube, and at least one closed circuit can exist. A closed circuit exists when the exhalation gas—after processing—is reused for inspiration. When using a two-hose system, the connection 93 can be designed as a Y-piece, via which the inspiration tube and the expiration tube can be connected.P580 In some embodiments, the tube system 92 can also be a single-tube system and have only one inspiratory tube. In this case, the patient 90 can be supplied with the breathing gas mixture 5 via the tube system 92 and the patient interface 91 and exhale into the environment. Thus, an open circuit without an expiratory branch can exist. In some embodiments, the tube system 92 can also be a two-tube system and have an inspiratory tube and an expiratory tube, without the breathing gas flowing in a closed circuit. This system is referred to herein as a semi-open circuit.A semi-open circuit in the sense of the invention means that the patient 90 can be supplied with the respiratory gas mixture 5 via the inspiratory tube of the tube system 92 and the patient interface 91 and can exhale via the expiratory tube of the tube system 92, wherein the exhaled gas is released into the environment via the expiratory tube. The device 100 is configured and designed to form a closed circuit and / or a semi-open circuit and / or an open circuit, depending on the use of the tube system and the settings in the device 100. The device 100 can thus be used flexibly, since the respiratory gas line 4 can form a closed circuit and / or a semi-open circuit and / or an open circuit. Depending on the application, it is possible to switch between a closed circuit, a semi-open circuit, and / or an open circuit.A closed circuit in the sense of the invention means that the breathing gas mixture 5 is circulated in the main flow S, wherein oxygen O2 and / or anesthetics and / or other gases or gas components or substances can be added to or removed. Gas exchange takes place in the patient's lungs. Oxygen (O2) is absorbed into the blood and carbon dioxide (CO2) is excreted. The patient thus removes gas or gas components from the circuit and adds new and / or changed gases or gas components to the circuit. Thus, gases or gas components must generally be continuously removed and / or added to the breathing gas mixture circulated in the circuit. For example, oxygen O2 and / or anesthetics and / or other gases can be replenished as needed. Carbon dioxide (CO2) and / or other undesirable gas components can be removed from the circuit.Thus, the gas components can be used and / or removed and disposed of in a defined manner. The control device 101 and / or a user can regulate / control the proportions of the components of the breathing gas mixture 5. For this purpose, fresh gas and / or oxygen O2 and / or anesthetics and / or CO2 are introduced or diverted or separated. The device 100 can comprise at least one PAUX connection for pneumatic accessories (not shown). Preferably, the device 100 comprises more than one connection, for example two or three or four or more. The PAUX connections can be configured and designed to connect ventilation- and / or anesthesia-relevant accessories to the device 100. These accessories can be selected from the group: laryngeal mask, tracheal tube, cuff, esophageal catheter, bladder catheter.These accessories can perform their function with the aid of a P580 balloon, which can be supplied with flow and / or pressure and / or volume via the PAUX ports. The PAUX ports can be configured and designed such that the functions of the connected accessories can be automatically checked. For this purpose, the device 100 can be designed to supply or remove flow and / or pressure to the PAUX ports. Furthermore, sensors can be connected to the PAUX ports to check the functionality of the accessories. To monitor the gas composition of the breathing gas mixture 5, the device 100 can comprise at least one sensor 19. The at least one sensor 19 is arranged in and / or on the breathing gas line 4. The sensor 19 can, for example, detect the oxygen concentration and / or the CO2 concentration (capnometry) and / or the concentration of one or more anesthetics and / or the humidity.The sensor 19 can therefore be designed as an oxygen sensor and / or CO2 sensor and / or an anesthetic gas sensor and / or a humidity sensor. The device 100 can alternatively or additionally also comprise a multi-gas sensor 20. The multi-gas sensor 20 is configured and designed to detect different gas components in parallel. In a preferred embodiment, the device 100 comprises at least one multi-gas sensor 20. The sensors 19 and / or the multi-gas sensor 20 are arranged at at least one location on the respiratory gas line 4. The sensors 19 and / or the multi-gas sensor 20 detect the gas composition of the respiratory gas mixture 5. The sensors 19 and / or the multi-gas sensor 20 can be arranged in the inspiratory branch 1 and / or the expiratory branch 2 of the respiratory gas line 4.In an exemplary embodiment according to the figures, at least one multigas sensor 20 can be arranged directly in front of the patient at or near the patient interface. For example, the multigas sensor 20 can be connected to the Y-piece 93 of the tubing system 92. The multigas sensor 20 can take a sample gas from the Y-piece 93 in order to measure inspiratory and expiratory values. In some embodiments, a switching valve can be provided on the multigas sensor 20 in order to measure the anesthetic concentration directly at the anesthetic evaporation point. This has a safety aspect when the anesthetic needs to be changed. However, it can also be used to accelerate the regulation of the anesthetic concentration. This is advantageous because the total gas volume of the device and lungs is very large (8-9 liters) and the anesthetic must be mixed in.In some embodiments, the sensors 19 can also be arranged at multiple locations on the breathing gas line 4 in order to monitor the gas composition of the breathing gas mixture 5 in detail. For example, CO2 sensors and / or O2 sensors can be arranged before and after the patient, as well as before and after a device for CO2 separation, namely a chemical separation means 40 and / or a mechanical separation means 60 (see below). This allows the functioning of the separation means 40, 60 to be monitored. P580 In an exemplary embodiment according to the figures, at least one oxygen sensor 19 can be arranged directly after the blower 3 and detect the oxygen concentration. The control or regulation of the components of the breathing gas mixture 5 is carried out by the control device 101. Stored instructions and / or preset therapy conditions and / or user specifications and / or the detected sensor signals can be taken into account here.The user settings can be made manually by a user, such as a medical professional. The user settings can be made in advance and / or during ventilation / anesthesia. The control device 101 takes into account, in particular, the recorded sensor signals. In particular, the sensor signals of the at least one CO2 sensor 19 and / or O2 sensor 19 and / or anesthetic gas sensor 19 and / or multigas sensor 20 are taken into account. Thus, the control device 101 can be capable of adaptively adjusting the components of the breathing gas mixture 5 to the respective situation during ventilation or anesthesia. Typically, the breathing gas mixture 5 returns to the circuit of the breathing gas line 4 after flowing through the sensors 19 or the multigas sensor 20 and being measured.However, it is also possible for respiratory gas mixture 5 to be taken from the circuit in order to examine its gas components without the gas being subsequently returned to the circuit. This can be advantageous for making the evaluation of the measurement signals more sensitive. The device can preferably comprise at least one flow sensor 17, 18 and / or at least one pressure sensor 15, 16, 39. The device 100 can comprise at least one inspiratory flow sensor 17. The at least one inspiratory flow sensor 17 can be arranged, for example, downstream of the blower 3 in the inspiratory branch 1 of the respiratory gas line 4. In the exemplary embodiment according to Figure 1, the inspiratory flow sensor 17 is arranged between the blower 3 and the O2 flush supply line 11. The inspiratory flow sensor 17 is configured and designed to measure at least one inspiratory flow.Alternatively or additionally, the device 100 can comprise at least one inspiratory pressure sensor 15. The at least one inspiratory pressure sensor 15 can, for example, be arranged downstream of the blower 3 in the inspiratory branch 1 of the respiratory gas line 4. In the exemplary embodiment according to Figure 1, the inspiratory pressure sensor 15 is arranged directly in front of the patient 90 or the patient interface. The inspiratory pressure sensor 15 is configured and designed to measure at least one inspiratory pressure. Alternatively or additionally, the device 100 can comprise at least one pressure sensor 39. The pressure sensor 39 can, for example, be arranged in or on the reservoir line 13. In the exemplary embodiment according to Figure 1, the pressure sensor 39 is arranged adjacent to the reservoir 12 in the reservoir line 13. The pressure sensor 39 is configured and designed to measure at least one pressure of the reservoir 12.The bag pressure of the reservoir 12 can be detected via the pressure sensor 39. The pressure sensor 39 can transmit the detected pressure values ​​to the control device 101 in order to monitor the pressure of the reservoir 12. P580 Furthermore, the device 100 can comprise at least one expiratory flow sensor 18. The at least one expiratory flow sensor 18 can be arranged, for example, in the expiratory branch 2 of the respiratory gas line 4. The expiratory flow sensor 18 is set up and designed to measure at least one expiratory flow. Alternatively or additionally, the device 100 can comprise at least one expiratory pressure sensor 16. The at least one expiratory pressure sensor 16 can be arranged, for example, in the expiratory branch 2 of the respiratory gas line 4. In the exemplary embodiment according to Figure 1, the expiratory pressure sensor 16 is arranged directly after the patient 90 or the patient interface.The expiratory pressure sensor 16 is configured and designed to measure at least one expiratory pressure.The flow sensors 17, 18 and / or pressure sensors 15, 16, 39 and / or sensors 19, 20 are designed as measuring devices and record at least one ventilation-specific parameter 110 selected from the group: inspiratory patient pressure, inspiratory patient flow, inspiratory tidal volume, inspiratory minute volume, inspiratory respiratory rate, inspiratory O2 concentration, inspiratory CO2 concentration, inspiratory N2O concentration, inspiratory anesthetic gas concentration; expiratory patient pressure, expiratory patient flow, expiratory tidal volume, expiratory minute volume, expiratory respiratory rate, expiratory O2 concentration, expiratory CO2 concentration, expiratory N2O concentration, expiratory anesthetic gas concentration; gas temperature, gas humidity, leakage, or the like. The ventilation-specific parameters 110 to be recorded are not limited to these examples.The control device 101 is configured and designed to adaptively regulate the operation of the device 100 depending on determined and analyzed ventilation parameters. Measured values ​​and parameters from accessories such as cuff pressure (tube seal), pressure of a gastric or bladder catheter, laryngeal mask seal pressure, leakage, resistance, bag pressure, or the like can also be recorded and incorporated. Based on these ventilation-specific parameters 110, the control device 101, which is in communication with the measuring devices, can determine the technical ventilation parameters and, in particular, also adapt them adaptively. In addition to pressure, flow, or volume, the technical ventilation parameters also include the supply of fresh gas and / or oxygen O2 and / or anesthetics. Based on the measuring devices, a possible leak can also be detected and transmitted to the control device 101.The device 101 can comprise an alarm device that can trigger an alarm signal upon detection of a leak. The device 100 can have at least one reservoir 12 and at least one reservoir line 13. The reservoir 12 can be designed, for example, as a hand-held bag. The reservoir 12 can alternatively or additionally also be designed as a breathing bellows. The reservoir 12 can supply the delivery energy P580 for the breathing gas mixture 5. The reservoir 12 can, in particular, be actuated manually by a user. For example, a user can actuate the reservoir 12 by squeezing it together, so that delivery energy is provided for the breathing gas mixture 5. The reservoir 12 is, among other things, set up and designed to provide a volume for the breathing gas mixture 5 for the purpose of pressure monitoring or pressure equalization. For this purpose, the reservoir 12 is pneumatically connected to the breathing gas line 4 via the reservoir line 13.The reservoir 12 can serve both as a pressure source and as a pressure sink. The reservoir 12 can also serve as a volume source and as a volume sink. The reservoir line 13 is configured such that a flow of the respiratory gas mixture 5 towards the reservoir 12 is possible. The reservoir line 13 is also configured such that a flow of the respiratory gas mixture 5 away from the reservoir 12 is possible. During inspiration, the reservoir 12 can serve as a pressure and / or volume source. During expiration, the reservoir 12 can serve as a pressure and / or volume sink. The reservoir 12 comprises, for example, at least the volume of one breath. For example, the reservoir 12 comprises at least 250 ml, preferably at least 500 ml, particularly preferably at least 1 liter. In a specific exemplary embodiment, the reservoir comprises between 1 liter and 5 liters, for example between 2 liters and 2.5 liters.The reservoir 12 is, among other things, designed and constructed to provide a volume for delivery to the blower 3. A large portion of the tidal volume delivered to the patient 90 can be delivered from the reservoir 12 via the blower 3 to the patient 90. When the patient 90 breathes, a gas exchange takes place in the lungs, which reduces the volume per breath. Therefore, volume must always be added to the closed circuit to at least replace the exhaled oxygen. In some embodiments, at least one of the O2 flush supply lines 11 of the device 100 can be arranged such that the reservoir 12 can be filled directly with oxygen. This can provide an additional safety level, as the reservoir 12 can thus be filled quickly and directly with a large amount of oxygen and / or an oxygen mixture.This can be particularly advantageous when the device 100 is operated in a TIVA mode and / or an HFOT mode. In some embodiments, the device 100 can comprise at least one pressure sensor 39. The pressure sensor 39 can be configured and designed to detect the pressure of the reservoir 12. The pressure sensor 39 is preferably arranged in or on the reservoir line 13. The pressure sensor 39 can be configured and designed to detect the pressure of the reservoir 12 and transmit it to the control device 101. The filling state of the reservoir 12 can be detected and monitored via the pressure sensor 39. A maximum and / or a minimum pressure of the reservoir 12 can be stored in the control device 101. If the pressure in the reservoir 12 falls below a critical level and / or the pressure P580 in the reservoir 12 rises above a critical level, an action can be triggered. For example, an alarm can be triggered.For this purpose, the device 100 can comprise an alarm device controlled by the control device 101 (not shown). The alarm can signal the control device 101 and / or the user, i.e., the medical personnel, that the pressure in the reservoir 12 needs to be increased or decreased. If the minimum pressure of the reservoir 12 is undershot, pressure can build up in the reservoir 12. For example, the fresh gas module 6 and / or the O2 flush 10 can be controlled or actuated such that fresh gas and / or oxygen is introduced into the reservoir 12 to increase the pressure in the reservoir 12. If the maximum pressure of the reservoir 12 is exceeded, pressure can be released from the reservoir 12. For this purpose, the reservoir line 13 is pneumatically connected to the discharge system 14. The discharge system can comprise at least one overflow valve 25, via which pressure can be released from the reservoir 12.This prevents overfilling of the reservoir 12. The device 100 can comprise at least one discharge system 14, via which excess gases, for example excess respiratory gas mixture 5, can be discharged. The discharge system 14 can be configured and designed to discharge at least a portion of the respiratory gas mixture 5 for the purpose of pressure monitoring or pressure equalization. The discharge system 14 can also be configured and designed to regulate the oxygen and / or anesthetic concentration of the respiratory gas mixture 5. The discharge system 14 is designed as a gas-carrying line and is pneumatically connected to the respiratory gas line 4. The discharge system 14 comprises at least one outlet 14-A. The discharge system 14 can comprise one or more lines, all of which open into the same outlet 14-A (see Figure 1). Multiple lines with multiple outlets 14-A are also possible (not shown).Breathing gas mixture 5 can be conveyed with a flow S3 via the conveying system 14. The direction of the flow S3 always runs from the breathing gas line 4 towards the outlet 14-A. In the specific exemplary embodiment according to Figure 1, the conveying system 14 comprises, for example, three lines, namely the first line 14i, the second line 14ii, and the third line 14iii. The lines 14i, 14ii, 14iii are each pneumatically connected at least to the breathing gas line 4 and each open into the outlet 14-A. In this way, the breathing gas mixture 5 can be discharged from the breathing gas line 4 via at least three different routes. Multiple lines and multiple outlets 14-A are conceivable. The device 100 is not limited to the exemplary embodiments illustrated. The breathing gas mixture 5 can be discharged into the environment via the outlet 14-A or can remain in the circuit.For this purpose, the discharge system 14 can optionally have a pump (not shown here), which can direct the discharged respiratory gas mixture 5 from the outlet 14-A via a line (not shown) back to the fresh gas module 6. P580 The outlet 14-A can comprise at least one filter 94 (not shown). In preferred embodiments, the outlet 14-A can comprise a double filter system. Multiple filters 94 are also conceivable. The filters 94 are preferably arranged interchangeably at the outlet 14-A. The discharged respiratory gases can be filtered via the filters 94 at the outlet 14-A, thus preventing substances that are potentially harmful to the environment or health from escaping unfiltered into the environment. The filter 94 can, for example, comprise activated carbon. Activated carbon can act as an absorbent for volatile anesthetics and / or their metabolites and / or other substances.The filters 94 can thus be designed as activated carbon filters, with which volatile anesthetics VA and / or their metabolites and / or other substances potentially harmful to the environment or health can be filtered out of the discharged respiratory gas mixture 5. Through absorption, the absorbed substances accumulate in the activated carbon until it must be replaced or cleaned to restore its filtering properties. In preferred embodiments, at least one sensor 95 (not shown) can be arranged in or at the outlet 14-A. The sensor 95 is preferably arranged downstream of the filter 94 in the flow direction. The sensor 95 can, for example, be designed as an optical sensor and be configured to detect the anesthetic concentration of the discharged respiratory gas mixture 5 and / or transmit it to the control device 101. In this way, the filtering properties of the activated carbon filters can be determined.In one exemplary embodiment, a first filter 94i and a second filter 94ii can be arranged in or at the outlet 14-A. The first filter 94i and the second filter 94ii can form a double filter system with a magazine function, which can effectively prevent the escape of anesthetics. In a double filter system, for example, two activated carbon filters can be arranged one behind the other. Sensors 95 can be arranged upstream and / or downstream of a first filter 94i. Alternatively or additionally, sensors can also be arranged upstream and / or downstream of the second filter 94i. The sensors can then detect the respective anesthetic concentrations upstream and downstream of the filters. If the anesthetic gas concentration downstream of the first filter rises above a predefined limit, the second filter can continue to filter the breathing gas mixture.Such a dual filter system with a sensor offers the advantage that the first filter only needs to be replaced when it can demonstrably no longer filter anesthetics from the respiratory gas. The second filter still ensures effective filtration of the respiratory gas mixture. Costs for disposal and filter material can be saved. The evacuation system 14 can thus be configured and designed to dispose of the anesthetic gas in a controlled manner and / or to reprocess it for reuse. The device 100 is configured and designed to be able to conduct the respiratory gas mixture 5 in a closed circuit. This offers the advantage that the volatile anesthetics VA, which are usually harmful to the environment and climate, remain in the system and are not released into the environment in an uncontrolled manner.Furthermore, the device 100 according to the invention enables economical and thus cost-effective use of anesthetics, since unused anesthetics are not released into the environment but can be recycled. Since the exhaled air of the patient 90 remains in the breathing gas line 4 of the closed circuit, it is necessary to remove carbon dioxide (CO2) from the breathing gas mixture 5. Therefore, the device 100 has at least one separating agent 40, 60 for separating CO2 from the breathing gas mixture 5. In a first embodiment according to Figure 1, the device comprises the at least one separating agent 40. The separating agent 40 can be designed as a chemical CO2 absorber. The separating agent 40 can thus contain one or more chemically acting absorbents that bind CO2. The separating agent 40 is also referred to herein as chemical separating agent 40.The separating agent 60 is also referred to herein as a mechanical separating agent 60 (see below). Chemical absorbents can be selected from the group: calcium hydroxide, sodium hydroxide, potassium hydroxide, barium hydroxide. For example, a mixture of one or more of these components is used in the form of soda lime, through which the breathing gas mixture 5 is passed after expiration. During the chemical reaction between the chemical absorbents and CO2, the CO2 is bound and water (H2O) is formed. The reaction is exothermic, so temperatures between 60 and 70°C can develop. The chemical absorbents also partially bind anesthetics, so the anesthetic concentration should be monitored downstream of the separating agent 40 so that the anesthetic can be replenished as needed. The CO2 binding of the chemical separating agent 40 is very sensitive and active even at very low CO2 concentrations in the breathing gas mixture 5.Since water precipitates during the chemical absorption of CO2 in the chemical absorber, the breathing gas mixture 5 is enriched with H2O after it has passed through the chemical separating agent 40. For this reason, the device 100 can comprise a humidity control module 41. The humidity control module 41 is configured and designed to regulate the humidity of the breathing gas mixture 5. The humidity control module 41 can, for example, be configured as a cold trap and contain a water reservoir in which excess, precipitating water can be collected and disposed of. Optionally, the device 100 can comprise one or more humidity sensors (not shown). Humidity sensors are particularly advantageous when the device 100 is operated with a chemical separating agent 40.The humidity sensors can be configured and designed to determine the humidity of the respiratory gas mixture 5 and to provide feedback to the control device 101 and / or the humidity control module 41. The humidity sensors can preferably be arranged in the inspiratory branch 1 and determine the humidity in the inspiratory respiratory gas mixture 5. For introducing fresh gas and / or oxygen O2 and / or anesthetics, the device 100 can have at least one module 6, 8, 10. The modules 6, 8, 10 are each connected to the respiratory gas line 4 via at least one supply line 7, 9, 11. The supply lines can be pneumatically connected to the P580 respiratory gas line 4, wherein the supply lines can be permanently open or can be opened and / or closed in a controlled manner via valves. The modules 6, 8, 10 can serve as a pressure and / or volume source, and the respiratory gas line 4 can serve as a pressure and / or volume sink.The device 100 can comprise at least one fresh gas module 6 and at least one fresh gas supply line 7. Fresh gas can be added to the breathing gas mixture 5 via the fresh gas supply line 7. For this purpose, the fresh gas supply line 7 is pneumatically connected to the breathing gas line 4. The fresh gas can be introduced at at least one fresh gas feed point 207. Fresh gas, within the meaning of the invention, includes any fluid, breathing gas, and / or gas mixture that is suitable and can be used for breathing, ventilation, and / or respiratory therapy. Fresh gas can, for example, be supplied ambient air or a gas mixture of the ambient air and an additional gas, or an additional gas alone. The fresh gas can be supplied directly from the ambient air and / or obtained from compressed gas cylinders and / or from a central gas system (CGS) of the hospital. Fresh gas can also be oxygen or oxygen-enriched air.In some embodiments, the fresh gas can also contain at least one anesthetic gas. The fresh gas supply line 7 generally opens into the inspiratory branch 1 of the breathing gas line 4. The fresh gas can be introduced into the breathing gas line 4 upstream of the blower 3 or downstream of the blower 3. An oxygen-containing gas mixture and / or oxygen can be introduced into the breathing gas line 4 via the fresh gas module 6 in order to maintain or control the oxygen concentration of the breathing gas mixture 5. The breathing gas mixture 5 is conveyed in the breathing gas line 4 so that it can be supplied with fresh gas via the fresh gas module 6 and thus enriched with oxygen. The oxygen content of the breathing gas mixture 5 is controlled or regulated by the control device 101. The oxygen content of the breathing gas mixture 5 can be controlled or regulated automatically based on the detected sensor signals.The control or regulation of the oxygen content of the respiratory gas mixture 5 can also be carried out manually, in particular, by a user such as a medical professional. This allows the medical professional to supply fresh gas or oxygen to the patient during ventilation and / or anesthesia at any time as needed. The oxygen supply can be regulated such that the oxygen concentration of the respiratory gas mixture 5 is generally in a range between 10 and 60%, preferably between 20 and 50%. An oxygen saturation of 40 to 50% can generally be used for continuous ventilation and / or anesthesia. P580 In preferred embodiments according to the figures, the fresh gas is introduced into the respiratory gas mixture 5 upstream of the blower 3. The at least one fresh gas supply line 7 then opens into the respiratory gas line 4 upstream of the blower 3.In some embodiments, the fresh gas can be introduced into the breathing gas line 4 at more than one point, for example at least two points. For example, the device 100 can be configured such that the fresh gas module 6 can be connected to the breathing gas line 4 via at least two supply lines 7i, 7ii. In the specific embodiment according to Figure 1, the fresh gas supply line 7 can be divided into at least two fresh gas supply lines 7i, 7ii, namely, for example, a first fresh gas supply line 7i and a second fresh gas supply line 7ii. The first fresh gas supply line 7i and the second fresh gas supply line 7ii can be pneumatically connected to the breathing gas line 4. The first fresh gas supply line 7i and the second fresh gas supply line 7ii can preferably open into the breathing gas line 4 at different points.In some embodiments, the fresh gas supply lines 7i, 7ii can each introduce fresh gas into the breathing gas line simultaneously (not shown). In preferred embodiments, the fresh gas supply lines 7, 7i, 7ii can be controlled via at least one fresh gas switching valve 32 such that only one of the fresh gas supply lines 7i or 7ii can introduce fresh gas into the breathing gas line at a time. The fresh gas switching valves 32 can be used to control which of the fresh gas supply lines 7, 7i, 7ii fresh gas is introduced into the breathing gas line 4. The fresh gas switching valves 32 can thus be used to control the location of the fresh gas feed into the breathing gas line 4. The fresh gas switching valves 32 can be switched electronically and / or mechanically. The fresh gas switching valves 32 can be switched automatically by the control device 101 and / or manually by the user.The fresh gas switching valve 32 can be designed as a monostable or bistable directional control valve. In preferred embodiments, the fresh gas switching valve 32 is designed as a monostable directional control valve. For example, the fresh gas switching valve 32 comprises a solenoid coil and a spring, the interaction of which can be used to switch the valve. Energizing the solenoid coil actively directs the valve 32 to a first switching position. When de-energized, the solenoid coil is inactive, so that the spring relaxes and moves the valve to the second switching position. When de-energized, the valve 32 is in its basic position. Figure 1 shows that fresh gas is introduced via the first fresh gas supply line 7i when the valve 32 is in its basic position, i.e., de-energized. The second fresh gas supply line 7ii is operated when the valve 32 is energized.In the exemplary embodiment according to Figure 1, the fresh gas module 6 is connected to the fresh gas supply line 7. The fresh gas supply line 7 is connected to the fresh gas switching valve 32. The fresh gas switching valve 32 can, for example, be designed as a 2 / 3-way valve and thus have three P580 connections and two switching positions. The fresh gas switching valve 32 can then also be connected to the first fresh gas supply line 7i and to the second fresh gas supply line 7ii and, depending on the switching position, supply either the first fresh gas supply line 7i or the second fresh gas supply line 7ii with fresh gas from the fresh gas module 6. In the exemplary embodiment according to Figure 1, the first fresh gas supply line 7i and the second fresh gas supply line 7ii open into the breathing gas line 4 at different locations. Thus, the device 100 can be configured to regulate the location of the fresh gas introduction into the breathing gas line 4.For example, the first fresh gas supply line 7i can open into the breathing gas line 4 upstream of the first check valve 21 in the flow direction. For example, the second fresh gas supply line 7ii can open into the breathing gas line 4 downstream of the first check valve 21 in the flow direction. For example, the second fresh gas supply line 7ii can open into the breathing gas line 4, in particular, between the first check valve 21 and the evaporation element 8a (Figure 1). In alternative embodiments, it is also conceivable for the device 100 to comprise at least two 2 / 2-way fresh gas directional valves instead of the one 2 / 3-way fresh gas directional valve 32. For example, the first fresh gas supply line 7i can comprise a first fresh gas directional valve, which can be designed as a 2 / 2-way valve with two connections and two switching positions.For example, the second fresh gas supply line 7ii can comprise a second fresh gas directional control valve, which can also be designed as a 2 / 2-way valve with two connections and two switching positions (not shown). The 2 / 2-way valves can then be connected in parallel by the control device 101 such that either the first fresh gas supply line 7i or the second fresh gas supply line 7ii can be opened to introduce fresh gas into the breathing gas mixture 5. Alternatively or additionally, the device 100 can comprise at least one oxygen module 10. The oxygen module 10 can be designed as an O2 flush 10 and comprise at least one O2 flush supply line 11. Oxygen O2 or an oxygen-containing gas mixture can be introduced into the breathing gas line 4 via the O2 flush supply line 11. The O2 flush supply line 11 is pneumatically connected to the breathing gas line 4 for this purpose.The oxygen can be introduced at at least one O2 flush feed point 211. The oxygen can be drawn from compressed gas cylinders and / or from a central gas system (CGS) of the hospital. Preferably, the device 100 is connected to the central gas system (CGS) and additionally has connections to at least one compressed gas cylinder. Thus, the oxygen can be drawn either from the central gas system (CGS) or from compressed gas cylinders. As a result, in the event of a failure of the central gas supply, the oxygen supply via the compressed gas cylinders can be guaranteed at least for a certain period of time. The O2 flush 10 can be designed and configured so that a user, for example, medical personnel, can quickly fill the breathing gas line 4 (the circuit part) and / or the reservoir 12 with oxygen.The O2 flush 10 can be used to: P580 - refill the breathing gas line 4 and / or the reservoir 12 that has run dry after a leak - wash out anesthetics from the patient's lungs - ventilate the patient with pure oxygen for a certain period of time In particular, the O2 flush of the oxygen module 10 is designed and configured to quickly flood the breathing gas line 4 and / or the reservoir 12 and / or the patient's lungs with oxygen in emergency situations. The flow rate of the oxygen or the oxygen-containing gas mixture can be 60 l / min, for example. The flow rate is advantageously particularly high so that the breathing gas line 4 and / or the reservoir 12 can be quickly refilled after a leak and / or the anesthetic can be quickly flushed out.A leak in the breathing gas line 4 and / or the reservoir 12 can occur intentionally or unintentionally, for example after a hose change, a filter change, a sensor replacement, or improper use of the hose system 92 or the patient interface 91. In such cases, the loss of breathing gas mixture 5 in the breathing gas line 4 and / or the reservoir 12 cannot be replenished quickly enough with the normal fresh gas flow. The O2 flush then offers a quick way to refill the breathing gas line 4 and / or the reservoir 12 with a breathable gas. Furthermore, patients can be ventilated with undiluted oxygen via the O2 flush, as needed, at least for a short time, for example for a few breaths. The O2 flush can supply the patient with at least 90% oxygen, preferably with at least 93% oxygen.The oxygen flush of the oxygen module 10 allows undiluted oxygen to be fed into the breathing gas line 4, just as it comes from the supply (namely, the central gas system or the compressed gas cylinder). The oxygen introduction via the O2 flush 10 can be regulated such that the oxygen concentration of the breathing gas mixture 5 is up to 100%, at least for a defined, short period of time. Ventilation with up to 100% oxygen for a short period of time may be necessary during an operation. For example, a patient is briefly ventilated with up to 100% oxygen during the induction of anesthesia. The oxygen introduction via the O2 flush 10 can also be regulated such that the oxygen concentration of the breathing gas mixture 5 is, for example, at least 60%, at least for a defined, short period of time.An oxygen saturation of 60% or more, preferably 80% or more, and particularly preferably at least 90% can be used to flush out anesthetics. During surgery, it may happen that the anesthetics must be quickly removed from the patient's body, for example in the event of an allergic reaction to the anesthetic, e.g., in the event of malignant hyperthermia. The rapid removal of anesthetics from the patient's lungs can be achieved by flooding with pure or highly concentrated oxygen. Such oxygen flooding of the patient's lungs can quickly reduce the anesthetic concentration. P580 The O2 flush supply line 11 can open into the inspiratory branch 1 of the breathing gas line 4. The oxygen can be introduced upstream of the blower 3 or downstream of the blower 3.In preferred embodiments according to the figures, the oxygen can be introduced into the breathing gas mixture 5 downstream of the blower 3. The O2 flush supply line 11 then opens into the breathing gas line 4 downstream of the blower 3. This offers the advantage that the oxygen-enriched breathing gas mixture 5 is not passed through the blower 3, which offers increased safety. An excessively high oxygen concentration in the blower 3 can lead to complications such as a short circuit, fire, or damage to individual components of the blower 3. In some embodiments, multiple O2 flush supply lines 11 can be included, which can open into the breathing gas line 4 at different points. In some embodiments, oxygen can be introduced into the breathing gas line 4 via the O2 flush 10 at more than one point, for example at at least two points.For example, the device 100 can be configured such that the O2 flush 10 can be connected to the breathing gas line 4 via at least two O2 flush supply lines 11i, 11ii. In preferred embodiments according to the figures, the O2 flush can be introduced into the breathing gas mixture 5 upstream of the blower 3 and / or downstream of the blower 3. The at least one O2 flush supply line 11 then opens into the breathing gas line 4 upstream of the blower 3 and / or downstream of the blower 3. In some embodiments, the oxygen of the O2 flush 10 can be introduced into the breathing gas line 4 at more than one point, for example at at least two points. For example, the device 100 can be configured such that the O2 flush 10 can be connected to the breathing gas line 4 via at least two O2 flush supply lines 11i, 11ii.In the specific embodiment according to Figure 1, the O2 flush supply line 11 can be divided into at least two O2 flush supply lines 11i, 11ii, namely, for example, a first O2 flush supply line 11i and a second O2 flush supply line 11ii. The first O2 flush supply line 11i and the second O2 flush supply line 11ii can be pneumatically connected to the breathing gas line 4. The first O2 flush supply line 11i and the second O2 flush supply line 11ii can preferably open into the breathing gas line 4 at different points. In some embodiments, the O2 flush supply lines 11i, 11ii can each introduce oxygen into the breathing gas line 4 simultaneously (not shown). In preferred embodiments, the O2 flush supply lines 11, 11i, 11ii can be controlled via at least one O2 flush switching valve 31 such that only one of the O2 flush supply lines 11i or 11ii can introduce oxygen into the breathing gas line 4.The O2 flush switching valves 31 can be used to regulate which of the O2 flush supply lines 11, 11i, 11ii oxygen is introduced into the breathing gas line 4. The O2 flush switching valves 31 can thus be used to regulate the location of the oxygen feed into the breathing gas line 4. P580 The O2 flush switching valve 31 can be designed as a monostable or bistable directional control valve. In preferred embodiments, the O2 flush switching valve 31, like the fresh gas switching valve 32, is designed as a monostable directional control valve with a solenoid coil and spring. Energizing the solenoid coil actively moves the valve 31 to a first switching position. When de-energized, the solenoid coil is inactive, so that the spring relaxes and brings the valve to the second switching position. When de-energized, the valve 31 is in its basic position. The O2 flush switching valves 31 can be switched electronically and / or mechanically.The O2 flush switching valves 31 can be switched automatically by the control device 101 and / or manually by the user. In particular, the O2 flush switching valves 31 can be switched manually, so that a user (medical personnel) can supply oxygen as needed and can also determine the feed location in the breathing gas line 4. Figure 1 shows that oxygen is introduced via the first O2 flush supply line 11i when the valve 31 is in its basic position, i.e., de-energized. The second O2 flush supply line 11ii is operated when the valve 32 is energized. In the exemplary embodiment according to Figure 1, the O2 flush 10 is connected to the O2 flush supply line 11. The O2 flush supply line 11 is connected to the O2 flush switching valve 31. The O2 flush switching valve 31 can, for example, be designed as a 2 / 3 way valve and thus have three connections and two switching positions.The O2 flush switching valve 31 can then also be connected to the first O2 flush supply line 11i as well as to the second O2 flush supply line 11ii and, depending on the switching position, supply either the first O2 flush supply line 11i or the second O2 flush supply line 11ii with oxygen from the O2 flush 10. In the exemplary embodiment according to Figure 1, the first O2 flush supply line 11i and the second O2 flush supply line 11ii open into the breathing gas line 4 at different locations. Thus, the device 100 can be configured to regulate the location of the oxygen introduction into the breathing gas line 4. For example, the first O2 flush supply line 11i can open into the breathing gas line 4 downstream of the blower 3 in the flow direction. In some embodiments, it may be particularly advantageous if the O2 flush supply line 11 opens into the breathing gas line 4 as close to the patient as possible.For example, the second O2 flush supply line 11ii can open into the breathing gas line 4 upstream of the blower 3 in the flow direction. For example, the second O2 flush supply line 11ii can open into the breathing gas line 4 upstream of the first check valve 21 in the flow direction (Figure 1). In alternative embodiments, it is also conceivable for the device 100 to comprise at least two 2 / 2-way valves 31 (not shown) instead of the one 2 / 3-way valve 31. For example, the first O2 flush supply line 11i can comprise a first O2 flush switching valve, which can be designed as a 2 / 2-way valve with two ports and two switching positions. For example, the second O2 flush supply line 11ii can comprise a second O2 flush switching valve, which can also be designed as a 2 / 2-way valve with two ports and two switching positions.P580 The two 2 / 2-way valves can then be connected in parallel by the control device 101 such that either the first O2 flush supply line 11i or the second O2 flush supply line 11ii can be opened in order to introduce oxygen from the O2 flush into the breathing gas mixture 5. The device 100 can optionally comprise a separate nitric oxide module 43 and at least one nitric oxide supply line 44 (not shown). Nitric oxides, for example nitrous oxide N2O, can be used, for example, to intensify anesthesia and / or alleviate pain. Nitrous oxide N2O can thus be administered in addition to the at least one volatile anesthetic. The nitric oxide module 43 can be set up and arranged in the device in parallel and equivalent to the fresh gas module 6 and / or the oxygen module 10. The nitric oxide module 43 can have a separate nitric oxide supply line 44.In some embodiments, the nitric oxide (laughing gas) can also be introduced into the breathing gas line 4 together with the fresh gas and / or the other anesthetics. The nitric oxide supply line 44 can have an additional safety valve to monitor the nitric oxide concentration. In the event of a failure of the oxygen module 10 and / or the fresh gas module 6, the additional safety valve can quickly and reliably shut off the nitric oxide supply. The supply lines, in particular the fresh gas supply line 7, the O2 flush supply line 11, and the nitric oxide supply line 44, can each comprise at least one element to ensure the functionality and safety of the supply lines 7, 11, 44. The elements can be comprised singly or multiple times and can vary in their arrangement. The supply lines 7, 11, 44 can be identically constructed or can vary from one another.In particular, the fresh gas supply lines 7, the O2 flush supply lines 11, and the nitrogen oxide supply lines 44 can, in principle, be constructed almost identically. Figure 2 schematically shows an exemplary structure of the supply lines 7, 11, 44, 71. The oxygen and / or the oxygen-containing gas mixture and / or the fresh gas and / or the nitrogen oxide can each be obtained from at least one supply source 89. For safety reasons, at least two supply sources 89 are preferably included. For example, the oxygen and / or the oxygen-containing gas mixture and / or the fresh gas and / or the nitrogen oxide can each be obtained from at least one compressed gas cylinder 89 and / or from a gas system, for example a central gas system (CGS) of a hospital, and can each be introduced into the breathing gas line 4 via the supply lines 7, 11, 44.In advantageous embodiments, fresh gas, oxygen, and nitrogen oxide can be obtained both from a ZGA and from pressurized cylinders 89. In this case, the device 100 comprises at least two supply lines 7, 11, 44. Thus, oxygen can be fed into the breathing gas path 4 via a first supply line 11 from a ZGA and optionally via a second supply line 11 from a pressurized gas cylinder 89. Correspondingly, fresh gas can be fed into the breathing gas path 4 via a first supply line 7 from a ZGA and optionally via a second supply line 7 from a pressurized gas cylinder 89. Correspondingly, nitrogen can be fed into the breathing gas path 4 via a first supply line 44 from a ZGA and optionally via a second supply line 44 from a pressurized gas cylinder 89. In this case, the control device 101 can control the supply lines 7, 11, 44 such that the respective P580 feed from the ZGA is prioritized.A gas feed from the compressed gas cylinders 89 is only activated when the ZGA fails or is no longer to be or can no longer be used for other reasons. The compressed gas cylinders 89 can thus be used, for example, as a reserve for an emergency situation. The arrangement of several compressed gas cylinders 89 is also conceivable. At least one filter 82 can be arranged in each of the supply lines 7, 11, 44. The filters 82 are designed and constructed to filter out possible solid particles from the introduced fluid. The filters 82 are configured as an optional safety element. The filters 82 can preferably be arranged downstream directly after the supply sources 89. Optionally and additionally, water separators and / or oil separators can also be arranged in or on the supply lines 7, 11, 44 (not shown). At least one sensor 84, 85 can be arranged in or on the supply lines 7, 11, 44.The sensors 84, 85 can be configured and designed to detect or monitor the pressure and / or volume and / or flow in the supply lines 7, 11, 44. For example, at least one pressure sensor 84 can be arranged in each of the supply lines 7, 11, 44. The pressure sensors 84 can detect how much pressure and / or volume is drawn from the compressed gas cylinders 89. The fill level of the compressed gas cylinders 89 can be monitored via the pressure sensors 84 and transmitted to the control device 101. If the fill level falls below a critical level, an alarm can be triggered. For this purpose, the device can comprise an alarm device controlled by the control device 101 (not shown). The pressure sensors 84 can preferably be arranged downstream directly after the compressed gas cylinders 89 and the filter 82. For example, at least one flow sensor 85 can be arranged in each of the supply lines 7, 11, 44.The flow sensors 85 can detect the gas flow in the supply lines 7, 11, 44. The flow in the supply lines 7, 11, 44 can be monitored via the flow sensors 85 and transmitted to the control device 101. The flow sensors 85 can preferably be arranged downstream directly before the confluence with the breathing gas line 4. Fine flow control can be achieved with the help of the flow sensors 85. At least one pressure regulator 80 and / or one stenosis 81 can be arranged in or on the supply lines 7, 11, 44. The pressure regulator 80 can be designed as a pressure reducer 80. The pressure reducer 80 and / or the stenosis 81 can be configured to regulate the pressure from the supply sources 89 such that the pressure is reliably below the lowest specified supply pressure. The supply pressures of the central gas supplies and the compressed gas cylinders can vary greatly.However, the metering valves for the gases require a constant supply pressure, as their characteristic curve depends on it. Therefore, the pressure regulators 80 and / or the stenoses 81 regulate the pressures to a value that is safely below the lowest specified supply pressure. This allows the metering valves to always operate consistently. Pressures of up to approximately 20 MPa can exist in the compressed gas cylinders 89. The pressure reducers 80 and / or the stenoses 81 are configured and designed to regulate the pressure from the compressed gas cylinders 89 to at least half, preferably at least a quarter, particularly preferably at least a tenth P580 of the pressure originally prevailing in the compressed gas cylinders 89. For example, the pressure reducers 80 and / or the stenoses 81 are configured and designed to regulate the pressure from approximately 20 MPa, preferably to typically 450 + / - 50 kPa.The pressure reducers 80 and / or the stenoses 81 can be configured and designed to adjust the pressure such that it is lower than the smallest operating pressure of the device 100. At least one valve 83, 86, 87, 88, 31, 32 can be arranged in or on the supply lines 7, 11, 44. The supply lines 7, 11, 44 preferably each comprise at least one pressure relief valve 83, preferably at least two pressure relief valves 83. The pressure relief valves 83 can be configured and designed as opening pressure valves to divert the corresponding gas from the supply line 7, 11, 44 if the pressure in the supply lines 7, 11, 44 is too high. A first pressure relief valve 83 can be arranged downstream of the pressure regulator 80 and / or the stenosis 81. The first pressure relief valve 83 can be configured and designed to release pressure.This offers special protection in the event that the pressure regulator 80 fails and excessive pressure from the supply source 89 prevails in the supply lines 7, 11, 44. In some embodiments, at least one second pressure relief valve 83 can be arranged in the supply lines 7, 11, 44. For example, the second pressure relief valve 83 can be arranged upstream directly before the introduction into the breathing gas line 4. The pressure relief valves 83 offer the advantage of additional protection. Excess gas can be discharged into the environment. In some embodiments, the excess gas can also be specifically discharged and reused (not shown). Pressure relief valves 83 and stenosis 81 are designed and configured to limit the maximum flows. In particular, pressure relief valve 83 and stenosis 81 can limit the maximum flows in the event of a fault.In the event of a defect in the pressure regulator 80, i.e., in the event that the pressure regulator 80 allows all gas from the supply sources 89 to pass through, the pressure relief valve 83 can divert the excess gas. If the pressure regulator 80 fails, the stenoses 81 can be configured to limit the maximum flow such that the pressure relief valve 83 is protected and the pressure relief valve 83 can divert the flow. In addition, the supply lines 7, 11, 44 preferably each comprise at least one check valve 86. In some embodiments, the check valve 86 can be designed as a simple check valve. In preferred embodiments, the check valve is designed as a spring-loaded check valve 86. The check valve 86 is configured to control the flow direction in the supply lines 7, 11, 44 and, in particular, to prevent backflow of the gas into the supply sources 89.The check valve 86 ensures that the supply sources 89 are not contaminated with the breathing gas mixture 5 from the breathing gas line 4. The supply lines 7, 11, 44, 71 can also each comprise at least one switching valve 87, 31, 32 and / or at least one metering valve 88, 88i. In preferred embodiments, the switching valves 87, 31, 32 and / or the metering valves 88, 88i can be designed as bistable valves. The metering valves 88, 88i can be designed, for example, as needle valves. P580 The bistable switching valves 87 and / or metering valves 88 are preferably arranged upstream of the junction with the breathing gas line 4 and are configured to control the supply line and / or the supply quantity into the breathing gas line 4. For example, the bistable switching valves 87 and / or metering valves 88 can control the flow and / or volume and / or pressure introduced into the breathing gas line 4.In some embodiments, the flow can be controlled in particular via the bistable switching valves 87 and / or metering valves 88. For example, at least one switching valve 87 can be arranged in each of the supply lines 7, 11, 44. The at least one switching valve 87 in each of the supply lines 7, 11, 44 can, for example, be designed as a bistable valve. For example, at least one bistable switching valve 87 can be arranged in the fresh gas supply lines 7. In addition, at least one bistable switching valve 87 can be arranged in the nitrogen oxide supply lines 44. In addition, at least one bistable switching valve 87 can be arranged in the O2 flush supply lines 11. Preferably, all supply lines 7, 11, 44 have at least one bistable switching valve 87. The bistable switching valves 87 can each be arranged upstream directly after the check valves 86.The bistable switching valves 87 can preferably be switched in an open position or a closed position. An open position allows unrestricted gas flow. A closed position can hermetically seal the supply line and prevent gas flow in the supply line. Preferably, the bistable switching valves 87 can be adjusted from an open position to a closed position. The position of the bistable switching valves 87 can be controlled by the control device 101. The position of the switching valves 87 can be used to regulate which of the lines 7, 11, 44 is open and which is closed. Thus, the position of the switching valves 87 can be used to regulate the supply sources from which gas is fed into the breathing gas line 4.For example, the position of the switching valves 87 can be used to regulate whether the respective gas is introduced into the breathing gas line 4 from the central ventilation system (ZGA) or from the compressed gas cylinders, or not at all. The bistable switching valves 87 can be configured so that power is required to switch between an open and a closed state and vice versa. The switching energy can be selected to be very low. The bistable switching valves 87 then remain open or closed without the need for additional energy. The bistable switching valves 87 can therefore remain in the predetermined position without power. This offers the advantage that in an emergency situation, such as a power failure or low power availability, a software crash, or another technical error, the last selected functions and settings are retained and ventilation is still possible.The bistable switching valves 87 can also be configured to allow manual switching. This allows medical personnel to act in an emergency situation. To ensure patient safety, the device 100 offers the option of manual ventilation. In the event of a power and / or software failure, the device 100 switches, without any action from the P580 user, to a state that allows the user to provide emergency ventilation to the patient using manual ventilation. Pressure changes must be possible. The fresh gas must continue to flow, and the CO2 must be absorbed and / or diffused away. For this reason, all valves in the oxygen module 10 and / or fresh gas module 6 remain in their last switching position in the event of a power or software failure. In some embodiments, the bistable switching valves 87 can also be configured and designed such that the closed position is only maintained with the expenditure of energy.Thus, gas can only be introduced into the breathing gas line 4 when the bistable switching valves 87 are de-energized. This offers the advantage that the gas introduction into the breathing gas line 4 is guaranteed in an emergency situation, for example in the event of a power failure. This can ensure that the oxygen and / or fresh gas supply can be maintained. Furthermore, it can be ensured that the anesthetic gas supply can be maintained and the anesthesia is maintained. In some embodiments, the bistable switching valves 87 can also be configured and designed such that the open position is only maintained with the expenditure of energy. Thus, gas can only be introduced into the breathing gas line 4 when the bistable switching valves 87 are supplied with power.This can offer the advantage that the gas feed into the breathing gas line 4 is interrupted in an emergency situation, for example in the event of a power failure, and manual ventilation, for example ventilation with a hand bag, is enabled. Alternatively or additionally, at least one metering valve 88, 88i can be arranged in each of the supply lines 7, 11, 44, 71. The at least one metering valve 88, 88i in each of the supply lines 7, 11, 44, 71 can be designed, for example, as a needle valve 88, 88i. In alternative embodiments, the metering valve 88 can also be designed as a proportional valve. In some embodiments, metering can also be achieved via the arrangement of several switching valves with different orifices, so that the flow can be adjusted using different orifice sizes / powers. In preferred embodiments, however, the metering valve 88 is designed as a needle valve.Needle valves offer the advantage that an almost infinite number of switching positions can be realized. Very precise dosing is possible using needle valves. Needle valves offer the advantage of a very large control range, in which both very small flow rates and very large flow rates can be precisely adjusted. For example, at least one needle valve 88 can be arranged in the fresh gas supply lines 7. In addition, at least one needle valve 88 can be arranged in the nitrogen oxide supply lines 44. In addition, at least one needle valve 88 can be arranged in the O2 flush supply lines 11. Preferably, all supply lines 7, 11, 44 each have at least one needle valve 88. Needle valves 88 offer the advantage of enabling very fine pressure control at small flows. At the same time, needle valves 88 can permit very large flows.The needle valves 88 can be configured and designed such that the flow can be set to very low (0-30 l / min) or very high (80-120 l / min), as well as to any intermediate level. Thus, the device is suitable both for ventilation under anesthesia, where smaller flows are required, and for ventilation with large flows, for example, high-flow ventilation. For the same reason, the device 100 is particularly suitable both for the ventilation / anesthesia of adults, who require larger flows, and for the ventilation / anesthesia of children, infants, newborns, and premature babies, who require smaller flows. The needle valves 88 can be configured and designed such that a flow of 0 to 100 l / min is introduced into the breathing gas line 4. Preferably, a flow of 0 to 60 l / min is introduced into the breathing gas line 4.The device 100 can be operated in different operating modes, for which different flow rates can be set. The flow rate is generally set automatically via the control device 101. The flow rate can be set, for example, via the settings of the needle valves 88 in the supply lines 7, 11, 44. The needle valves 88 can be set up and designed such that a flow of 0 to 120 l / min can be generated. In a specific exemplary embodiment, the needle valves 88 can be set up and designed such that a flow of 0 to 60 l / min can be generated. In an operating mode for high-flow ventilation, a flow of up to 120 l / min can be generated, for example up to 100 l / min.For high-flow therapy, the flow can be passed through the deactivated blower 3 so that the flow can only be generated through the oxygen module 10 and / or the O2 flush supply line 11. In a working mode for total intravenous anesthesia, a flow of less than 60 l / min can be generated, for example less than 30 l / min, preferably less than 20 l / min. For example, in a working mode for total intravenous anesthesia, a flow of 18 l / min is generated. In an anesthesia mode with volatile anesthetics VA, a flow of less than 60 l / min can be generated, for example less than 30 l / min, preferably less than 20 l / min. For example, in an anesthesia mode with volatile anesthetics VA, a flow of 18 l / min is generated. In a working mode for CPAP ventilation, a flow of less than 60 l / min can be generated, for example, less than 30 l / min, preferably less than 20 l / min. For example, in a CPAP mode, a flow of 15 l / min is generated.In some embodiments, the needle valves 88 can be designed as bistable needle valves with stepper motors. This allows the needle valves 88 to function as metering valves. A combination of the needle valves with stepper motors offers the advantage that very small and very large flows can be metered. Needle valves with stepper motors have very good resolution even at very small flows. The bistable needle valves 88 with stepper motors can be configured and designed such that they remain in the last set position without power supply. This offers the P580 device 100 a special safety function in the event of a power failure, since the fresh gas and / or oxygen and / or nitrogen oxide supply can then continue. It is advantageous if the device 100 has at least one accumulator.The needle valves 88 can then be adjusted using the energy from the accumulators in the event of a power failure. The needle valves 88 can also be configured and designed such that manual adjustment is possible in the event of a power failure. This allows medical personnel to act even in emergency situations. The supply lines 7, 11, 44 can also each comprise at least the switching valve 31, 32, which were already described above in relation to Figure 1. The switching valves 31, 32 are preferably arranged directly before the supply line joins the breathing gas line 4. The switching valves 31, 32 control the point in the breathing gas line 4 at which the corresponding gas is introduced. The switching valves 31, 32 are configured and designed to regulate the feed point of the gases (fresh gas, oxygen). The device 100 can optionally comprise at least one anesthetic module 8 and at least one anesthetic supply line 9.The anesthetic module 8 is configured and designed to provide anesthetics to the system via the anesthetic supply line 9. The anesthetic module 8 can be controlled via the control device 101. The device 100 can be used for inhalation anesthesia or inhalation anesthesia. Volatile anesthetics (VA) can be used for inhalation anesthesia or inhalation anesthesia. For example, the volatile anesthetics (VA) can be selected from the group: isoflurane, sevoflurane, desflurane, halothane, enflurane, and methoxyflurane. Particularly preferred volatile anesthetics (VA) are selected from the group: isoflurane, sevoflurane, desflurane, and halothane. For inhalation anesthesia or inhalation anesthesia, gaseous anesthetics such as xenon, argon or nitrous oxide N2O (laughing gas) can be used alternatively or additionally.Nitrous oxide in particular can be added to breathing gas mixture 5 in some applications to support or positively influence the action of the volatile anaesthetics VA. The volatile anaesthetics VA are used to create optimal conditions for the patient with regard to at least the following parameters: - unconsciousness (patient is asleep / hypnosis) - freedom from pain / perception of pain (analgesia) - reduction of muscle tension - dampening of vegetative reflexes and defensive reflexes The volatile anaesthetics VA have low molecular weight and have a high vapor pressure and a relatively low boiling point. P580 Overview of volatile anaesthetics VA Name Structure Molar Boiling Vapor pressure MAC - MAC - Setting range Mass point (ambient 20°C) Awake Immobile on introduction [g] [°C] [%] [%] max.[%] Isoflurane CF3-CHCl-O-CHF2 185 48.5 313 ​​hPa (31.3%) 0.43 1.28 5 Sevoflurane CH-CF3-CF3-O-CH2F 200 58.6 207 hPa (20.7%) 0.63 2.05 8 Desflurane CF3-CHF-O-CHF2 168 22.8 873 hPa (87.3%) 2.40 6.00 18 Halothane CF3-CHBrCl 197 50.2 242 hPa (24.2%) 0.52 0.75 5 Enflurane CHF2-O-CF2-CHFCl 184 56.5 233 hPa (23.3%) - 1.58 5 Methoxyflurane CH3-O-CF2-CHCl2 165 104.7 26 hPa (2.6%) - 0.2 4 MAC = Minimum Alveole Concentration 1 MAC = 50% of patients are ideally anesthetized In some embodiments, the anesthetics can be introduced in gaseous form into the breathing gas line 4 (not shown). For gaseous introduction, the anesthetics VA or the gaseous anesthetics can be mixed with fresh gas beforehand. For this purpose, the device 100 can have a mixing chamber (not shown). The gaseous anesthetics mixed with fresh gas can then be fed via the anesthetic supply line 9 into the breathing gas line 4, where they mix with the breathing gas mixture 5.In preferred embodiments, the volatile anesthetics VA are introduced into the breathing gas line 4 via a liquid metering device. For this purpose, the device 100 can have at least one evaporation element 8a. The evaporation element 8a can be arranged in or on the breathing gas line 4. The evaporation element 8a can be formed as an integral component of the breathing gas line 4. The volatile anesthetics VA can then be fed into the evaporation element 8a of the breathing gas line 4 via the anesthetic module 8 and the anesthetic supply line 9. For this purpose, the anesthetic module 8 is pneumatically connected to the evaporation element 8a of the breathing gas line 4 via the anesthetic supply line 9. In the evaporation element 8a, the liquid volatile anesthetics VA can evaporate and combine with the breathing gas mixture 5.Liquid dosing of the volatile anesthetics VA can be achieved by cooling and / or pressurizing the anesthetics VA in a tank. In preferred embodiments, a first pressure P1 is present in the breathing gas line 4 and a second pressure P2 is present at least in the anesthetic supply line 9, wherein the first pressure P1 is lower than the second pressure P2. The second pressure P2 is, for example, at least 100 kPa. In preferred embodiments, the second pressure P2 can be at least 180 kPa. Thus, the volatile anesthetics VA can be introduced in liquid form into the evaporation element 8a via the anesthetic module 8 and the anesthetic supply line 9. Only there can the anesthetics VA evaporate and combine with the breathing gas mixture 5. P580 The concentration of anesthetic VA is generally selected such that the anesthetic concentration in the breathing gas mixture 5 is, for example, in a range between 0 and 25%.The device 100 is configured such that a user, for example, medical personnel such as the anesthesiologist, can adjust the concentration of the anesthetics VA very precisely and variably. Depending on the anesthetic used and the patient and / or type of surgery, the anesthesiologist can adjust the concentration of the anesthetics and adapt it to the conditions during the surgery. For sedation of the patient 90, the concentration of the individual volatile anesthetics VA in the breathing gas mixture 5 is typically selected as follows: Isoflurane 0 to 5%; Halothane 0 to 5%; Sevoflurane 0 to 8%; Desflurane 0 to 18%. The volatile anesthetics VA are generally not used together. Higher concentrations are possible and are at the discretion of the user, i.e., in particular, at the discretion of the anesthesiologist. The device 100 is configured and designed to allow the adjustment of all concentrations.The liquid dosing of volatile anesthetics offers the following advantages over gas dosing using a prior mixture with fresh gas: - More precise and therefore more economical dosing of anesthetics is possible - The supply of anesthetics is independent of the supply of fresh gas or oxygen - The anesthetic concentration is independent of the fresh gas concentration and / or the oxygen concentration - The pressure from anesthetic compressed gas cylinders can supply the energy for the anesthetics The anesthetic supply line 9 can lead into the evaporation element 8a. In the evaporation element 8a, the state of aggregation of the volatile anesthetics VA changes. Upon entering the evaporation element 8a of the breathing gas line 4, the volatile anesthetics VA are exposed to the pressure P1 of the breathing gas line 4 and thus become gaseous. The evaporation element 8a can be arranged in the inspiratory branch 1 of the breathing gas line 4.Thus, the anesthetics VA can be introduced into the inspiratory branch 1 of the respiratory gas line 4. The evaporation element 8a can be arranged upstream of the blower 3 or downstream of the blower 3. In preferred embodiments according to the figures, the evaporation element 8a can be arranged upstream of the blower 3. The evaporation element 8a can preferably be arranged downstream of the fresh gas supply lines 7i, 7ii. In the specific embodiments according to the figures, the evaporation element 8a is arranged between the confluence of the first fresh gas supply line 7i with the respiratory gas line 4 and the blower 3. The device 100 is advantageously configured such that at least one permanent flow, the byflow, is formed in the respiratory gas line 4. The byflow ensures that the breathing gas mixture 5 in the breathing gas line 4 is always in motion.In the evaporation element 8a, the byflow has a positive effect on the evaporation rate of the volatile anesthetics VA. P580 The byflow in the evaporation element 8a can be generated and maintained by the reservoir 12 and / or by the blower 3 and / or by the fresh gas module 6 and / or by the oxygen module 10. The byflow in the evaporation element 8a allows the liquid volatile anesthetics VA to evaporate and mix optimally with the respiratory gas mixture 5. Figure 3 schematically shows a section of the respiratory gas line 4, in which the evaporation element 8a is arranged, which is connected to the anesthetic module 8 via the anesthetic supply line 9. From Figure 3, it can be seen that the evaporation element 8a can be arranged in the breathing gas line 4 between the first check valve 21 and the blower 3. The evaporation element 8a can preferably be arranged upstream directly in front of the blower 3.The evaporation element 8a can preferably be arranged downstream of the fresh gas feed point 207 of the first fresh gas supply line 7i. The evaporation element 8a can preferably be arranged downstream of the first check valve 21. The check valve 21 can then prevent the respiratory gas mixture 5 conveyed in the respiratory gas line 4 from flowing against the main flow direction S. The anesthetic module 8 can be connected to the evaporation element 8a via the anesthetic supply line 9. An anesthetic feed 209 can be introduced into the respiratory gas mixture 5 via the evaporation element 8a. Different volatile anesthetics VA can be supplied to the respiratory gas mixture 5 via the anesthetic module 8. As a rule, only one anesthetic is added to the patient at a time. Using the anesthetic module 8, it is also possible to change the anesthetic during the operation.At least one volatile anesthetic VA can be introduced in liquid form into the evaporation element 8a via the anesthetic module 8. In the evaporation element 8a, the volatile anesthetic VA can evaporate and mix with the respiratory gas mixture 5. To provide the volatile anesthetic VA in liquid form, the anesthetic module 8 and the anesthetic supply line 9 can be cooled and / or kept under pressure. Preferably, the anesthetic module 8 and the anesthetic supply line 9 are kept under the second pressure P2. The pressure P2 is preferably at least 180 kPa. At this pressure, the volatile anesthetic VA is in the liquid state as long as the temperature is below 40°C. Preferred volatile anesthetics VA are, for example, selected from the group: isoflurane, sevoflurane, desflurane, and halothane.The anesthetic module 8 can comprise at least one of the following units: pressure supply unit 810, receiving unit 820, selection unit 830, dosing unit 840, safety unit 850, temperature unit 860. The anesthetic module 8 is to be understood as a pneumatic unit. All units of the module 8 are pneumatically connected to one another (directly or indirectly). The connection can be established via the at least one anesthetic supply line 9. The anesthetic module 8 and the anesthetic supply line 9 are preferably under pressure P2 in order to keep the volatile anesthetic VA to be delivered liquid. The storage and / or P580 delivery and / or control of anesthetics from the anesthetic module 8 can be controlled by the control unit 101. The anesthetic module 8 can be connectable to at least one device for storing volatile anesthetics 800.The devices for storing volatile anesthetics can be designed as anesthetic tanks 800. The at least one tank 800 is configured and designed to receive and / or store and / or dispense volatile anesthetics VA. In this case, an individual tank 800 is preferably used for each individual volatile anesthetic VA. The tanks 800 are configured and designed to receive and / or store and / or dispense a single volatile anesthetic VA. In this case, the tanks 800 are preferably pressurized such that the stored volatile anesthetics are in a liquid state at room temperature. The pressure in the tanks 800 can be in a range between 100 kPa and 500 kPa in order to keep the anesthetics liquid. The pressure in the tanks 800 is preferably in a range between 150 kPa and 300 kPa. The pressure in the 800 tanks, for example, is at least 180 kPa.The tanks 800 are thus also configured and designed to absorb and / or maintain and / or release pressure. The tanks 800 can be refillable with anesthetics VA. The tanks 800 can be configured and designed such that the fill level of the anesthetic is detectable (not shown). The fill level can be detected visually. For this purpose, the tanks 800 can be at least partially transparent. For example, the tanks 800 can have a viewing window, optionally with a scale, through which the fill level of the tanks 800 can be visually read. The fill level can also be detected by sensors. For this purpose, the tanks 800 can comprise a floating element that floats on the anesthetic and is, for example, magnetic. The field strength can be detected via a magnetic sensor. Based on the field strength, the location of the floating element can be determined.The fill level of the anesthetic can then be determined based on the position of the floating element. The tanks 800 can also have elements that allow for unambiguous assignment (not shown). For example, a code can be stored on or in the tanks 800 that allows for unambiguous assignment of the individual tank 800 or the anesthetic contained therein. The coding can be implemented, for example, mechanically and / or sensorily and / or visually. In order to connect the tanks 800 to the device 100, the anesthetic module 8 can comprise at least one receiving unit 820. The receiving unit 820 comprises at least one receiving bay 821. The receiving unit 820 can accommodate at least one tank 800 via the receiving bays 821. Preferably, the receiving unit 820 comprises more than one receiving bay 821 for accommodating a plurality of different tanks 800, for example, two (see Figure 3) or more (not shown).The device 100 can have a dedicated receiving bay 821 for each individual tank 800, i.e., for each anesthetic. In some embodiments, it is also conceivable for a P580 receiving bay 821 to be designed to accommodate different individual tanks 800 containing different anesthetics. The receiving bays 821 can have at least one device (not shown here) for identifying the individual tanks 800. This offers an additional safety aspect, as it prevents confusion between the different anesthetics. Detection can be performed mechanically and / or visually and / or sensorially. This ensures that the correct tank 800 with the correct anesthetic is placed in the designated receiving bay 821. The receiving bays 821 can, for example, have tank-specific connection devices for mechanically identifying the individual tank 800.Alternatively or additionally, the detection can also be visually coded, for example via color coding of the individual tanks 800 and their respective receiving bay 821. Alternatively or additionally, the detection can also be sensory or electrically coded. For this purpose, the tanks 800 can have, for example, a barcode or similar, and the receiving bays 821 can have a corresponding sensor. The receiving unit 820 is configured and designed to receive one or more tanks 800 such that the tanks 800 are pressurized. The receiving unit 820 is preferably configured to maintain the pressure in the tanks 800 at, for example, at least 180 kPa. For this purpose, the receiving unit 820 is configured and designed to supply pressure to the tanks 800 and / or to discharge pressure from the tanks 800. For this purpose, the receiving unit 820 can be connected to at least one pressure supply unit 810.The pressure supply unit 810 is configured and designed to supply or relieve pressure to the receiving unit 820 and thus to the tanks 800. The pressure supply unit 810 can supply pressure and / or remove pressure. For example, the pressure supply unit 810 can be connected to the fresh gas module 6 and / or the oxygen module 10 in order to draw fresh gas and / or oxygen to provide a pressure. In a preferred embodiment, the pressure supply unit 810 draws fresh gas at a regulated pre-pressure in order to provide the pressure. The pressure supply unit 810 can preferably comprise a pressure regulator in order to regulate the pressure from the fresh gas module 6 to the pressure level required in the tanks 800. The pressure supply unit 810 can also comprise at least one pressure sensor in order to detect the pressure in the respective tanks 800.The pressure supply unit 810 can also include at least one temperature sensor to detect the temperature. The device 100 can include at least one alarm device (not shown). The anesthetic module 8 can interact with the alarm device via the control unit 101. For example, the alarm device can issue an alarm if the temperature rises above a value at which it cannot be guaranteed that all volatile anesthetics can still be kept liquid. Alternatively or additionally, the alarm device can also issue an alarm if the pressure falls below a value at which it cannot be guaranteed that all volatile anesthetics can still be kept liquid. P580 The pressure supply unit 810 can preferably have its own reservoir for storing fresh gas (not shown), so that the pressure can be maintained for a certain time even without access to the fresh gas module 6.The pressure supply unit 810 can also comprise at least one check valve so that the fresh gas supply can only run in the direction from the fresh gas module 6 to the pressure supply unit 810 and not vice versa. The pressure supply unit 810 can comprise at least one valve for loading 811 and at least one valve for relieving 812 the receiving unit 820 and / or the tanks 800. Thus, pressure can be supplied to the receiving unit 820 and / or the tanks 800 via the fresh gas module 6 and the valve 811. Pressure can be released from the receiving unit 820 and / or the tanks 800 via the valve 812. For this purpose, the anesthetic module 8 is connected to the outlet 14-A so that the pressure can be released via the valve 812 and the outlet 14-A. The pressure supply unit 810 may include at least one switching valve 813 to select the respective tank 800 to be supplied.In specific embodiments, a plurality of valves 811, 812, 813 is advantageous, which can be controlled by the control device 101 or directly by a user such that the pressure in all tanks 800 in use can be regulated. The receiving unit 820 is further configured and designed to receive one or more tanks 800 such that the tanks 800 can receive and / or store and / or dispense anesthetics. The anesthetic can be received in the respective tank 800 inside or outside the receiving bays 821. For this purpose, the tanks 800 can each comprise a filling valve (not shown). The anesthetics can be received when the tanks 800 are vented. The anesthetics can also be received when the tanks 800 are pressurized. This can be particularly advantageous for desflurane, since the vapor pressure at 40°C almost reaches a pressure of 1.8 bar.The receiving unit 820 is further configured and designed to ensure a controlled release of anesthetics from the tanks 800. The anesthetic module 8 is configured and designed such that the release of anesthetics from the tanks 800 into the anesthetic supply line 9 can only occur when the respective tank 800 and the anesthetic supply line 9 are loaded. The volatile anesthetic VA is then released in liquid form.The valves of the receiving unit 820 and / or the tanks 800 and / or the pressure supply unit 810 are set up and designed such that they interact to allow various functions, such as: - Tanks 800 are inserted into the receiving bays and are under pressure and supply volatile anesthetics VA - Tanks 800 are inserted into the receiving bays and are under pressure and do not supply volatile anesthetics VA P580 - Tanks 800 are inserted into the receiving bays and are under pressure and can be filled with volatile anesthetics VA - Tanks 800 are inserted into the receiving bays and are not under pressure and can be filled with volatile anesthetics VA - Tanks 800 are inserted into the receiving bays and are not under pressure and can be removed The receiving unit 820 can be pneumatically connected to the selection unit 830 via the anesthetic supply line 9.The selection unit 830 of the anesthetic module 8 is configured and designed to select the respective anesthetic. As a rule, only one volatile anesthetic VA is used at a time to avoid undesirable interactions between the volatile anesthetics VA. The anesthetic is selected by the medical personnel. For this purpose, an input can be made on the device 100. The selection unit 830, not shown in detail here, comprises at least one selection valve 831. The selection valve 831 can be designed, for example, as a 2 / 2-way switching valve. In a specific exemplary embodiment, the selection unit 830 can comprise several selection valves 831, in particular one for each individual anesthetic. The selection valves 831 are preferably designed as bistable 2 / 2-way switching valves.The selection valves 831 can each be configured and designed such that, in a de-energized state, they block the path to the dosing unit 840 and / or the evaporation element 8a. Energizing each of the selection valves 831 can switch such that the path to the dosing unit 840 and / or the evaporation element 8a is opened. In this case, it is preferably stored in the control unit 101 that only one selection valve 831 can be opened at a time. This ensures that only one of the anesthetics is fed into the breathing gas line 4 at a time. Check valves can be arranged downstream of the selection valves 831 to prevent backflow of anesthetics (not shown). The selection unit 830 can be pneumatically connected to the dosing unit 840 via the anesthetic supply line 9.The dosing unit 840 of the anesthetic module 8 is configured and designed to dose the respectively selected anesthetic. The dosing unit 840, not shown in detail here, can comprise at least one dosing valve 841 for this purpose. The dosing valves 841 are configured and designed to enable dosing of volatile anesthetics. Dosing can occur in a liquid or gaseous state of the anesthetics. In preferred embodiments, dosing occurs in a liquid state of the anesthetics. The dosing valves 841 can be configured and designed to apply a flow and / or a volume and / or a pressure. The dosing valves 841 can preferably specify a specific flow. The dosing valves 841 can preferably be configured and designed to allow continuous dosing. In some embodiments, the dosing valves 841 can be designed as needle valves.In some embodiments, the dosing valves 841 can be designed as needle valves with stepper motors. Needle valves offer the advantage of safe and precise dosing. Position coding is also possible. Using position coding, the dosing valves 841 can be designed and configured to dose different anesthetics VA. For example, more than one anesthetic can be delivered in a dosed manner into the circuit, for example more than two, for example at least three different volatile anesthetics VA. For example, isoflurane and / or sevoflurane and / or desflurane can be dosed into the circuit in a controlled manner using position coding of the dosing valves 841. The dosing valves 841 can be designed and configured such that the valve position remains at the last set value without current supply and / or falls to an open basic setting and / or falls to a closed basic position.In preferred embodiments, the metering valves 841 can be configured and designed such that the valve position remains in the last set position without the supply of energy. The metering valves 841 can be configured and designed such that they meter the last set flow without the supply of energy. This provides the device 100 with a special safety function in the event of a power failure, since the anesthetic delivery can then continue because, on the one hand, the metering valves 841 remain in their position and, on the other hand, the delivery energy of the anesthetic VA comes from the compressed gas cylinders. The metering unit 840 can further comprise at least one flow sensor and / or at least one pressure sensor and / or at least one temperature sensor (not shown). With these sensors, the flow and / or the pressure and / or the temperature can be detected in the metering unit 840 and controlled by the control unit 101.The dosing unit 840 can be pneumatically connected to the safety unit 850 via the anesthetic supply line 9. The safety unit 850 of the anesthetic module 8 is configured and designed to control the introduction of the anesthetic into the evaporation element 8a. The introduction of the anesthetic into the evaporation element 8a can be permitted and / or stopped via the safety unit 850. The safety unit 850 can be pneumatically connected to the evaporation element 8a via the supply line 9. Furthermore, the safety unit 850 can be pneumatically connected to the outlet 14-A (not shown). For this purpose, the safety unit 850 comprises at least one valve 851, 852. In some embodiments, the safety unit 850 can comprise at least two valves 851, 852. The valves 851, 852 can, for example, be connected in series.The valves 851, 852 can preferably be designed as 2 / 2-way switching valves and / or as 3 / 2-way switching valves. The valves 851, 852 can preferably be designed as monostable valves. In a specific exemplary embodiment, the safety unit 850 comprises a first valve 851 and a second valve 852. The valves 851, 852 can be arranged, for example, between the metering valve 841 and the evaporation element 8a in the anesthetic supply line 9. P580 The first valve 851 can, for example, be designed as a monostable 2 / 2-way switching valve and can be configured to allow or close the path to the evaporation element 8a. It can be provided that the valve 851 is closed when de-energized and open when energized, or vice versa. Preferably, an anesthetic flow into the evaporation element 8a is only possible when the first valve 851 is energized.Thus, the first valve 851 can serve as a safety valve, so that the introduction of anesthetics into the evaporation element 8a can only occur actively. In an emergency situation (power and / or software failure), the valve 851 can thus automatically interrupt the introduction of volatile anesthetics. However, the first valve 851 can preferably also be configured so that it can be switched manually. Thus, the introduction of volatile anesthetics VA can also be achieved in an emergency situation, since the metering valves 841 remain in their position and the delivery energy of the anesthetics VA comes from the compressed gas cylinders and the first valve 851 is open, thus opening the path to the evaporation element 8a. The second valve 852 can, for example, be designed as a monostable 3 / 2-way switching valve and configured to allow or close the path to the evaporation element 8a and / or to the outlet 14-A.It can be provided that the valve 852 opens the path to the evaporation element 8a when de-energized and opens the path to the outlet 14-A when energized, or vice versa. Preferably, anesthetic flow into the outlet 14-A is only possible when the second valve 852 is energized. Thus, anesthetic can be actively discharged into the outlet 14-A via the second valve 852. Thus, the safety unit 850 can in particular also be set up and designed to flush out anesthetic VA from the anesthetic supply line 9. This can be advantageous in particular when changing the anesthetic. By flushing the anesthetic supply line 9, it can be prevented that more than one anesthetic is present in the anesthetic supply line 9 at a time. The safety unit 850 can also comprise an inclination sensor (not shown). The spatial orientation of the evaporation element 8a and / or the device 100 as a whole can be determined via the inclination sensor.The temperature unit 860 of the anesthetic module 8 is configured and designed to detect and / or regulate the temperature in or on the evaporation element 8a. The temperature unit 860 can comprise at least one temperature sensor to detect the temperature in or on the evaporation element 8a. Furthermore, the temperature unit 860 can comprise at least one heating element 861. The at least one heating element 861 can be configured and designed to influence the temperature in the evaporation element 8a. For example, the heating elements 861 can heat the evaporation element 8a, preferably to a temperature above room temperature. For example, temperatures of up to 40°C can be set to increase the evaporation rate of the anesthetic in the evaporation element 8a. The temperature of the evaporation element 8a affects the evaporation rate of the anesthetic. Basically, the higher the temperature, the higher the evaporation rate.The evaporation rate can thus be up to 2 liters per minute. P580 At the start of anesthesia, evaporation rates of up to 2 l / min may be necessary to initiate anesthesia. With saturated fatty tissue, lower evaporation rates may be necessary to maintain anesthesia. The device 100 can then be adjusted such that the evaporation rate is below 2 l / min, for example, below 1 l / min or below 0.5 l / min. With saturated fatty tissue, an evaporation rate of 1 ml / min to 100 ml / min may sometimes be sufficient to maintain anesthesia. The evaporation rate can be variably adjusted via the anesthetic module 8. The device 100 may include a plurality of additional functional valves 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, which are described below. The terms "first," "second," etc., are sometimes used herein.serves merely to differentiate between the various valves and has no technical significance, in particular no prioritization or the like. From Figure 1 it can be seen that the device 100 can comprise at least one pressure regulating valve 30 which is arranged in the breathing gas line 4. The pressure regulating valve 30 can be configured to influence or regulate the flow direction of the main flow S. The pressure regulating valve 30 is configured to permit or regulate variable volume flows. In some embodiments, the pressure regulating valve 30 can be designed as a bistable switching valve. The pressure regulating valve 30 can be switched in an open position or in a closed position or in at least one middle position. An open position allows the gas flow to pass through without restriction. A closed position can hermetically seal the supply line and prevent the gas flow in the breathing gas line 4.A middle position can release the gas flow to a limited extent. In preferred embodiments, the pressure control valve 30 can be designed as a proportional valve. For example, the pressure control valve 30 can be designed as a 2 / 2 proportional directional control valve (see figures). The pressure control valve 30 is preferably configured to selectively shut off the flow in at least one direction. Due to the arrangement of the pressure control valve 30 in the breathing gas line 4, the flow direction of the breathing gas mixture 5 is irreversible. The pressure control valve 30 is preferably designed as an adjustable pressure control valve 30 for regulating an expiratory pressure Pexsp. The pressure control valve 30 can be designed as a PEEP valve and configured to set or maintain at least the positive end-expiratory pressure (PEEP). The pressure control valve 30 can prevent the pressure drop during exhalation from reaching the ambient air pressure.The pressure control valve 30 represents an adjustable stenosis. The pressure control valve 30 can be electrically set to a value and / or passively regulated to a preset value. The pressure control valve 30 can be set to a patient-specific PEEP. The patient-specific PEEP can be determined and set in advance. In healthy adults, the PEEP is generally between 15 and 20 hPa. In lungs with pre-damaged P580 and / or during surgery, a higher PEEP may be required. The PEEP can be preset and / or adjusted during use. The operating pressure of the pressure control valve 30 can be electrically adjustable. The operating pressure of the pressure control valve 30 is preferably adjustable to a PEEP of 0 to 100 hPa, preferably from 0 to 80 hPa, particularly preferably from 3 to 80 hPa. The pressure control valve 30 is designed and constructed to assume any switching position within its working range.The setting of the pressure control valve 30 can be controlled manually and / or by the control device 101. The pressure control valve 30 can be configured such that power is only required to change the operating pressure. Thus, the pressure control valve 30 can be configured to remain in its preset position without the need for power. In some embodiments, the pressure control valve 30 can be configured such that, in the de-energized state, it returns to a basic state with a defined pressure. In the de-energized basic state, the PEEP valve 30 can, for example, passively regulate within a range between 3 and 10 hPa. In a specific embodiment, the PEEP valve 30 can, for example, passively regulate to a PEEP of 5 hPa. Thus, the device 100 can maintain a PEEP of, for example, 5 hPa even in an emergency situation, for example in the event of a power failure.At least the byflow flows continuously through the PEEP valve 30 and seals it. The byflow has a positive effect on the functioning of the PEEP valve 30. The device 100 is configured and designed to perform complex maneuvers to determine the optimal ventilation parameters. For example, the PEEP and / or the inspiratory pressure can be determined automatically. For example, loops via pressures and / or flows and / or volumes can also be used, such as pressure-volume loops (PV loops). Thus, the device can advantageously be used for ventilation and anesthesia and still perform complex maneuvers such as loops or PEEP finders. The device 100 can comprise a number of additional valves that serve the safety and / or function of the device. For example, the device 100 can comprise valves 21, 22, 23, 24, 25, 26, 27, 28, 29.The valves 21, 22, 23, 24, 25, 26, 27, 28, 29 can be designed, for example, as check valves. Check valves can control and / or restrict and / or prevent the flow of a gas, for example, the breathing gas mixture 5, in one direction. Opening the check valve permits flow. Closing the check valve selectively blocks flow in at least one direction. Check valves can restrict or prevent the gas from flowing back against the flow direction.The valves 21, 22, 23, 24, 25, 26, 27, 28, 29 can each be designed as a - simple check valve or as a - lockable check valve with, for example, a solenoid coil or as a - simple, loaded check valve with, for example, a spring or as a P580 - adjustable, loaded check valve with, for example, a solenoid coil and a spring or as a - continuously adjustable, loaded check valve with, for example, a solenoid coil, a spring and a stepper motor. Simple check valves only allow flow in one direction. In particular, the valves 21, 22, 23 can be designed as simple check valves, for example. Lockable check valves can allow flow in one direction in the rest position and block flow in one direction. Lockable check valves can block flow in both directions in an active position, for example when the solenoid coil is energized.The valve 28 can preferably be designed as a lockable check valve. Loaded check valves only allow flow in one direction and are closed in a resting position. Simple, loaded check valves, for example, are spring-loaded and open at a predefined pressure (working pressure) depending on the spring setting. The working pressure of simple spring-loaded check valves can be constant. The valve 27 can preferably be designed as a simple loaded check valve. The working pressure of adjustable spring-loaded check valves can be adjustable. The adjustment of the working pressure of loaded check valves and the blocking of lockable check valves can be done automatically and / or manually.The working pressure of the loaded or lockable check valves can be adjusted, for example, via spring tension and / or with a solenoid coil and / or with a stepper motor. Adjustable, loaded check valves can, for example, comprise not only the spring but also a solenoid coil that can at least partially or completely counteract the spring tension. When the solenoid coil is energized, the spring tension is reduced or completely removed, so that the flow can be increased or opened. When de-energized, the spring is active, so that the flow is reduced or closed. The valves 24, 25, 26 can, for example, be designed as adjustable, loaded check valves with a spring and solenoid coil. An additional stepper motor allows for continuous adjustment of the flow.The APL valve 29 can, for example, be designed as a continuously adjustable, loaded check valve with a spring, solenoid coil, and stepper motor. The device 100 can, for example, comprise at least one simple check valve 21, 22. For example, the device 100 can have at least a first simple check valve 21 in the inspiratory branch 1 and additionally or alternatively at least a second simple check valve 22 in the expiratory branch 2. In the specific exemplary embodiment according to Figure 1, the first check valve 21 and / or the second check valve 22 can thus be arranged in the breathing gas line 4. The arrangement of several simple check valves in the breathing gas line 4 can also be expedient and possible in some embodiments (see Figure 4). P580 The first check valve 21 can be arranged in the breathing gas line 4 upstream of the blower 3 in the flow direction.In the specific embodiment according to Figure 1, the first check valve 21 is arranged upstream of the first fresh gas supply line 7i entering the breathing gas line 4, in the direction of flow. In the specific embodiment according to Figure 1, the first check valve 21 is arranged downstream of the second fresh gas supply line 7ii entering the breathing gas line 4, in the direction of flow. In the specific embodiment according to Figure 1, the first check valve 21 is arranged upstream of the first O2 flush supply line 11i entering the breathing gas line 4, in the direction of flow. In the specific embodiment according to Figure 1, the first check valve 21 is arranged downstream of the second O2 flush supply line 11ii entering the breathing gas line 4, in the direction of flow. For example, the first check valve 21 is designed as a simple check valve.In some embodiments, it is also conceivable that the first check valve 21 is designed as a spring-loaded check valve (not shown). The second check valve 22 can be arranged in the expiratory branch 2. The second check valve 22 can be arranged in the breathing gas line 4 downstream of the patient interface in the flow direction. For example, the second check valve 22 is designed as a simple check valve. In some embodiments, it is also conceivable that the second check valve 22 is designed as a spring-loaded check valve (not shown). The check valves 21, 22 can be configured as simple check valves and designed to control at least the flow direction of the main flow S.The first check valve 21 can be configured and designed to at least control the flow direction of the main flow S and, in particular, to prevent a backflow of the respiratory gas mixture 5 into the reservoir 12. The second check valve 22 can be configured and designed to at least control the flow direction of the main flow S and, in particular, to prevent a backflow of the respiratory gas mixture 5 to the patient 90. The arrangement of further simple check valves in the respiratory gas line 4 is possible and is shown, for example, in Figure 4 (see below). The device 100 can further comprise the valves 23, 24, which are arranged in or on the respiratory gas line 4. According to the specific exemplary embodiments according to Figures 1 and 4, the device 100 can comprise at least one first safety valve 23 and / or at least one second safety valve 24.The first safety valve 23 and / or the second safety valve 24 can be arranged in the breathing gas line 4. The first safety valve 23 and / or the second safety valve 24 can be arranged in the breathing gas line 4 downstream of the blower 3. In the specific exemplary embodiments according to Figures 1 and 4, the safety valves 23 and 24 are arranged in the breathing gas line 4 directly downstream of the first O2 flush supply line 11i joining the breathing gas line 4 and thus immediately upstream of the P580 patient interface. The first safety valve 23 and / or the second safety valve 24 are thus preferably arranged in the inspiratory branch 1. The safety valves 23, 24 are preferably arranged in opposite directions to one another. The safety valves 23, 24 can be configured and designed to ensure the safety of the device 100 in an emergency situation.An emergency situation can occur, for example, in the event of a power failure, low power availability, or a technical defect in the device 100 or parts of the device 100. The safety valves 23, 24 can also ensure the safety of the device 100 if the pressure in the breathing gas line 4 is too high and / or too low. The safety valves 23, 24 enable the patient to inhale and / or exhale independently. The safety valves 23, 24 also enable the patient to be ventilated manually, e.g., using a hand bag. Independent breathing and / or manual ventilation can then take place solely via the inspiratory branch 1 of the device 100 and the safety valves 23, 24, bypassing the remaining elements of the device 100. The first safety valve 23 can be configured as a free breathing valve or as an inspiratory deficiency valve.The first safety valve 23 is preferably designed as a simple check valve. The patient can inhale via the first safety valve 23 if, for example, the blower 3 fails and is not supplying any conveying energy. This makes it possible for inspiration to occur, for example, via the first safety valve 23. In this case, the inspiration gas can be taken directly from the ambient air. The second safety valve 24 can be configured as a static pressure relief valve. The second safety valve 24 is preferably designed as a spring-loaded check valve. For example, the second safety valve 24 can be an adjustable spring-loaded check valve. The second safety valve preferably also has a solenoid coil with which the spring can be actuated.The second safety valve 24 can be subjected to a constant pressure so that the safety valve 24 remains closed during normal operation of the device 100. The second safety valve 24 can then open when the pressure in the breathing gas line 4 is higher than the working pressure of the safety valve 24, so that pressure and / or volume can escape via the safety valve 24. The second safety valve 24 can also be opened electronically, for example, by energizing the solenoid coil. The second safety valve 24 can thus be designed as a mechanical and / or electrical pressure relief valve. If the pressure in the breathing gas line 4 increases, the second safety valve 24 can open passively and / or actively. The pressure in the breathing gas line 4 can be increased, for example, if the expiratory path is obstructed, for example, by a hose system 92 blocked by contamination or kinking.P580 The second safety valve 24 thus makes it possible for expiration to occur in emergency situations. In this case, the expiratory breathing gas 5exsp can be released directly into the ambient air via the inspiratory branch 1 and the second safety valve 24. The device 100 can comprise at least one further, preferably a plurality of, valves 25, 26, 27, 28, 29. In the specific exemplary embodiments according to the figures, the device 100 can comprise, for example, five further differently arranged valves 25, 26, 27, 28, 29. For better clarity, the valves 25, 26, 27, 28, 29 are referred to below as overflow valve 25, drain valve 26, inlet valve 27, shut-off valve 28, APL valve 29. The device 100 can comprise at least one overflow valve 25. Alternatively or additionally, the device 100 may comprise at least one drain valve 26.Alternatively or additionally, the device 100 may comprise at least one inlet valve 27. Alternatively or additionally, the device 100 may comprise at least one shut-off valve 28. Alternatively or additionally, the device 100 may comprise at least one APL valve 29 (airway pressure limiting valve). The overflow valve 25, drain valve 26, inlet valve 27, and APL valve 29 are preferably designed as spring-loaded check valves. The shut-off valve 28 is preferably designed as a lockable check valve. The overflow valve 25, drain valve 26, inlet valve 27, shut-off valve 28, and APL valve 29 can be set to one or different adjustable working pressures. The working pressures can be set manually and / or automatically. The working pressures can be preset or adjusted manually or automatically during operation of the device 100.The working pressures of overflow valve 25, drain valve 26, inlet valve 27, shut-off valve 28, and APL valve 29 can be predefined with at least one setting. The inlet valve 27 can be set such that the working pressure is above 0 hPa, for example, in a range from 0.1 hPa to 10 hPa. The working pressure of the inlet valve 27 can preferably be predefined with one setting. In some embodiments, the working pressure of the inlet valve 27 can also have at least two settings. In the specific embodiment according to Figure 1, the inlet valve 27 can be set to a relatively low working pressure. For example, the working pressure of the inlet valve 27 can be set to 2 hPa. In such a setting, complete emptying of the reservoir 12 during mechanical ventilation is avoided, since the inlet valve 27 opens and can introduce ambient air into the breathing gas line 4 and / or the reservoir line 13.The shut-off valve 28 and / or the drain valve 26 and / or the overflow valve 25 can also be predefined with a setting. In preferred embodiments, the working pressures of the shut-off valve 28 and / or the drain valve 26 and / or the overflow valve 25 can preferably be operated with at least two different working pressures and therefore in at least two settings. The working pressures of the shut-off valve 28 and / or the drain valve 26 and / or the overflow valve 25 can be set such that the working pressure is in a range from 0 hPa to 200 hPa. For example, the working pressures of the shut-off valve 28 and / or the drain valve 26 and / or the overflow valve 25 can be operated either with at least one relatively high working pressure or with at least one relatively low working pressure. The shut-off valve 28 and / or the drain valve 26 and / or the overflow valve 25 can be configured to be adjustable between the at least two settings.Preferably, the working pressure can be switched manually and / or automatically at least between a first setting and a second setting. Preferably, the working pressure can be switched between a rather low working pressure and a rather higher working pressure. By definition, a low working pressure exists at working pressures less than 50 hPa. A higher working pressure exists at working pressures greater than 50 hPa. For example, the working pressure of the shut-off valve 28 and / or the drain valve 26 and / or the overflow valve 25 can be set to 10 hPa or lower in a first setting, preferably to 5 hPa or lower, for example 2 hPa or lower. For example, the working pressure of the shut-off valve 28 and / or the drain valve 26 and / or the overflow valve 25 can be set to 50 hPa or higher, preferably to 100 hPa or higher, in a second setting.A setting to a relatively low working pressure of, for example, 2 hPa or less causes the corresponding valve in the device to be in a quasi-open position, thus allowing gas to pass through. A setting to a relatively high working pressure of, for example, 100 hPa or higher causes the corresponding valve in the device to be in a quasi-closed position, thus preventing gas from passing through. The working pressure of the APL valve 29 can allow at least one, preferably several, particularly preferably a multitude of settings. For this purpose, the APL valve 29 can be equipped with a stepper motor, which allows a preferably continuous adjustment of the spring tension. The overflow valve 25 and / or the drain valve 26 and / or the APL valve 29 can be arranged in or on the forwarding system 14.As a rule, only expiratory respiratory gases 5 are discharged through the overflow valve 25, the drain valve 26 and the APL valve 29. exspIn the specific embodiment according to Figure 1, the arrangement of the valves is as follows: The overflow valve 25 can, for example, be arranged in the first line 14i of the circulation system 14. The overflow valve 25 can be arranged between the reservoir 12 and the outlet 14-A. The overflow valve 25 can be set up and designed to control the pressure of the reservoir 12. Preferably, the overflow valve 25 is designed as a spring-loaded check valve. The overflow valve 25 can be set up and designed to release pressure from the reservoir 12. The APL valve 29 can, for example, be arranged in the second line 14ii of the circulation system 14. The drain valve 26 can, for example, be arranged in the third line 14iii of the P580 circulation system 14. Drain valve 26 and APL valve 29 can, for example, be arranged in parallel lines 14ii, 14iii of the conveying system 14.The drain valve 26 can be configured to divert gases bypassing the APL valve. The inlet valve 27 can be arranged in or on the breathing gas line 4. Ambient air can be fed into the breathing gas line 4 via the inlet valve 27. The inlet valve 27 can, for example, be arranged downstream of the separating agent 40 on the breathing gas line 4. The inlet valve 27 can, for example, be arranged downstream of the humidity control module 41 on the breathing gas line 4. The inlet valve 27 can preferably branch off between the chemical separating agent 40 and the humidity control module 41. The inlet valve 27 can, for example, optionally feed ambient air into the breathing gas line 4 between the chemical separating agent 40 and the humidity control module 41. The ambient air can be fed into the breathing gas line 4 via the inlet valve 27 at an ambient air feed point 227.The shut-off valve 28 can be arranged in the breathing gas line 4. The shut-off valve 28 can, for example, be arranged downstream of the separating agent 40. The shut-off valve 28 can, for example, be arranged downstream of the humidity control module 41. The shut-off valve 28 can preferably be arranged between the chemical separating agent 40 and the humidity control module 41. The valves 25, 26, 27, 28, 29 are in particular designed and configured to influence the function of the device 100. The flow path of the breathing gas mixture 5, for example, can be influenced via different modes of operation and / or settings of the valves 25, 26, 27, 28, 29. For example, different functional modes and / or settings of the valves 25, 26, 27, 28, 29 can be used to regulate whether the breathing gas mixture 5 remains in the circuit and / or is passed on via the forwarding system 14 and / or whether ambient air is introduced into the breathing gas mixture 5.In particular, the shutoff valve 28 and / or the APL valve 29 and / or the drain valve 26 can be configured and designed to control the path of the respiratory gas mixture 5. Depending on the setting of the working pressure of the shutoff valve 28 and / or the APL valve 29 and / or the drain valve 26, the respiratory gas mixture 5 can be guided in a closed circuit or in a semi-open circuit. A closed circuit can be useful, for example, if the device 100 is operated in an anesthesia mode with volatile anesthetics (VA). A semi-open circuit can be useful, for example, if the device 100 is operated in a TIVA mode. A semi-open circuit can also be useful if the device 100 is operated in a service mode, for example, in a drying mode.The device 100 can thus be operated in different operating modes, as described below in P580, via the settings of valves 25, 26, 27, 28, 29 and optionally also via the settings of the blower 3 and / or the pressure relief valve 30, as well as via the actuation of the reservoir 12. The operating mode of the device 100 can be set manually and / or automatically specified by the control device 101. With the device 100, volatile anesthetics (VA) can be applied, directed, and, in particular, also specifically diverted for disposal or reuse. However, ventilation without volatile anesthetics can also be achieved with the device 100.The device 100 can, for example, be operated in a working mode selected from the group: anesthesia mode with volatile anesthetics (VA); anesthesia mode with intravenously administered anesthetics (TIVA mode); ventilation mode with anesthetics; ventilation mode without anesthetics, such as O2 therapy, high-flow O2 therapy (HFOT), CPAP, BiLevel, SIMV (synchronized intermittent mandatory ventilation). In principle, all ventilation modes commonly used in intensive care medicine can be implemented with the device 100. The device 100 offers the advantage that lung-protective ventilation can be implemented even under anesthesia. For example, pressure-controlled ventilation can be performed, which means a relatively low load on the lungs. Pressure-controlled ventilation is particularly advantageous for patients with lung damage.The control device 101 can regulate the device 100 such that the device 100 can be operated in different operating modes. The regulation can be achieved, for example, via the different adjustability of the components blower 3 and / or valves 25, 26, 27, 28, 29 and / or pressure relief valve 30. In particular, the flow path of the breathing gas mixture 5 and thus the operation of the device 100 as a whole can be influenced by adjusting the working pressure levels of the spring-loaded check valves 25, 26, 27, 28, 29. The operating mode of the device 100 can be set before commissioning or changed during operation. The change from one operating mode to another can be performed manually by a user, for example, by medical personnel.The switch from one operating mode to another can also occur automatically by the control device 101 when the conditions under ventilation and / or anesthesia change. For example, the device 100 can be operated in an anesthesia mode, a ventilation mode, or a combined anesthesia and ventilation mode. The operating modes can each be operated in different ways, for example, as automatic ventilation (machine ventilation), as manual ventilation (hand ventilation), or in error mode. Manual ventilation may be or become necessary, among other things, during the induction and / or recovery of anesthesia, during surgery in the neck or pharynx, and / or in emergency situations. Machine ventilation can be used, for example, during surgery with volatile anesthetics and / or intravenously administered anesthetics.Mechanical ventilation can also be used for ventilation and / or respiratory support of patients who are unable to breathe independently or who require respiratory support. P580 Operation in error mode can serve to reduce power and / or be necessary in the event of a power failure, software crash, or other technical error. Operation in error mode provides a safe state in which manual ventilation with at least a fresh gas flow is possible. Figures 1A to 1G show the device 100 of the first embodiment in various circuits and settings for implementing different operating modes. Inactive and / or blocked elements and connections are shown in dashed lines; active and / or free elements and connections are marked with solid lines. With reference to elements, active herein means that the elements can function as described and / or have gases flowing through them.With regard to elements, inactive means that the elements do not perform their described function and / or are not or only passively flowed through by gases. With regard to lines, active means that gases can be conducted through this line and that the path is not, or at least not completely, blocked. With regard to lines, blocked means that gases cannot be conducted through this line and the line is preferably hermetically sealed. The various functional valves, in particular the overflow valve 25, the drain valve 26, the inlet valve 27, and the shut-off valve 28, can each be set to relatively high working pressures or relatively low working pressures to implement the different operating modes. A high working pressure in the sense of the invention means that the respective valve is closed and blocks the gas flow in the line in which it is located.A high working pressure can exist, for example, if the corresponding valve is subjected to a working pressure of more than 50 hPa, for example 100 hPa. A low working pressure in the sense of the invention means that the respective valve is open and can allow gas flow in the line in which it is located. A low working pressure can exist, for example, if the corresponding valve is subjected to a working pressure of less than 10 hPa, for example 2 hPa or less than 0.5 hPa. The working pressure of the APL valve 29 can preferably be continuously adjusted and allow a variety of settings. The APL valve 29 can thus limit and / or prevent the gas flow in the corresponding line. The APL valve 29 is preferably designed as an electrically adjustable valve. The APL valve 29 is configured to regulate an inspiratory pressure Pinsp.The APL valve 29 can cause breathing gas mixture 5 to be discharged via the outlet 14-A if the pressure in the breathing gas line 4 exceeds the inspiratory pressure Pinsp. In preferred embodiments, the APL valve 29 is configured as a controllably loaded check valve with a stepper motor. The APL valve 29 is preferably configured to remain in its last set position without power supply. Thus, the APL valve 29 can regulate to the last set inspiratory pressure Pinsp without power supply. This is particularly advantageous in the event of a power failure, as it allows the APL valve 29 to continue performing its function. In preferred embodiments, the APL valve 29 can be configured as a digital APL valve 29. The APL valve 29 can preferably be controlled automatically by the software or by the control device 101. The APL valve can alternatively or additionally be operated manually.This gives medical personnel the option of operating the APL valve manually if necessary, e.g., using a haptic encoder (rotary handle), and loading or unloading the APL. Figure 1A shows the device 100 in a first operating mode M1 for manual ventilation with the application of volatile anesthetics. Figure 1A shows that the blower 3 is inactive in the first operating mode M1. An inactive blower 3 means that the blower 3 does not supply any conveying energy. The fan wheel of the blower 3 is not driven in the inactive blower. In an inactive state, the breathing gas mixture 5 can flow through the blower 3. In the first operating mode M1, the reservoir 12 supplies the conveying energy for the breathing gas mixture 5. The reservoir 12, which can be designed, for example, in the form of a hand bag, is operated manually or automatically in the first operating mode M1. The reservoir 12 can thus supply the breathing energy in the first working mode M1.When the reservoir 12 is actuated, the breathing gas mixture 5 is pumped into the reservoir line 13. The overflow valve 25 is pressurized to a high working pressure and blocks the first line 14i. This allows the breathing gas mixture 5 to be introduced from the reservoir line 13 into the inspiratory branch 1 of the breathing gas line 4. The check valve 21 prevents the breathing gas mixture 5 from flowing back into the reservoir line 13. In the first operating mode M1, the fresh gas module 6 is active. In the first operating mode M1, the fresh gas switching valve 32 is in its basic position, so that fresh gas can be introduced into the breathing gas line 4 via the first fresh gas supply line 7i. In the first operating mode M1, the first fresh gas supply line 7i is active. In the first operating mode M1, the second fresh gas supply line 7ii is inactive. The fresh gas can then be introduced in the flow direction behind the check valve 21.The fresh gas feed point 207 can then be arranged between the first check valve 21 and the evaporation element 8a (and thus the anesthetic feed 209). The fresh gas introduction can preferably occur with a constant flow. The fresh gas can then form at least one byflow. In the first operating mode M1, the anesthetic module 8 is active. In the first operating mode M1, volatile anesthetics VA can be introduced into the evaporation element 8a via the anesthetic module 8 and the anesthetic supply line 9 and thus added to the breathing gas mixture 5 as needed. The breathing gas mixture 5 can be optimally enriched with volatile anesthetics VA via the fresh gas byflow. In the first operating mode M1, the oxygen module 10 is active. An active oxygen module 10 means that oxygen can optionally be introduced via the O2 flush 10.In the first operating mode M1, the O2 flush switching valve 31 is in its basic position, so that optional P580 oxygen can be introduced into the breathing gas line 4 via the first O2 flush supply line 11i. In the first operating mode M1, the first O2 flush supply line 11i is active. In the first operating mode M1, the second O2 flush supply line 11ii is inactive. The oxygen introduction via the O2 flush 10 can optionally occur after (manual or automatic) actuation of the O2 flush 10. The oxygen introduction then occurs via the O2 flush 10 and the first O2 flush supply line 11i in the flow direction behind the blower 3 and in front of the safety valves 23, 24. The O2 flush feed point 211 can then be arranged between the blower 3 and the safety valves 23, 24. This offers the advantage that the volatile anesthetics can be quickly flushed out of the lungs via oxygen flooding, if necessary. The O2 flush 10 can also be used to fill the reservoir 12, e.g.after a leak. The oxygen then flows from the O2 flush 10 via the feed point 211 into the breathing gas line 4 and from there in the flow direction S through the inspiratory branch 1 and the expiratory branch 2 to the reservoir 12. In the first operating mode M1, the patient can be manually supplied with inspiratory breathing gas 5 via the inspiratory branch 1. insp and optionally supplied with volatile anesthetics (VA). In the first operating mode M1, the expiratory branch 2 with its elements can also be active and expiratory breathing gas 5 exsp In the first working mode M1, the expiratory breathing gas can be 5 exsp be diverted away from the patient via the expiratory branch 2. The check valve 22 prevents backflow of the expiratory breathing gas 5 exspto the patient. The PEEP valve 30 is active and set to an individual PEEP. The main flow direction S of the respiratory gas mixture 5 runs via the inspiratory branch 1 towards the patient interface and from the patient interface into the expiratory branch 2. The sensors 16, 17, 18, 19, 20, 39 are active in the first operating mode M1. The valves 26, 28, 29 are switched in the operating mode M1 such that the respiratory gas mixture 5 in the expiratory branch 2 can take two different paths: The respiratory gas mixture 5 or portions of the respiratory gas mixture 5 can be directed in the direction of the main flow S in the circuit and / or diverted from the circuit via the discharge system 14. The shut-off valve 28 is pressurized with a low working pressure in the first operating mode M1 and releases the respiratory gas line 4. In the first operating mode M1, the shut-off valve 28 can act as a simple check valve without the action of the solenoid coil.As a result, the breathing gas mixture 5 can be directed at least partially in the direction of the main flow S in the circuit in working mode M1. The breathing gas mixture 5 is then fed back into the inspiratory branch 1 from the expiratory branch 2. In the process, the breathing gas mixture 5 passes through the separating agent 40 and the humidity control module 41, which are active in the first working mode M1. CO2 is separated in the separating agent 40, and moisture can be removed from the breathing gas mixture 5 in the humidity module 41. In the inspiratory branch 1, fresh gas and / or oxygen and / or anesthetics can be fed back into the breathing gas mixture 5. The settings of the drain valve 26 and the APL valve 29 can influence whether the second line 14ii and the third line 14iii are active and thus conduct gas. From Figure 1A, P580 shows that in the first working mode M1, the second line 14ii is active and the third line 14iii is blocked.In the first operating mode M1, the release valve 26 is subjected to a high working pressure and blocks the third line 14iii. In the first operating mode M1, the APL valve 29 is subjected to a working pressure that restricts the gas flow through the second line 14ii. This allows the breathing gas mixture 5 to be at least partially discharged from the circuit through the second line 14ii of the circulation system 14. The APL valve 29 can be set to a patient-specific inspiratory pressure Pinsp. The patient-specific inspiratory pressure Pinsp can be determined and set in advance. In healthy adults, the inspiratory pressure Pinsp is typically between 20 and 25 hPa. In previously damaged lungs and / or during surgery, a higher inspiratory pressure Pinsp may be or become necessary. The inspiratory pressure Pinsp can be preset and can also be adjusted during use.The setting of the APL valve 29 can be controlled manually and / or by the control device 101. By diverting a partial gas from the circuit, the APL valve 29 can limit the maximum pressure during inspiration. Furthermore, diverting a partial gas can ensure that gas exchange takes place. Through gas exchange, pulmonary metabolites (such as methane or ammonia) can be removed from the circuit. Fresh gas and / or oxygen and / or anesthetics can be supplied to the circuit as needed. During inspiration, the reservoir 12 is actively activated. The breathing gas mixture 5 reaches the patient via the Y-piece 93 until the inspiratory pressure Pinsp set on the APL valve 29 is reached in the patient. An inspiratory plateau can then be maintained in which no flow flows to or from the patient. During expiration, the activation of the reservoir 12 is terminated.The breathing gas mixture 5 flows from the patient via the Y-piece 93 into the expiratory branch 2, and the pressure drops to the PEEP set on the pressure control valve 30. An expiratory plateau then exists, during which no flow flows from or to the patient. Manual ventilation always involves an excess fresh gas flow. The excess volume can only be released into the circulation system 14 during inspiration. The reservoir 12 must then always be displaced to a greater extent than the patient volume. Figure 1B shows the device 100 in a second operating mode M2 ​​for automatic ventilation with the application of volatile anesthetics. Figure 1B shows that the blower 3 is active in the second operating mode M2. The active blower 3 supplies the conveying energy for the breathing gas mixture 5. The fan wheel of the blower 3 is driven and conveys the breathing gas mixture 5.In the second operating mode M2, the blower 3 can generate the required patient flow and a constant byflow. In the second operating mode M2, the blower 3 can generate a set flow pattern. In the second operating mode M2, the reservoir 12 serves as a storage device for part of the breathing gas mixture 5. In the second operating mode M2, the reservoir 12 does not supply any delivery energy for the breathing gas mixture 5. In the second operating mode M2, the reservoir 12 can at least partially supply the volume for the blower 3. In the second operating mode M2, the fresh gas switching valve 32 and the O2 flush switching valve 31 are in the basic position, so that fresh gas can be introduced into the breathing gas line 4 via the first fresh gas supply line 7i and optionally oxygen via the first O2 flush supply line 11i. In the second operating mode M2, the fresh gas can be introduced downstream of the check valve 21 in the direction of flow. The fresh gas introduction can preferably be carried out with a constant flow.The fresh gas, together with the blower flow, forms a byflow. In the second operating mode M2, the anesthetic module 8 is active. In the second operating mode M2, volatile anesthetics (VA) can be introduced into the evaporation element 8a via the anesthetic module 8 and the anesthetic supply line 9 and thus added to the breathing gas mixture 5 as needed. The breathing gas mixture 5 can be optimally enriched with volatile anesthetics (VA) via the byflow. In the second operating mode M2, the patient can be supplied with inspiratory breathing gas 5 via the inspiratory branch 1. insp and optionally supplied with volatile anesthetics. In the second operating mode M2, the expiratory branch 2 can also be active, so that the expiratory breathing gas 5 exspis diverted away from the patient via the expiratory branch 2. The check valves 21, 22 prevent the respiratory gas mixture 5 from flowing back against the main flow direction S. The PEEP valve 30 is active and set to an individual PEEP. The main flow direction S of the respiratory gas mixture 5 runs via the inspiratory branch 1 towards the patient interface and from the patient interface via the expiratory branch 2. The respiratory gas mixture 5 is then fed back from the expiratory branch 2 into the inspiratory branch 1 and / or the reservoir 12. During inspiration, the respiratory gas mixture 5 flows mostly into the patient until an inspiratory plateau is reached. The byflow flows through the expiratory branch 2. When the inspiratory plateau is reached, the blower 3 predominantly delivers the byflow, which flushes the circuit K1. During this phase, the byflow refills the reservoir 12.In the second operating mode M2, the valves 26, 28, 29 are switched such that the breathing gas mixture 5 essentially flows in the circuit along the main flow direction S: In the second operating mode M2, the shutoff valve 28 is subjected to a low working pressure and releases the breathing gas line 4. The APL valve 29 is subjected to a higher working pressure than the shutoff valve 28 and thus blocks the second line 14ii. The drain valve 26 is subjected to a high working pressure and blocks the third line 14iii. This allows the breathing gas mixture 5 to be directed in the direction of the main flow S in the circuit in the second operating mode M2. The breathing gas mixture 5 is then fed from the expiratory branch 2 back into the inspiratory branch 1. In the process, the breathing gas mixture 5 passes through the separating agent 40 and the humidity control module 41.CO2 is separated in the separating agent 40, and moisture can be removed from the respiratory gas mixture 5 in the humidity module 41. Fresh gas and / or oxygen and / or anesthetics can be fed back into the respiratory gas mixture 5 in the inspiratory branch 1. In the second operating mode M2, the overflow valve 25 is pressurized to a low working pressure and can open the first line 14i. Thus, the respiratory gas mixture 5, or portions of the respiratory gas mixture 5, can be conducted through the first line 14i of the discharge system 14 to the outlet 14-A and released into the environment. When the reservoir 12 is full, i.e., when the pressure of the reservoir 12 exceeds the set pressure of the overflow valve 25, respiratory gas can be diverted from the reservoir 12 to the outlet 14-A via the first line 14i and through the overflow valve 25. This can effectively prevent overfilling of the reservoir 12.Overfilling the reservoir 12 could damage it and / or cause it to burst. The inlet valve 27 can be designed as a volume and / or flow deficiency valve. The inlet valve 27 can be set to a low working pressure. The inlet valve 27 is preferably set such that outside air can be supplied to the circuit when there is a negative pressure in the breathing gas line 4. In the second operating mode M2, a negative pressure can arise in the breathing gas line 4, for example, in the event of a (unintentional or intentional) leak. Operating the blower 3 when there is a leak in the system can cause the reservoir 12 to run dry and a negative pressure to arise in the breathing gas line 4. A negative pressure in the breathing gas line 4 can open the inlet valve 27 so that ambient air can be supplied to the breathing gas line 4 via the inlet valve 27. For example, the inlet valve 27 is set to a working pressure of 2 hPa.This corresponds to the pressure of the filled reservoir 12. Considering Figures 1A and 1B, for example, it can be seen that the breathing gas mixture 5 can be conducted in a substantially closed circuit and / or in a substantially semi-open circuit. The interaction of the shut-off valve 28, the discharge valve 26, and the APL valve 29 is crucial here. The interaction of the valves 26, 28, 29 can be as follows: With a low working pressure set for the shut-off valve 28 and a high working pressure set for the discharge valve 26 and the APL valve 29, the breathing gas mixture 5 can be conducted in a substantially closed circuit. The closed circuit exists when the working pressure of the shut-off valve 28 is lower than the working pressure of the discharge valve 26 and the APL valve 29.Because the respective working pressure of the drain valve 26 and APL valve 29 is higher than the working pressure of the shut-off valve 28, the path to outlet 14-A is blocked. Because the respective working pressure of the drain valve 26 and APL valve 29 is higher than the working pressure of the shut-off valve 28, the path of the breathing gas line 4 to the separating agent 40 and / or to the humidity control module 41 is open. With a high working pressure of the shut-off valve 28 and low working pressures of the drain valve 26 and / or APL valve 29, the breathing gas mixture 5 can be conducted in a semi-open circuit. The semi-open circuit exists when the working pressure of the shut-off valve 28 is greater than the respective working pressure of the drain valve 26 and APL valve 29. In this case, the shut-off valve 29 blocks the path to the blower 3.The flow direction of the respiratory gas mixture 4 then runs - roughly sketched - from the blower 3 via the inspiratory branch 1 to the patient interface and to the patient 90 and from the patient 90 via the expiratory branch 2 to the outlet 14-A. Because the working pressure of the shut-off valve 28 is higher than the respective working pressures of the discharge valve 26 and APL valve 29, the path to the chemical release agent 40 or to the blower 3 is blocked. Because the working pressure of the shut-off valve 28 is higher than the respective working pressures of the discharge valve 26 and APL valve 29, the path to the outlet 14-A is open. Figure 1C shows the device 100 in a third working mode M3 for manual ventilation without the application of volatile anesthetics. Figure 1D shows the device 100 in a fourth working mode M4 for automatic ventilation without the application of volatile anesthetics.Alternatively or in addition to use with volatile anesthetics, the device 100 can be operated in working modes without the application of volatile anesthetics. The device 100 is thus also designed and configured to ventilate the patient without volatile anesthetics. Thus, the device 100 can also be used with total intravenous anesthesia (TIVA) and / or with local anesthesia such as spinal anesthesia. In TIVA, anesthetics, such as propofol, are injected into the bloodstream. Additional anesthesia with inhalation anesthetics is possible. The device 100 offers the advantage of allowing ventilation in combination with total intravenous anesthesia, whereby alternatively or additionally, volatile anesthetics (VA) can also be administered via the airways.In operating modes without the addition of inhalation anesthetics VA, the device 100 can, for example, be operated in an open and / or semi-open circuit. In operation without inhalation anesthetics VA, the respiratory gas can be discharged into the environment. In operating modes without the addition of inhalation anesthetics VA, the respiratory gas mixture can be completely replaced for each respiratory phase (inspiration and expiration). Thus, the minute volume is constantly renewed. For the treatment of an adult, this means that an average of approximately 6 l / min of respiratory gas mixture is provided and applied. Figure 1C shows that the blower 3 is inactive in the third operating mode M3, so that the respiratory gas mixture 5 merely flows through the blower 3. In the third operating mode M3, the reservoir 12 supplies the delivery energy for the respiratory gas mixture 5 and thus the respiratory energy. In the third operating mode M3, the anesthetic module 8 is generally inactive.In the third operating mode M3, as a rule, no volatile anesthetics VA are added to the breathing gas mixture 5. When the reservoir 12 is actuated, the breathing gas mixture 5 is pumped into the reservoir line 13. From the reservoir line 13, the breathing gas mixture 5 is introduced into the inspiratory branch 1 of the breathing gas line 4. The check valve 21 prevents the breathing gas mixture 5 from flowing back into the reservoir line 5. P580 In the third operating mode M3, the fresh gas switching valve 32 can preferably be switched such that fresh gas can be introduced into the breathing gas line 4 via the second fresh gas supply line 7ii. The fresh gas can then be introduced upstream of the first check valve 21 in the direction of flow. In the third working mode M3, the O2 flush switching valve 31 can preferably be switched such that oxygen can optionally be introduced into the breathing gas line 4 via the second O2 flush supply line 11ii.The oxygen introduction via the O2 flush 10 can optionally occur after (manual or automatic) actuation of the O2 flush 10. The oxygen introduction then occurs via the O2 flush 10 and the second O2 flush supply line 11ii in the direction of flow upstream of the blower 3. In the third operating mode M3, the oxygen introduction via the O2 flush 10 preferably occurs in the direction of flow upstream of the first check valve 21. In the third operating mode M3, fresh gas and / or oxygen can thus be fed into the breathing gas line 4 upstream of the first check valve 21 and thus fill the reservoir 12 as needed. In the third operating mode M3, the patient can be manually supplied with inspiratory breathing gas 5 at least via the inspiratory branch 1. insp In the third operating mode M3, the expiratory branch 2 with its elements can also be active. In the third operating mode M3, the expiratory breathing gas 5 exspbe diverted away from the patient via the expiratory branch 2. The PEEP valve 30 is active and set to an individual PEEP. The PEEP valve 30 can regulate to the set PEEP pressure. The main flow direction S of the respiratory gas mixture 5 runs via the inspiratory branch 1 towards the patient interface and from the patient interface via the expiratory branch 2. In working mode M3, volatile anesthetics VA are generally not applied, so the respiratory gases do not have to be conducted in a closed circuit. In working mode M3, the expiratory respiratory gas 5 exspvia the expiratory branch 2 and the discharge system 14 into the environment. In the third operating mode M3, the respiratory gas mixture 5 is conducted in a semi-open circuit, i.e., inspiration occurs via the inspiratory branch 1 and expiration occurs via the expiratory branch 2, with the expiratory respiratory gas 5exsp being discharged via the discharge system 14 and not fed back into the inspiratory branch 1. For this purpose, the shut-off valve 28 can be subjected to a high working pressure in the third operating mode M3 and block the connection between the inspiratory branch 1 and the expiratory branch 2 in such a way that the expiratory respiratory gas 5exsp cannot be fed back into the inspiratory branch. In the third operating mode M3, no respiratory gas flows through the separating agent 40 and the humidity control module 41 and are inactive.In the third working mode M3, the drain valve 26 is subjected to a low working pressure and opens the third line 14iii. The APL valve 29 is subjected to a higher working pressure than the drain valve 26 and thus blocks the second line 14ii. P580 Due to the low working pressure of the drain valve 26, the expiratory breathing gas 5exsp is diverted via the third line to outlet 14-A and into the environment, bypassing the APL valve 29. In the third working mode M3, the APL valve 29 is inactive, so that the PEEP valve 30 also specifies the inspiratory pressure Pinsp. In the third working mode M3, the PEEP corresponds to the inspiratory pressure Pinsp. During expiration, the PEEP valve 30 regulates to the PEEP pressure. During inspiration, the PEEP valve 30 regulates the inspiratory patient pressure.In the third operating mode M3, the breathing gas mixture 5 is not conditioned, but rather the entire gas used is released into the environment via the discharge system 14. Figure 1D shows that in the fourth operating mode M4, the breathing gas mixture 5 is conducted in a semi-open circuit, similar to the third operating mode M3. The flow path of the fourth operating mode M4 essentially corresponds to that of the third operating mode M3. In contrast to the third operating mode, the blower 3 is active in the fourth operating mode M4 and supplies the conveying energy for the breathing gas mixture 5. In the fourth operating mode M4, the blower 3 can generate the required patient flow and a constant byflow. In the fourth operating mode M4, the blower 3 can dynamically generate a set patient flow pattern. In the fourth operating mode M4, the reservoir 12 can at least partially supply the volume for the blower 3. The fresh gas introduction can preferably take place at a constant flow.The fresh gas, together with the blower flow, forms a byflow. The active blower 3 creates a negative pressure in front of the blower 3 in the inspiratory branch 1, so that the inlet valve 27 can be activated in the fourth operating mode M4. If the fresh gas and / or oxygen feed is too low, ambient air can be pumped into the breathing gas line 4 via the inlet valve 27. In the fourth operating mode M4, the overflow valve 25 is subjected to a low working pressure and can open the first line 14i. Thus, the breathing gas mixture 5 can be at least partially guided through the first line 14i to the outlet 14-A and released into the environment. The overflow valve 25 can be configured and designed to protect the reservoir 12 from overexpansion and / or destruction.In the fourth operating mode M4, fresh gas can be fed into the breathing gas line 4 via the fresh gas module 6 and / or oxygen via the O2 flush 10 upstream of the first check valve 21 and quickly fill the reservoir 12 as needed. Overfilling of the reservoir 12 can be effectively prevented by the overflow valve 25. Figure 1E shows the device 100 in a fifth operating mode M5 for manual ventilation in an emergency mode. The device 100 is configured and designed to be able to be operated safely with the fifth operating mode M5 even in emergency situations. An emergency situation can occur, for example, if the primary power source 103 and / or the secondary power sources 104 fail. An emergency situation can also occur, for example, if the primary power source 103 P580 and / or the secondary power sources 104 can only provide limited energy.In an emergency situation, the power supply may be reduced or fail completely. In the fifth operating mode M5, the device 100 can be operated without power and / or in a power-saving mode. In the fifth operating mode M5, the device 100 can be operated without a power source and / or only with the secondary power sources 104. Alternatively or additionally, an emergency situation can also occur if critical components of the device 100, such as the control device 101, the software, the hardware, or the blower 3, fail partially or entirely. In the fifth operating mode M5, the device 100 can preferably retain the last selected functions and settings and continue to enable ventilation. The fifth operating mode M5 enables medical personnel to remain capable of acting even in emergency situations.The device 100 is configured and designed to automatically switch to the fifth operating mode M5 upon the occurrence of an emergency situation in order to ensure emergency supply. It is also possible to manually set the fifth operating mode M5. This can be advantageous for establishing power-saving operation. In the fifth operating mode M5, the monitor can be dimmed to save power. In the fifth operating mode M5, all actuators can be de-energized. In the fifth operating mode M5, the sensors can be inactive. In the fifth operating mode M5, the blower 3 can also be put into power-saving operation. For example, the blower can be operated less dynamically. The device 100 can be configured and designed to administer volatile anesthetics VA in the fifth operating mode M5, since the fresh gas flow can be maintained. In preferred embodiments, no volatile anesthetics VA are administered in the fifth operating mode M5.The anesthetic module 8 and the evaporation element 8a are inactive, so that the patient can continue to be ventilated with the device 100, but without the application of volatile anesthetics. Anesthesia with intravenous anesthetics is then possible. Figure 1E shows that the blower 3 can be inactive in the fifth operating mode M5. In the fifth operating mode M5, the reservoir 12 can supply the delivery energy for the respiratory gas mixture 5. The respiratory gas mixture 5 can flow (passively) through the blower 3. When the reservoir 12 is actuated, the respiratory gas mixture 5 is delivered into the reservoir line 13. From the reservoir line 13, the respiratory gas mixture 5 is introduced into the inspiratory branch 1 of the respiratory gas line 4. The check valve 21 prevents the breathing gas mixture 5 from flowing back into the reservoir line 5. When de-energized, the fresh gas switching valves 32 are in their basic position.Thus, in the fifth working mode M5, fresh gas can be fed into the breathing gas line 4 via the first fresh gas supply line 7i. The fresh gas can thus be fed in at the feed point 207 and downstream of the check valve 21. P580 In working mode M5, the fresh gas can be fed into the breathing gas line at a constant flow because the switching valve 87 and / or the metering valve 88 of the fresh gas supply line 7 can remain in their last set positions when de-energized. This means that the metering of fresh gas can remain at the last set value. In the fifth working mode M5, the O2 flush 10 can be operated manually so that oxygen can optionally be fed into the breathing gas line 4. When de-energized, the O2 flush switching valves 31 are in their basic position. The oxygen can thus be fed in via the first O2 flush supply line 11i.The oxygen can thus be fed in at the feed point 211 and upstream of the safety valves 23, 24 in the direction of flow. The patient can thus be supplied with breathing gas and / or fresh gas and / or oxygen in the fifth working mode M5 by actuating the reservoir 12 and via the fresh gas module 6 and / or the oxygen module 10. Figure 1E shows that the expiratory breathing gas 5exsp is guided in the fifth working mode M5 in a similar way to the first working mode M1. The flow path of the fifth working mode M5 essentially corresponds to that of the first working mode M1: The valves 26, 28, 29 are switched in the fifth working mode M5 such that the breathing gas mixture 5 in the expiratory branch 2 can take two different paths: The breathing gas mixture 5 or portions of the breathing gas mixture 5 can be guided in the direction of the main flow S in the circuit and / or diverted from the circuit via the discharge system 14.In emergency mode M5, the breathing gas mixture 5 can be conducted at least in the first circuit K1. In emergency mode M5, the breathing gas mixture 5 can be at least partially discharged via outlet 14-A. In the fifth operating mode M5, the shut-off valve 28 is de-energized and thus inactive. Thus, the shut-off valve 28 acts as a simple check valve and releases the breathing gas line 4 in the direction of the main flow S. The expiratory breathing gas 5exsp can thus be at least partially directed in the direction of the main flow S in the circuit. In the process, the expiratory breathing gas 5exsp passes through the separating agent 40, in which CO2 can be chemically separated. The humidity management system 41 is inactive when de-energized and is merely flowed through. In the inspiratory branch 1, fresh gas and / or oxygen can be supplied to the breathing gas mixture 5 again. The third line 14iii of the discharge system 14 is blocked by the drain valve 26 in the fifth operating mode M5.When de-energized, the drain valve 26 is subjected to a high working pressure. When de-energized, the drain valve 26 can, for example, have a working pressure of 100 hPa due to the spring tension. The second line 14ii of the circulation system 14 can be active in the fifth working mode M5 because the APL valve 29 remains in the last set position when de-energized. The APL valve 29 can therefore continue to regulate to the (last set) inspiratory pressure Pinsp in the emergency mode M5 when de-energized. P580 Since the working pressure of the APL valve 29 in the fifth working mode M5 is lower than the working pressure of the drain valve 26, the expiratory breathing gas 5exsp can be at least partially diverted through the second line 14ii and the outlet 14-A. The gas flow through the second line 14ii can thus be released to a limited extent by the APL valve 29 in the fifth working mode M5.Excess breathing gas mixture 5 that cannot be circulated in the breathing gas line 4 can be discharged via the second line 14ii during inspiration. In the fifth operating mode M5, the pressure control valve 30 is de-energized and thus generally no longer adjustable. In the fifth operating mode M5, the pressure control valve 30 can passively regulate the expiratory pressure Pexsp. When de-energized, the pressure control valve 30 drops to its passive working pressure. In the fifth operating mode M5, the pressure control valve 30 can passively regulate the PEEP, for example, to 5 hPa. In contrast to the first operating mode M1, the sensors 15, 16, 17, 18, 19, 20, 39 and the humidity control module 41 are de-energized and thus inactive in the fifth operating mode M5. Alternatively or in addition to the previously described operating modes, the device 100 can also be operated in at least one sixth operating mode M6, which can provide a large, substantially constant flow.A constant flow can be used, for example, to perform high-flow therapy (HFOT). The device 100 can be used to perform HFOT. For this purpose, humidifiers and / or heating elements (not shown here) can optionally be connected to the device 100 to humidify and / or heat the respiratory air. The sixth operating mode M6 can be used in combination with spinal anesthesia and / or with other local anesthetics. The sixth operating mode M6 can be operated with conscious patients who are to receive respiratory support. Figure 1F shows the device 100 in the sixth operating mode M6 for a constant flow (HFOT), wherein volatile anesthetics VA can optionally be applied. The sixth operating mode M6 can be implemented both without the addition of volatile anesthetics (see Figure 1F) and with the application of volatile anesthetics (not shown).The sixth operating mode M6 can also be implemented in a fault mode (not shown). Figure 1F shows the device 100 in the sixth operating mode for a constant flow and without application of volatile anesthetics. The device 100 is configured and designed to generate a nearly constant flow without generating or predetermining a breathing pattern. In the sixth operating mode M6, the flow is applied independently of the patient's breathing phases. In the HFOT modes, flows of up to 80 l / min can be achieved. In HFOT mode, constant flows of 60 l / min are generally generated. HFOT can be performed via an open and / or semi-open circuit. P580 HFOT is preferably performed via an open circuit without expiratory branch 2 (see Figure 1F). The device 100 can then have only one inspiration tube.In this case, the patient 90 can be supplied with the breathing gas mixture 5 via the inspiration tube and the patient interface 91 and exhale into the environment. The patient interface 91 is preferably a nasal cannula to implement an HFOT. Figure 1F shows that in the sixth operating mode M6, neither the blower 3 is active nor does the reservoir 12 supply the delivery energy. The breathing gas mixture 5 is driven exclusively by the fresh gas module 6. In the sixth operating mode M6, the fresh gas switching valves 32 are in their basic position. Thus, in the sixth operating mode M6, fresh gas can be fed into the breathing gas line 4 via the first fresh gas supply line 7i. The feed of fresh gas can thus take place at the feed point 207 and in the flow direction behind the check valve 21. The feed of fresh gas can preferably provide the flow for the HFOT.The constant fresh gas flow can preferably be directed directly to the patient interface without interference. Optionally, in the sixth operating mode M6, the O2 flush 10 can be manually operated and optionally additional oxygen can be fed into the breathing gas line 4. In the sixth operating mode M6, the O2 flush switching valves 31 are in their basic position. Oxygen can thus be fed in via the first O2 flush supply line 11i. Oxygen can thus be fed in at the feed point 211 and, in the direction of flow, upstream of the safety valves 23, 24. The inspiratory pressure sensor 15 and / or the inspiratory flow sensor 17 and / or the oxygen sensor 19 are preferably active in the sixth operating mode M6. The second safety valve 024 can be electrically activated in the sixth operating mode M6 and offers additional protection.The device 100 is alternatively or additionally configured to provide a constant flow in the sixth operating mode M6 and simultaneously administer volatile anesthetics VA (not shown). Even with the application of volatile anesthetics, a constant flow is generated without generating or predetermining a breathing pattern and independently of the patient's breathing phases. In the sixth operating mode M6, the anesthetic module 8 and / or the evaporation element 8a can optionally be activated. A constant fresh gas flow is fed in via the fresh gas module 6 and the first fresh gas supply line 7i. After being fed in, this flow can be enriched with anesthetics VA in the evaporation element 8a and can be fed directly to the patient interface without further influence.The device 100 can then be configured and designed to be connected to a hand bag 35 designed for this purpose, so that the volatile anesthetics are not released into the environment but can be reused via the hand bag 35 (not shown). P580 When applying volatile anesthetics in the sixth operating mode M6, the multigas sensor 20 can also preferably be active. Furthermore, for safety reasons, a near-patient O2 flush is possible. Alternatively or additionally, the device 100 is configured to provide a constant flow in a failure mode without applying volatile anesthetics (not shown).In the error mode of the sixth operating mode M6, for example in a de-energized state, the fresh gas feed can continue behind the first check valve 21, since the switching valve 87 and / or the metering valve 88 of the fresh gas supply line 7 can remain de-energized in their last set positions. In the error mode of the sixth operating mode M6, the sensors 15, 17, 19 can be deactivated. In the error mode, no measurements are taken by the inspiratory flow sensor 17 and / or the O2 sensor 19 and / or the inspiratory pressure sensor 15. In the error mode of the sixth operating mode M6, the anesthetic module 8 can be deactivated manually or automatically so that no more anesthetics are fed in. The O2 flush 10 can still be operated manually in the error mode of the sixth operating mode M6, so that oxygen can optionally be fed into the breathing gas line 4 close to the patient.Figure 1G shows the device 100 in a seventh operating mode M7, which represents a service mode. In the seventh operating mode M7, the device 100 is generally not connected to a patient 90. As an alternative to the previously described operating modes, the device 100 can be operated in the seventh operating mode M7, which allows maintenance and / or servicing and / or drying. For example, the device 100 can also be operated in a standby mode. Advantageously, the device 100 can be operated in the seventh operating mode M7 to enable drying of the device 100 or at least parts of the device 100. In this way, the moisture condensed from the breathing gas line 4 by the use of the chemical separating agent 40 can be effectively removed. In the seventh operating mode M7, the fresh gas module 6 is inactive.In the seventh operating mode M7, the fresh gas module 6 can be deactivated by closing the metering valve 88 and / or the switching valve 87 in the fresh gas supply line 7. In the seventh operating mode M7, the blower 3 is active. The blower 3 can generate a constant pressure and / or a constant flow and / or a constant volume. The blower 3 can generate a negative pressure upstream of the blower 3 in the breathing gas line 4 in the flow direction. Since the fresh gas module 6 is inactive, it does not supply fresh gas to the blower 3. Therefore, in the seventh operating mode M7, the inlet valve 27 can open. Thus, in the seventh operating mode M7, air from the environment can be sucked into the device 100 via the inlet valve 27. The ambient air can be fed into the breathing gas line 4 via the inlet valve 27 at the ambient air feed point 227.P580 In the specific embodiment according to Figure 1, the feed point for ambient air 227 can be located downstream of the separating means 40 in the flow direction. In this embodiment, the feed point for ambient air 227 can preferably be located downstream of the shut-off valve 28 in the flow direction. The feed point for ambient air 227 is, for example, upstream of the humidity control module 41 in the flow direction. In the specific embodiment according to Figure 1, the feed point for ambient air 227 is located between the shut-off valve 28 and the humidity control module 41. The sucked-in ambient air is thus passed through the humidity control module 41. In the seventh operating mode M7, the humidity control module 41 is inactive and can be passively flowed through by the sucked-in ambient air. The ambient air can absorb moisture in the humidity control module 41. The ambient air then flows through the inspiratory branch 1 and the expiratory branch 2.The Y-piece 93 is closed on the patient side in the seventh operating mode M7. Ambient air can also flow through the first check valve 21, the blower 3, the inspiratory flow sensor 17, the hose system 92, the second check valve 22, the PEEP valve 30, the expiratory flow sensor 18, and / or the drain valve 27, whereby the ambient air can absorb moisture and discharge it via the outlet 14-A. In the seventh operating mode M7, the drain valve 26 is pressurized to a low working pressure and opens the third line 14iii. The APL valve 29 is pressurized to a higher working pressure than the drain valve 26 and thus blocks the second line 14ii. Due to the low working pressure of the drain valve 26, the moisture-saturated ambient air is discharged via the third line 14iii to the outlet 14-A and into the environment, bypassing the APL valve 29.Figure 4 shows a schematic structure of the device in a second exemplary embodiment. The exemplary embodiment according to Figure 4 corresponds in its essential structure to that of the exemplary embodiment according to Figure 1, but can comprise at least the at least one mechanical separation means 60. The separation means 60 can be designed as a mechanical CO2 absorber 60. The CO2 separation can take place mechanically via at least one diffusion filter 61, as described further below with regard to Figure 4. The mechanical separation means 60 can be comprised alternatively or in addition to the chemical separation means 40. However, the device 100 preferably comprises either the chemical separation means 40 (see Figure 1) or the mechanical separation means 60 (see Figure 4). The mechanical separation means 40 can be arranged in or on the breathing gas line 4. The mechanical separation means 40 can be arranged downstream of the patient interface.The mechanical separating means 40 is preferably arranged in the expiratory branch 2 of the respiratory gas line 4. The mechanical separating means 40 can be arranged downstream of the multi-gas sensor 20. The mechanical separating means 40 can be arranged downstream of the expiratory pressure sensor 16. P580 The mechanical separating means 40 can be arranged upstream of the conduction system 14. The mechanical separating means 40 can be arranged upstream of the PEEP valve 30. The mechanical separating means 40 can be arranged upstream of the junction of the bypass 75 into the expiratory branch 2. The mechanical separating means 40 can be arranged upstream of the second safety valve 22. In the specific exemplary embodiment according to Figure 3, the mechanical separating means 40 can be arranged between the junction of the bypass 75 into the expiratory branch 2 and the patient interface.The device 100 in the exemplary embodiment according to Figure 4 can comprise further additional elements compared to the exemplary embodiment according to Figure 1, which enable the functioning of the device 100 with the mechanical separating means 60 or at least positively influence it. The device 100 in the exemplary embodiment according to Figure 4 can also comprise fewer elements than the exemplary embodiment according to Figure 1. For example, the exemplary embodiment according to Figure 4 can be designed without a chemical absorber 40. Thus, the humidity control module 41 no longer needs to be included. In alternative embodiments, however, the device 100 can also be equipped with a mechanical separating means 60 and with a humidity control module 41 (not shown).The device 100 can comprise at least one sweep gas module 70 and at least one sweep gas supply line 71 for providing, introducing, discharging, and controlling sweep gas 64 for the mechanical separating means 60 (see also further below, Figure 5). The sweep gas module 70 is configured and designed to provide sweep gas 64 for the separating means 60. Sweep gas 64 can be introduced and / or discharged into the mechanical separating means 60 in a controlled manner via the sweep gas supply line 71. For this purpose, the sweep gas supply line 71 is pneumatically connected to the separating means 60. The device 100 can also comprise at least one bypass 75. The bypass 75 can be designed as a gas-conducting line and be pneumatically connected to the breathing gas line 4. At least a portion of the breathing gas mixture 5 can be conducted via the bypass 75.The bypass 75 can permit or enable a bypass flow S1, the direction of which is indicated in Figure 4 by a dashed line. In the exemplary embodiment according to Figure 4, the bypass flow S1 can exist in addition to the main flow S of the respiratory gas mixture 5. The bypass 75 is configured to at least temporarily establish a respiratory gas-conducting connection from the inspiratory branch 1 to the expiratory branch 2 such that a second circuit K2 is formed, in which the respiratory gas mixture 5 can be conducted. The second circuit K2 can correspond at least partially to the first circuit K1. In this case, the bypass 75 is arranged such that the connection 93 for a patient interface is not arranged in the second circuit K2. The connection 93 for a patient interface is arranged only in the first circuit K1. Furthermore, the bypass 75 is arranged such that the mechanical separating means 60 is not arranged in the second circuit K2.The mechanical separating means 60 is arranged only in the first circuit K1. P580 The respiratory gas mixture 5 can be conducted in the first circuit K1 with the main flow S and additionally in the second circuit K2 with the bypass flow S1. Bypass flow S1 and main flow S of the respiratory gas mixture 5 can run parallel at least in some regions. At least one valve 76 can be arranged in the bypass 75. The valve 76 can be designed as a check valve. The valve 76 can then at least specify the direction of the bypass flow S1. The valve 76 can in particular prevent the bypass flow S1 from flowing back into the inspiratory branch 1 of the respiratory gas line 4. In some embodiments, the valve 76 can be designed as a simple check valve or as a loaded check valve (not shown). In preferred embodiments, the valve 76 can be designed as a lockable check valve and thus as a bypass shut-off valve 76.In the specific exemplary embodiment according to Figure 4, the bypass shut-off valve 76 can, for example, be designed as a lockable check valve with a solenoid coil. The bypass shut-off valve 76 can thus preferably be operated in at least two settings: In a first setting, for example in a rest position, the bypass shut-off valve 76 can allow flow in one direction and block flow in one direction. In this first setting, the bypass shut-off valve 76 can act as a simple check valve. In a second setting, for example in an active position, the bypass shut-off valve 76 can block flow in both directions. The active position of the valve 76 can be established, for example, by energizing the solenoid coil. The bypass 75 can branch off in the inspiratory branch 1. The bypass 75 can open into the expiratory branch 2. The bypass 75 can branch off between the blower 3 and the patient interface 91.The bypass 75 can preferably branch off between the blower 3 and the feed point 211 of the first O2 flush supply line 11i. In the specific exemplary embodiment according to Figure 4, the bypass 75 can branch off, for example, between the inspiratory flow sensor 17 and the feed point 211 of the first O2 flush supply line 11i. To prevent backflow from the oxygen module 10 into the bypass 75 and / or the blower 3, at least one further check valve, namely a third safety valve 77, can advantageously be included. The third safety valve 77 can be arranged in the breathing gas line 4 between the branch of the bypass 75 and the feed point 211 of the first O2 flush supply line 11i. For example, the third safety valve 77 is designed as a simple check valve. In some embodiments, it is also conceivable that the third safety valve 77 is designed as a spring-loaded check valve.The bypass 75 can flow back into the breathing gas line 4 between the patient interface 91 and the blower 3. The bypass 75 can thus flow into the expiratory branch 2. The bypass 75 can preferably flow back into the breathing gas line 4 between the separating means 60 and the blower 3. The bypass 75 can in particular flow back into the breathing gas line 4 between the separating means 60 and the anesthetic module 8. In the specific embodiment according to Figure 4, the bypass 75 can, for example, flow into the expiratory P580 branch 2 of the breathing gas line 4 after the second safety valve 22. The second safety valve 22 can then prevent the bypass flow S1 from running counter to the main flow S1 and in the direction of the separating means 60. The bypass 75 can branch off from the breathing gas line 4 after the blower 3 and rejoin the breathing gas line 4 at least before the anesthetic module 8. The bypass flow S1 can be generated through the bypass 75.In the exemplary embodiment according to Figure 4, the bypass flow S1 is not directed to the patient 90. In the exemplary embodiment according to Figure 4, the bypass flow S1 is not generated at the inlet of the oxygen module 10. In the exemplary embodiment according to Figure 4, the bypass flow S1 is not directed through the separating means 60. The second safety valve 22 prevents the bypass flow S1 from flowing in the direction of the separating means 60. In this embodiment, the bypass flow S1 runs at least from the blower 3 through the bypass 75 to the anesthetic module 8 and back to the blower 3. Thus, a second gas circuit can be formed through the bypass 75 with the bypass flow S1, which can exist alternatively or in addition to the gas circuit of the main flow S. The bypass flow S1 and the main flow S can run parallel in the breathing gas line 4, at least in some areas.Bypass flow S1 and main flow S cannot, at least in some areas, run in a common line. With liquid dosing, one or more anesthetics VA are held under pressure and therefore in liquid form in the anesthetic module 8 and / or the anesthetic supply line 9 and from there injected into the breathing gas line 4. Upon reaching the breathing gas line 4, the anesthetics VA evaporate and mix with the breathing gas mixture 5. Because a permanent gas flow exists in the evaporation element 8a due to the bypass flow S1, the anesthetics VA can mix particularly advantageously with the breathing gas mixture 5. With this type of liquid dosing, a prior mixing of anesthetics VA and fresh gas is no longer necessary. Thus, a mixing chamber separate from the breathing gas line 4 for a separate mixture of fresh gas or breathing gas and anesthetics VA is no longer required.The liquid dosing enables very precise, economical dosing of anesthetics VA, which is independent of the supply of fresh gas and / or oxygen. The evaporation element 8a can replace a conventional mixing chamber. Figure 5 shows a schematic structure of the mechanical separation means 60 with diffusion filter 61. The mechanical separation means 60 can in principle be designed as a two-chamber system 65 and comprise at least one first chamber 62 and at least one second chamber 63. The first chamber 62 and the second chamber 63 are separated from one another by the at least one diffusion filter 61. The mechanical separation means 60 can comprise a plurality of such two-chamber systems 65, which can run parallel to one another. In one exemplary embodiment, the two-chamber systems 65 are designed as gas-conducting tubes. The tubes may have a diameter of 0.1 mm to 10 mm, preferably from P580 0.1 mm to 5 mm, particularly preferably from 0.3 to 1 mm.For example, the tubes of the dual-chamber systems 65 have a diameter of 0.5 mm. For example, the mechanical separating means 60 comprises several thousand such tubes (not shown). The total diameter of the tubes and thus of the separating means 60 advantageously corresponds to the diameter of the breathing gas line 4. The diffusion filter 61 can be designed as a semipermeable membrane and have pores 65 configured such that only molecules below a certain size can pass through the membrane. The diffusion filter 61 is preferably made of a chemically inert material. The diffusion filter 61 is characterized by being cleanable, disinfectable, and reusable. For example, the diffusion filter 61 is made of plastic, ceramic, glass, metal, or combinations thereof.In exemplary embodiments, the material of the diffusion filter 61 is selected from the group consisting of polysulfone, polyethersulfone, cellulose, cellulose ester, cellulose acetate, cellulose nitrate, regenerated cellulose, silicone, polyamide, polyamideimide, polyamide urea, polycarbonate, ceramic, stainless steel, silver, silicon, zeolite, aluminosilicate, polyacrylonitrile, polyethylene, polypropylene, polytetrafluoroethylene, polyvinylidene fluoride, polyvinyl chloride, and polypiperazinamide. Combinations of these materials are also possible. The breathing gas mixture 5 can be directed in the direction of the main flow S through the first chamber 62 of the two-chamber system 65. Expiratory breathing gas 5 is preferred. exsp passed through the separating agent 60 to separate CO2. The expiratory breathing gas 5 exspcan be passed through the first chamber 62. For this purpose, the separation means 60 is preferably arranged in the expiratory branch 2. It is particularly advantageous if the separation means 60 is arranged very close to the patient 90. In some embodiments, the separation means 60 can alternatively or additionally also be configured to separate nitrous oxide (N2O). The separation of N2O can be carried out in a manner equivalent to the separation of CO2 described herein. A sweep gas 64 can be passed through the second chamber 63 of the two-chamber system 65. The sweep gas 64 is configured to scrub at least CO2 from the respiratory gas mixture 5. The sweep gas 64 is passed through the second chamber 63 with a sweep gas flow S2, the direction of which is indicated in Figure 5 by an arrow S2. The direction of the sweep gas flow S2 is preferably selected opposite to the direction of the main flow S of the breathing gas mixture 5, which is indicated here with an arrow S.The device 100 can comprise the at least one sweep gas module 70 and the at least one sweep gas supply line 71. Sweep gas 64 can be introduced into the separating agent 60 via the sweep gas supply line 71. Sweep gas 64 can be introduced, in particular, into the second chamber 63 of the separating agent 60 via the sweep gas supply line 71. Sweep gas 64 can also be discharged from the second chamber 63 via the sweep gas supply line 71. For this purpose, the sweep gas supply line 71 is pneumatically connected to the second chamber 63. The sweep gas supply line 71 can supply and / or discharge sweep gas 64 to the separating agent 60. P580 In some embodiments, the sweep gas 64 can be obtained from compressed gas cylinders. The sweep gas 64 can alternatively or additionally be supplied via the oxygen module 10 and / or the fresh gas module 6. The control device 101 and / or the sweep gas module 70 can predetermine the composition of the sweep gas 64.The control device 101 and / or the sweep gas module 70 can predetermine a flow and / or volume of the sweep gas 64. The sweep gas module 70 can be connected to the control device 101 and / or controlled by the control device 101. The control device 101 and / or the sweep gas module 70 can also be configured to prevent or terminate the sweep gas flow, so that the device 100 can also be operated without the sweep gas 64. This is advantageous, for example, when the device 100 is operated in a semi-open circuit, for example in TIVA mode. Without a sweep gas flow in the second chamber 63, the separating agent 60 is inactive. The breathing gas mixture 5 can then flow through the mechanical separating agent 60 without gas components such as CO2 being separated. The sweep gas 64 is designed in such a way that the concentration of CO2 is significantly lower than that of the breathing gas mixture 5.The sweep gas 64 is configured such that the CO2 concentration of the sweep gas 64 when introduced into the second chamber 63 is below 20%, preferably below 10%, particularly preferably below 5%. Ideally, the CO2 concentration of the sweep gas 64 when introduced into the second chamber 63 is 0%. The sweep gas 64 is also advantageously free of anesthetics VA. The sweep gas 64 is also configured such that the concentration of oxygen O2 and / or nitrogen N2 can preferably be at least equal to or higher than that of the expiratory respiratory gas mixture 5. The O2 concentration of the sweep gas 64 when introduced into the second chamber 63 is above 0%, preferably above 20%, particularly preferably above 40%. For example, the O2 concentration of the sweep gas 64 when introduced into the second chamber 63 can be 47%. The N2 concentration of the sweep gas 64 when introduced into the second chamber 63 is above 0%, preferably above 20%, particularly preferably above 40%.For example, the N2 concentration of the sweep gas 64 when introduced into the second chamber can be 6353%. Due to a concentration gradient across the diffusion filter 61, the breathing gas mixture 5 can be separated in the mechanical separation medium 60. The nature of the diffusion filter 61 allows particularly small molecules to be separated out. In particular, molecules consisting of a few atoms, for example fewer than 5 atoms, can be separated out. In particular, CO2 molecules can be separated out. Oxygen O2 and nitrogen N2 can also pass through the diffusion filter 61. Anesthetics VA, which have more than 5 atoms, however, cannot pass through the diffusion filter 61 and remain in the breathing gas mixture 5. P580 The initial concentration of the gas components of the sweep gas 64 can be used to control which gas components are filtered out of the breathing gas mixture 5 and which gas components remain in the breathing gas mixture 5.With regard to carbon dioxide CO2, the following scenario can be advantageous: If a sweep gas 64 is introduced into the second chamber 63 that contains a lower CO2 concentration than the breathing gas mixture 5 in the first chamber 62, CO2 can be filtered out of the breathing gas mixture 5. This allows CO2 to be removed from the breathing gas mixture 5. This makes the breathing gas mixture 5 suitable for inspiration again. The breathing gas mixture 5 can thus be conducted in a closed circuit. With regard to oxygen O2 and / or N2, the following scenarios can be advantageous: If a sweep gas 64 is introduced into the second chamber 63 that contains the same and / or a higher O2 concentration than the breathing gas mixture 5 in the first chamber 62, O2 can remain in the breathing gas mixture 5. If the breathing gas mixture 5 is then used again for inspiration, it contains oxygen at the concentration of the sweep gas 64.If sweep gas 64 is introduced into the second chamber 63, which contains a lower O2 concentration than the breathing gas mixture 5 in the first chamber 62, O2 can be filtered out of the breathing gas mixture 5. This can offer the advantage that oxygen that was temporarily made available to the patient in excess can be reused and / or that the breathing gas mixture 5 can be reused despite a temporary O2 excess. The retention or removal of N2 and / or N2O from the breathing gas mixture 5 can also be regulated in this way according to the same principle. The gas concentrations of the introduced sweep gas 64 can be controlled via the control device 101 and / or the sweep gas module 70. The volume and / or flow of the introduced sweep gas 64 can also be controlled via the control device 101 and / or the sweep gas module 70. In some embodiments, the sweep gas flow through the separating means 60 is constant.In some embodiments, the sweep gas flow can also be adaptively adjusted to the ventilation and thus, for example, to the tidal volume or the minute volume. Control is preferably carried out automatically by specifications and values ​​stored in the control device 101, but can also be set manually by medical personnel if necessary. In some embodiments, the sweep gas flow and / or the sweep gas volume corresponds to the flow and / or volume of the respiratory gas mixture 5. In advantageous exemplary embodiments, the sweep gas 64 is introduced into the separating agent 60 in excess of the respiratory gas mixture 5. For example, the same amount of sweep gas 64 is introduced into the second chamber 63 per breath as the respiratory gas mixture 5 flows into the first chamber 62. Advantageously, more sweep gas 64 is introduced into the second chamber 63 per breath than the respiratory gas mixture 5 flows into the first chamber 62.P580 The ratio of the amount of sweep gas 64 to breathing gas mixture 5 can be at least 1:1, preferably at least 1.2:1, particularly preferably at least 1.4:1. For example, the ratio of sweep gas 64 to breathing gas mixture is 51.5:1 or more. A ratio of sweep gas 64 to breathing gas mixture 5 of at least 2:1 or at least 5:1 is also conceivable. Typically, the sweep gas is dosed such that it is 1.2 to 1.5 times the minute volume. The ratio of the amount of sweep gas 64 to breathing gas mixture 5 can be variably adjustable and adaptively adapted to the respective ventilation situation. Preferably, the sweep gas flow can be based on the CO2 concentration of the expiratory breathing gas 5. exspbe adjustable. The mechanical separating means 60 with the sweep gas module 70 offers the advantage that the CO2 concentration of the respiratory gas mixture 5 can be adjusted quickly, precisely, highly dynamically, and cost-effectively. Since a high CO2 concentration stimulates the patient to breathe spontaneously, the CO2 concentration can, for example, influence the weaning of the patient from mechanical ventilation. The sweep gas supply line 71 can be constructed correspondingly to the supply lines according to Figure 2. The sweep gas supply line 71 can also have more or fewer elements than the supply lines according to Figure 2. The sweep gas supply line 71 can comprise at least one valve 88i for metering sweep gas 64. The sweep gas module 70 can be supplied with gas in particular by the fresh gas module 6 and / or the oxygen module 10.The sweep gas supply line 71 can then comprise at least one bistable switching valve 87 and / or at least one bistable needle valve 88 as well as at least one flow sensor 85, via which the sweep gas introduction into the separating agent 60 is controlled (not shown). The advantages of the mechanical separating agent 60 compared to a chemical separating agent 40 are as follows: - Significant savings in anesthetics VA, since these are not filtered out, but remain in the circuit and thus in the breathing gas mixture 5 - The mechanical separating agent 60 is chemically neutral orinert - This means that no heat is generated and no water is formed during CO2 separation - This means that no hazardous chemical waste is produced - The mechanical release agent 60 is designed for very long periods of use (up to one year) and the release agent 60 rarely needs to be replaced - The release agent 60 can therefore be replaced by a service employee - Due to the less frequent replacement, there is a lower risk of contamination - The release agent 60 can optionally be reused after processing - Due to its longevity, the release agent 60 is more cost-effective than chemical release agents 40 P580 embodiments with a mechanical release agent 60 and a bypass 75 offer many advantages. The bypass 75 can be used to provide a permanent gas flow (byflow) in the breathing gas line 4, at least in sections.In particular, the bypass 75 can provide a permanent gas flow in the region of the respiratory gas line 4 into which the anesthetic supply line 9 opens. In particular, the bypass 75 can provide a permanent gas flow in the evaporation element 8a. Because a permanent flow (byflow) of the respiratory gas mixture 5 prevails in the evaporation element 8a, the anesthetics VA can be introduced and / or mixed into the respiratory gas mixture 5 particularly advantageously via a liquid metering device. The advantage of embodiments with at least one bypass 75 is that the byflow is not conducted through the entire system. The byflow can be limited to the second circuit K2. The bypass 75 prevents the byflow from flowing to the patient. The bypass 75 also prevents the byflow from flowing through the mechanical separating means 60.This offers the particular advantage that the expiratory breathing gas 5exsp is introduced undiluted into the separation medium 60. This significantly increases the efficiency of the mechanical separation medium 60. Firstly, due to the lack of byflow in the separation medium 60, the CO2 concentration upon introduction into the separation medium 60 is high, which has a beneficial effect on CO2 separation. Secondly, the residence time of the expiratory breathing gas 5exsp in the separation medium 60 is increased. In the expiratory plateau, there is no gas flow in the separation medium 60, which promotes the diffusion of CO2 into the sweep gas. The bypass shutoff valve 76 can be used to establish or block the respiratory gas-conducting connection of the bypass. Blocking the bypass 75 can be advantageous if the concentration of the anesthetic VA or that of the oxygen in the respiratory gas mixture 5 in the inspiratory branch 1 is to be changed quickly.It must be noted that the efficiency of the diffusion absorber is reduced during this time. The device 100 of the second exemplary embodiment can be operated in the different operating modes M1, M2, M3, M4, M5, M6, M7 described for Figures 1A-1F. The operating modes can be set manually and / or automatically specified by the control device 101. In the second exemplary embodiment, the device 100 can also be used to administer, direct, and, in particular, specifically divert volatile anesthetics (VA) for disposal or reuse. In the second exemplary embodiment, the device 100 can also be used to perform ventilation without volatile anesthetics (VA). The operating modes in the second exemplary embodiment can be implemented, for example, via the settings of the valves 25, 26, 27, 28, 29 and optionally also via the settings of the blower 3 and / or the pressure relief valve 30 as well as via the actuation of the reservoir 12.The operating modes in the second embodiment can also be influenced, in particular, by adjusting the bypass shutoff valve 76. The operating modes M1 to M7 of the second embodiment largely correspond to the operating modes of the first embodiment described above. However, there are differences, particularly due to the bypass and the P580-different separating means 40, 60, which are described below. In the first operating mode M1 for manual ventilation with the application of volatile anesthetics, the reservoir 12 also supplies the delivery energy for the respiratory gas mixture 5 and thus the respiratory energy in the second embodiment. The inspiratory respiratory gas 5. insp is delivered to the patient via the inspiratory branch 1 and the expiratory breathing gas 5 exspis carried away from the patient via the expiratory branch 2. The fresh gas switching valve 32 and the O2 flush switching valve 31 are in their basic positions. The fresh gas can thus be introduced downstream of the check valve 21. The optional oxygen introduction via the O2 flush 10 can be introduced downstream of the blower 3 and upstream of the safety valves 23, 24. The anesthetic module 8 is active, so that volatile anesthetics VA can be introduced into the evaporation element 8a via the anesthetic supply line 9 and added to the breathing gas mixture 5. The expiratory breathing gas 5 exsp can be diverted away from the patient via the expiratory branch 2. In the expiratory branch 2, the expiratory breathing gas 5 passes exspthe mechanical separating agent 60. The sweep gas module 70 is active in the first operating mode M1 and directs sweep gas into the separating agent 60. As a result, the separating agent 60 is also active and can at least CO2 from the expiratory breathing gas 5 exsp The expiratory breathing gas 5 exspcan then pass through the active PEEP valve 30, which regulates to an individual exhalation pressure. The breathing gas mixture 5 can then also take two different paths in the second embodiment: On the one hand, the breathing gas mixture 5 can be directed in the direction of the main flow S in the circuit, since the shut-off valve 28 is subjected to a low working pressure and releases the breathing gas line 4. In contrast to the first embodiment, the breathing gas mixture 5 does not have to pass through a chemical CO2 absorber 40 and thus also no humidity control module 41. Since the CO2 has already been separated by the mechanical separating agent 60, the breathing gas mixture 5 can be circulated and fed back to the patient. However, it is also conceivable that the second embodiment includes a humidity control module 41 in order to remove and / or add moisture to the circuit (not shown).On the other hand, the breathing gas mixture 5 can also be diverted from the circuit, at least in part, via the APL valve 29 through the discharge system 14. In contrast to the first exemplary embodiment according to Figure 1, in the second exemplary embodiment according to Figure 4, a second circuit with a bypass flow S1 can exist. The bypass 75 is set up and designed to allow the second circuit when required. In the first operating mode M1, the bypass shut-off valve 76 is subjected to a low working pressure or is in a rest position. In the first operating mode M1, the bypass shut-off valve 76 can act as a simple check valve without the action of the solenoid coil. In the first operating mode M1, the bypass shut-off valve 76 releases the bypass 75 in the direction of the bypass flow S1. P580 The bypass 75 offers the advantage of creating a second circuit for the breathing gas mixture 5 that is not directed to the patient.In the second circuit, a nearly constant flow can be generated that is independent of the patient's breathing phases. This nearly constant flow then also flows through the evaporation element 8a and promotes the liquid dosing of the anesthetics. Furthermore, by creating the second circuit, the bypass 75 offers the advantage that a lower flow is passed through the separating agent 60, thus saving sweep gas 64. In the second operating mode M2 ​​for mechanical ventilation with the application of volatile anesthetics, the blower 3 also supplies the delivery energy for the respiratory gas mixture 5 and thus the respiratory energy in the second exemplary embodiment. The reservoir 12 serves as a storage device for at least part of the respiratory gas mixture 5. The fresh gas switching valve 32 and the O2 flush switching valve 31 are in the basic position.Fresh gas is introduced into the breathing gas line 4 via the first fresh gas supply line 7i and delivered to the patient by the blower 3. The anesthetic module 8 is active. In the second exemplary embodiment, the sweep gas module 70 and thus also the separating agent 60 are also active in operating mode M2, so that at least CO2 can be separated and the breathing gas mixture 5 can at least partially remain in the circuit. When the blower 3 is operating, the blower 3 can draw in the breathing gas mixture 5 (enriched with fresh gas and / or anesthetics) from the breathing gas line 4, so that at least a partial negative pressure can arise upstream of the blower 3. This allows breathing gas mixture 5 to be drawn in from the reservoir 12. If the negative pressure persists, for example if the fresh gas module 6 and / or the reservoir 12 provides too little volume, the inlet valve 27 can open and supply ambient air to the breathing gas line 4.The feed point for ambient air 227 can be arranged in the breathing gas line 4. In some embodiments, the feed point for ambient air 227 can also be arranged in the reservoir line 13. For example, in the second embodiment according to Figure 4, the feed point for ambient air 227 can be located in the reservoir line 13. In this specific embodiment, the feed point for ambient air 227 can be located between the reservoir 12 and the reservoir feed point 213 in the breathing gas line 4. As a result, ambient air can be fed directly into the breathing gas line 4 via the reservoir line 14. The valves 26, 28, 29 are switched in the second operating mode M2 ​​such that the breathing gas mixture 5 essentially circulates along the main flow direction S. However, in contrast to the first embodiment, the breathing gas mixture 5 does not pass through a chemical separating agent 40 in the second embodiment.A humidity control module 41 can be included optionally, but may be dispensed with due to the missing chemical absorber 40. The bypass shut-off valve 76 of the second exemplary embodiment is in its rest position in the second operating mode M2. Thus, the bypass 75 is active and can be flowed through in the direction of the bypass flow S1. In the operating mode M2 ​​of the second exemplary embodiment, there is thus a second circuit for the respiratory gas mixture 5, as in the first operating mode M1. P580 The third operating mode M3 for manual ventilation without the application of volatile anesthetics can be very similar in the first and second exemplary embodiments. The respiratory gas mixture 5 can, for example, be guided in the same or a similar way. This can be achieved in particular by the bypass 75 and / or the sweep gas module 70 and / or the mechanical separating means 60 of the second exemplary embodiment being inactive in the third operating mode M3.In the third operating mode M3, the bypass shutoff valve 76 can be subjected to a high working pressure and / or be in an active position. In the third operating mode M3, the bypass shutoff valve 76 can act as a shutoff valve under the influence of the solenoid coil. In the third operating mode M3, the bypass shutoff valve 76 can shut off the bypass 75 such that the bypass 75 is inactive. In the third operating mode M3, the active bypass shutoff valve 76 prevents the second circuit for the breathing gas mixture 5. In the third operating mode M3, the sweep gas module 70 can be inactive. An inactive sweep gas module 70 does not pump sweep gas 64 into the mechanical separating means 60. Because there is no sweep gas flow in the separating means 60, the mechanical separating means 60 is inactive. The separating means 60 can flow passively. The expiratory breathing gas mixture 5. exspcan flow through the separating agent 60 in the third operating mode M3 without CO2 being separated. Since volatile anesthetics VA are generally not added to the breathing gas mixture 5 in the third operating mode M3, the expiratory breathing gas 5 exspby blocking the shut-off valve 28 and opening the drain valve 26 as described above in a semi-open circuit. The fourth operating mode M4 for automatic ventilation without the application of volatile anesthetics can also be very similar in the first and second exemplary embodiments. The breathing gas mixture 5 can, for example, be conducted in the same or a similar way. This can be achieved in particular by the bypass 75 and / or the sweep gas module 70 and / or the mechanical separating means 60 of the second exemplary embodiment being inactive in the fourth operating mode M4 as well. As in the first exemplary embodiment, in the second exemplary embodiment too, to implement the fourth operating mode M4, the blower 3 is active and the overflow valve 25 is pressurized with a low working pressure to activate the first line 14i. In addition, the shut-off valve 28 is active to prevent the circuit and the drain valve 26 is open to activate the third line 14iii.In contrast to the first exemplary embodiment, in the second exemplary embodiment, ambient air can be fed directly into the reservoir line 13 through the inlet valve 27 if necessary. The device 100 according to the second exemplary embodiment can be operated in the fifth operating mode M5 for manual ventilation in a battery and / or error mode. The fifth operating mode M5 can be similar in the first and second exemplary embodiments. Emergency supply via manual ventilation can be ensured by the reservoir 12 providing the pumping energy for the respiratory gas mixture 5 and fresh gas being fed into the respiratory gas line 4 at a constant flow via the first fresh gas supply line 7i. The fresh gas supply line 7i is open when de-energized.The flow path of the respiratory gas basically runs as in the first embodiment, from the reservoir 12 via the inspiratory branch 1 to the patient and from the patient via the expiratory branch 2 in the direction of the main flow S in the circuit and / or via the APL valve 29 and the second line 14ii to the outlet 14-A. In contrast to the first embodiment, in the second embodiment, the bypass 75 can be active. The bypass shutoff valve 76 can act as a simple check valve when de-energized. The respiratory gas mixture 5 can then additionally be conducted at a relatively constant flow in the second circuit. In the fifth operating mode M5, the sweep gas module 70 is active when de-energized, so that sweep gas 64 can be introduced into the mechanical separating means 60 and CO2 can be separated. When de-energized, the sweep gas supply line is open.The valve 88i for dosing sweep gas 64 can be configured to set the sweep gas dosage, without power, to 1.2 to 2 times the last set minute volume, preferably to 1.5 times. The advantage of the second embodiment is that the mechanical CO2 separation does not result in any significant moisture development. Furthermore, CO2 separation is ensured by the sweep gas module 70, which is active without power. The sixth operating mode M6 for a constant flow (HFOT), with or without the application of volatile anesthetics, can be very similar in the first and second embodiments. The breathing gas mixture 5 can, for example, be guided in the same or similar manner. This can be achieved in particular by the bypass 75 of the second embodiment being inactive in the sixth operating mode M6. The bypass shutoff valve 76 can be subjected to a high working pressure and / or be in an active position in the sixth operating mode M6.Thus, the bypass shutoff valve 76 can deactivate or block the bypass 75. An inactive bypass 75 in the sixth operating mode M6 means that the respiratory gas mixture 5 cannot pass through the bypass 75. The respiratory gas mixture 5 is then conducted in an open circuit as described above. The respiratory gas mixture 5 is conducted to the patient via the inspiratory branch 1 so that the patient can be supplied with a constant flow. The seventh operating mode M7 can be implemented in the second exemplary embodiment similarly to the first exemplary embodiment. The device 100 according to the second exemplary embodiment can thus also be operated in a service mode. The seventh operating mode M7 is particularly designed and configured to remove condensed moisture from the device 100.Even though the advantageous mode of operation of the mechanical release agent 60 compared to the chemical release agent 40 generally results in less moisture condensing in the device 100, it is possible to implement the seventh operating mode M7 to remove condensed moisture. In the seventh operating mode M7, when the blower 3 is operating and the fresh gas module 6 is inactive, ambient air can be pumped via the inlet valve 27 into the reservoir line 13 and from there into the breathing gas line 4. The gases can be discharged again via the outlet 14-A. In the seventh operating mode M7, the bypass 75 can be active and flowed through. It is also conceivable that the bypass 75 is deactivated by activating the bypass shutoff valve 76. During operation in the seventh operating mode M7, the sweep gas module 70 can be inactive and the mechanical release agent 60 can flow passively.Although the present invention has been described in detail using the exemplary embodiments, it will be obvious to those skilled in the art that the invention is not limited to these exemplary embodiments. Rather, modifications are possible in such a way that individual features are omitted or other combinations of the described individual features can be realized, provided that the scope of protection of the appended claims is not exceeded. The present disclosure includes all combinations of the presented individual features. List of reference numerals CO2 Carbon dioxide O2 Oxygen K1 First circuit K2 Second circuit M1 First operating mode M2 ​​Second operating mode M3 Third operating mode M4 Fourth operating mode M5 Fifth operating mode M6 Sixth operating mode M7 Seventh operating mode N2 Nitrogen P1 First pressure P2 Second pressure P insp Inspiratory pressure P exspExpiratory pressure PEEP positive end-expiratory pressure S Main flow S1 Bypass flow S2 Sweep gas flow S3 Outlet flow VA Volatile anesthetics ZGA Central gas system 1 Inspiratory branch 2 Expiratory branch 3 Blower unit / blower 3a Blower outlet 4 Breathing gas line 5 Breathing gas mixture 5 insp Inspiratory breathing gas 5 exspExpiratory breathing gas 6 Fresh gas module 7 Fresh gas supply line P580 7i First fresh gas supply line 7ii Second fresh gas supply line 8 Anesthetic module 8a Evaporative element 9 Anesthetic supply line 10 Oxygen module / O2 flush 11 O2 flush supply line 11i First O2 flush supply line 11ii Second O2 flush supply line 12 Reservoir 13 Reservoir line 14 Scavenging system 14i First line 14ii Second line 14iii Third line 14-A Outlet 15 Inspiratory pressure sensor 16 Expiratory pressure sensor 17 Inspiratory flow sensor 18 Expiratory flow sensor 19 Sensor 20 Multigas sensor 21 First check valve 22 Second check valve 23 First safety valve 24 Second safety valve 25 Overflow valve 26 Drain valve 27 Inlet valve 28 Shut-off valve 29 APL valve 30 Pressure control valve (PEEP valve) 31 O2 flush switching valve 32 Fresh gas switching valve 35 Hand bag 39 Pressure sensor 40 Chemical release agent 41 Humidity control module 43 Nitric oxide module 44Nitric oxide supply line 60 Mechanical separator 61 Diffusion filter 62 First chamber 63 Second chamber 64 Sweep gas 65 Dual-chamber system 70 Sweep gas module 71 Sweep gas supply line 75 Bypass 76 Bypass shut-off valve 77 Third safety valve 80 Pressure regulator / pressure reducer P580 81 Stenosis 82 Filter 83 Pressure relief valve 84 Pressure sensor 85 Flow sensor 86 Check valve 87 Switching valve 88 Dosing valve 89 Supply source 90 Patient 91 Patient interface 92 Tube system 93 Connection for a patient interface 94 Filter 95 Sensor 100 Device 101 Control unit 102 Storage unit 103 Primary power source 104 Secondary power source 110 Ventilation-specific parameters 111 Patient parameters 207 Fresh gas injection point 209 Anesthetic injection point 211 O2 flush injection point 213 Reservoir injection point 214 Connection point (scavenging system) 227 Ambient air injection point 800 Tank 810 Pressure supply unit 811 Loading valve 812 Unloading valve 813 Switching valve 820Receiving unit 821 Receiving bay 830 Selection unit 831 Selection valve 840 Dosing unit 841 Dosing valve 850 Safety unit 851 First valve (safety valve) 852 Second valve (safety valve) 860 Temperature unit 861 Heating element

Claims

P580 Patent Claims 1. Device (100) for supplying respiratory gas, comprising at least one respiratory gas line (4) for conducting a respiratory gas mixture (5), wherein the respiratory gas line (4) comprises at least one outlet (14-A) via which the respiratory gas mixture (5) can be at least partially, at least temporarily, discharged, wherein the respiratory gas line (4) comprises an inspiratory branch (1) designed to conduct respiratory gas to a connection (93) for a patient interface, wherein the respiratory gas line (4) comprises an expiratory branch (2) designed to conduct respiratory gas between the connection (93) for a patient interface and the outlet (14-A), characterized in that at least one check valve (28) is arranged in the respiratory gas line (4), which is designed and configured to at least temporarily establish a respiratory gas-conducting connection from the expiratory branch (2) to the inspiratory branch (1). 2.Device (100) according to claim 1, characterized in that the device (100) comprises at least one reservoir (12) for the respiratory gas mixture (5) and at least one fan (3) configured to provide conveying energy for the respiratory gas mixture (5), wherein the reservoir (12) and fan (3) are arranged in or on the inspiratory branch (1).

3. Device (100) according to one of the preceding claims, characterized in that the blocking valve (28) is designed as a check valve and is configured to establish the respiratory gas-conducting connection in a flow direction from the expiratory branch (2) to the inspiratory branch (1).

4. Device (100) according to one of the preceding claims, characterized in that the blocking valve (28) is designed as a blockable check valve and is configured to at least temporarily block the respiratory gas line (4) in both flow directions.Device (100) according to one of the preceding claims, characterized in that the device (100) comprises a control device (101) and at least one power source (103, 104), wherein the shut-off valve (28) is configured to block the respiratory gas line (4) in both flow directions when energized by the at least one power source (103, 104).

6. Device (100) according to one of the preceding claims, characterized in that the shut-off valve (28) is configured to prevent the respiratory gas-conducting connection from the expiratory branch (2) to the inspiratory branch (1) when energized, and / or that the respiratory gas mixture (5) can be completely discharged from the expiratory branch (2) via the outlet (14-A) when energized by the shut-off valve (28).Device (100) according to one of the preceding claims, characterized in that the inspiratory branch (1) and expiratory branch (2) form at least one first circuit (K1) without energizing the shut-off valve (28), in which circuit the respiratory gas mixture (5) can be conducted, wherein the respiratory gas mixture (5) can be at least partially discharged via the outlet (14-A).

8. Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one controllable pressure regulating valve (29, 30) which is configured to regulate an inspiratory pressure (Pinsp) and / or an expiratory pressure (Pexsp), wherein the pressure regulating valve (29, 30) is manually and / or electrically adjustable. P580 9. Device (100) according to claim 8, characterized in that the pressure control valve is designed as an APL valve (29) for controlling the inspiratory pressure (Pinsp), wherein the respiratory gas mixture (5) can be discharged via the outlet (14-A) when the pressure in the respiratory gas line (4) exceeds the inspiratory pressure (Pinsp).

10. Device (100) according to one of claims 8 or 9, characterized in that the APL valve (29) is designed as a controllably loaded check valve, and / or that the APL valve (29) comprises a stepper motor via which the APL valve (29) can be adjusted, wherein the valve position of the APL valve (29) is set and / or maintained under current supply.

11. Device (100) according to one of claims 8 to 10, characterized in that the valve position of the APL valve (29) remains at the last set value without current supply.The device (100) according to claim 8, characterized in that the pressure control valve is designed as a valve (30) for regulating the expiratory pressure (Pexsp), wherein the pressure control valve (30) is arranged in the expiratory branch (2), wherein the pressure control valve (30) is configured in particular to regulate an end-expiratory expiratory pressure (PEEP).

13. The device (100) according to one of claims 8 or 12, characterized in that the pressure control valve (30) is configured to passively regulate to a preset expiratory pressure (Pexsp) without energization, wherein the preset expiratory pressure (Pexsp) of the pressure control valve (30) is 3 hPa to 10 hPa, for example, 5 hPa.Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one anesthetic supply line (9) for introducing volatile anesthetics (VA) into the breathing gas line (4), wherein the breathing gas line (4) is designed such that a first pressure (P1) is present in the breathing gas line (4) during operation of the device (100), and wherein the anesthetic supply line (9) is designed such that a second pressure (P2) is present in the anesthetic supply line (9) during operation of the device (100), wherein the first pressure (P1) is lower than the second pressure (P2).

15. Device (100) according to claim 14, characterized in that the second pressure (P2) is at least 100 kPa, preferably at least 180 kPa and / or that the first pressure (P1) is less than 100 kPa, preferably less than 50 kPa, particularly preferably less than 10 kPa, more preferably less than 3 kPa. 16.Device (100) according to one of claims 14 or 15, characterized in that the anesthetic supply line (9) is designed to conduct the volatile anesthetics (VA) in liquid form to the breathing gas line (4), wherein the volatile anesthetics (VA) evaporate at an evaporation rate of 0 to 2 l / min upon introduction into the breathing gas line (4).

17. Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one safety valve (851) which is designed and configured to block the supply of volatile anesthetics (VA), wherein the safety valve (851) is designed as a switching valve which is electrically and / or manually adjustable. P580 18. Device (100) according to claim 17, characterized in that the safety valve (851) is designed as an electrically operated switching valve, wherein the safety valve (851) is configured, without energization, to block the introduction of volatile anesthetics (VA) into the respiratory gas mixture (5).

19. Device (100) according to one of the preceding claims, characterized in that the outlet (14-A) comprises at least one filter (94) positioned such that the respiratory gas mixture (5) discharged via the outlet (14-A) completely passes through the filter (94). 20.Device (100) according to claim 19, characterized in that the filter (94) is an absorbent and / or comprises an absorbent and is designed and configured to absorb at least volatile anesthetics (VA) and / or their metabolites, wherein a double filter system with a first filter (94i) and a second filter (94ii) is arranged at the outlet (14-A), wherein the second filter (94ii) is arranged downstream of the first filter (94i) in the flow direction.

21. Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one sensor (95) arranged in or at the outlet (14-A), wherein the sensor (95) is designed and configured to detect the concentration of volatile anesthetics (VA) and / or their metabolites and to transmit it to the control device (101). 22.Device (100) according to claim 21, characterized in that the sensor (95) is designed to detect the concentration of volatile anesthetics (VA) and / or their metabolites in the flow direction at least upstream and / or downstream of the first filter (92i) and to transmit it to the control device (101), wherein the control device (101) is configured to generate an alarm if the concentration of volatile anesthetics (VA) and / or their metabolites exceeds a limit value.

23. Device (100) according to one of the preceding claims, characterized in that the device (100) comprises a separating means (40, 60) configured to separate at least CO2 from the respiratory gas mixture (5), wherein the separating means is a chemical separating means (40) and / or a mechanical separating means (60). 24.Device (100) according to claim 23, characterized in that the mechanical separating means (60) is arranged in the expiratory branch (2), wherein the mechanical separating means (60) comprises at least one diffusion filter (61) which is designed as a semipermeable membrane and is permeable at least to CO2 molecules and / or is at least impermeable to volatile anesthetics (VA).

25. Device (100) according to one of claims 23 or 24, characterized in that the separating means (60) is designed as a two-chamber system (65) which comprises at least a first chamber (62) and at least a second chamber (63), wherein the first chamber (62) and the second chamber (63) are gas-conducting and are separated from one another by the diffusion filter (61), and / or wherein the first chamber (62) is designed to exsp ) and the second chamber (63) is arranged to receive a sweep gas (64), P580 wherein the sweep gas (64) has at least a lower CO2 concentration than the expiratory breathing gas (5exsp).

26. Device (100) according to one of claims 23 to 25, characterized in that the first chamber (62) is configured to direct the expiratory breathing gas (5 exsp) in the direction of a main flow (S), wherein the second chamber (63) is configured to guide the sweep gas (64) in the direction of a sweep gas flow (S2), wherein the flow direction of the main flow (S) is opposite to the flow direction of the sweep gas flow (S2).

27. Device (100) according to one of claims 3 to 26, characterized in that the CO2 concentration of the sweep gas (64) when introduced into the second chamber (63) is below 10%, preferably below 5%, particularly preferably 0%.

28. Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one sweep gas supply line (71) for providing sweep gas (64) for the mechanical separating means (60), wherein the sweep gas supply line (71) comprises at least one valve (88i) for metering sweep gas (64). 29.Device (100) according to claim 28, characterized in that the valve (88i) is designed to meter a flow rate of the sweep gas (64) which is greater than or equal to the flow rate of the expiratory breathing gas (5. exsp), and / or that the valve (88i) is designed to meter a flow rate of the sweep gas (64) which is 0 to 20 l / min, preferably 0 to 10 l / min.

30. Device (100) according to one of the preceding claims, characterized in that the valve (88i) is designed to adjust the flow rate of the sweep gas (64) in relation to the minute volume, wherein the flow rate of the sweep gas (64) is 1.1 to 2 times the minute volume, preferably 1.2 to 1.5 times the minute volume.

31. Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one valve (88) for dosing fresh gas and / or oxygen O2 and / or that the device (100) comprises at least one valve (841) for dosing volatile anesthetics (VA), the dosing valves (88, 88i, 841) being selected from the group: needle valve, proportional valve, switching valve, orifice, throttle valve. 32.Device (100) according to one of the preceding claims, characterized in that the metering valves (88, 88i, 841) are designed as needle valves, each with at least one stepper motor, via which the metering valves (88, 88i, 841) can be adjusted, wherein the valve position of the metering valves (88, 88i, 841) is set and / or maintained under current supply.

33. Device (100) according to one of the preceding claims, characterized in that the valve position of the metering valves (88, 88i, 841) remains at the last set value without current supply and / or falls to an open basic setting.

34. Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one sensor (15, 16, 17, 18, 19, 20) for detecting at least one ventilation-specific parameter (110). 35.Device (100) according to one of the preceding claims, characterized in that the device (100) comprises at least one storage unit (102) which is set up and. P580 is configured to store the ventilation-specific parameters (110) and / or patient parameters (111) recorded during the respiratory gas supply, wherein the patient parameters (111) comprise at least one of the following parameters: age, weight, height, body mass index (BMI), pre-existing conditions.

36. Device (100) according to one of the preceding claims, characterized in that the device is configured to dynamically adapt the flow rate of the sweep gas (64) to the ventilation-specific parameters (110) and / or to the patient parameters (111). 37.Device (100) according to one of the preceding claims, characterized in that the respiratory gas line (4) comprises a bypass (75) that branches off from the inspiratory branch (1) and opens into the expiratory branch (2) between the mechanical separating means (60) and the outlet (14-A), wherein the bypass (75) is configured to at least temporarily establish a respiratory gas-conducting connection from the inspiratory branch (1) to the expiratory branch (2) such that a second circuit (K2) is formed, in which the respiratory gas mixture (5) can be conducted.

38. Device (100) according to claim 37, characterized in that the second circuit (K2) corresponds at least partially to the first circuit (K1), wherein the connection (93) for a patient interface is arranged only in the first circuit (K1) and / or wherein the mechanical separating means (60) is arranged only in the first circuit (K1). 39.Device (100) according to claim 37 or 38, characterized in that the bypass (75) comprises at least one bypass shut-off valve (76) which is designed and configured to at least temporarily establish the respiratory gas-conducting connection in a flow direction from the inspiratory branch (1) to the expiratory branch (2).

40. Device (100) according to claim 39, characterized in that the bypass shut-off valve (76) is designed as a lockable check valve and is configured to at least temporarily block the bypass (75) in both flow directions, wherein the bypass shut-off valve (76) is configured to block the bypass (75) in both flow directions when energized by the at least one power source (103, 104) and / or wherein the breathing gas mixture (5) can be conducted at least partially in the second circuit (K2) without energizing the shut-off valve (28) and the bypass shut-off valve (76).Device (100) according to one of the preceding claims, characterized in that the device (100) is configured to conduct the respiratory gas mixture (5) in the first circuit (K1) with the main flow (S) and in the second circuit (K2) with a bypass flow (S1), wherein the main flow (S) is dependent on the breathing phases of a patient to be ventilated, wherein the bypass flow (S1) is independent of the breathing phases of a patient to be ventilated.

42. Device (100) according to one of the preceding claims, characterized in that at least the bypass flow (S1) of the second circuit (K2) is conducted through the PEEP valve (30). P580 43. Device (100) according to one of the preceding claims, characterized in that the device (100) is operable in different operating modes (M1, M2, M3, M4, M5, M6, M7), wherein the device (100) is operable in automatic operating modes (M2, M4, M6, M7) in which the blower (3) supplies the conveying energy for the breathing gas mixture (5), wherein the device (100) is operable in manual operating modes (M1, M3, M5) in which the reservoir (12) supplies the conveying energy for the breathing gas mixture (5). 44.Device (100) according to one of the preceding claims, characterized in that the device (100) is operable in operating modes with the application of volatile anesthetics (M1, M2, M5, M6) and / or in operating modes without the application of volatile anesthetics (M3, M4, M5, M6, M7), wherein the safety valve (851) is configured to permit the introduction of volatile anesthetics (VA) into the respiratory gas mixture (5) when energized and to block the introduction of volatile anesthetics (VA) into the respiratory gas mixture (5) when energized.

45. Device (100) according to one of the preceding claims, characterized in that the device (100) is operable in an emergency mode (M5) without a power supply and / or in a power-saving manner, wherein the emergency mode (M5) occurs automatically and / or is manually adjustable. 46.Device (100) according to claim 45, characterized in that the emergency mode (M5) occurs automatically when the functions of the power source (103, 104) and / or the control device (101) and / or the blower (3) are restricted or fail, wherein the breathing gas mixture (5) in the emergency mode (M5) can be conducted at least in the first circuit (K1), wherein the breathing gas mixture (5) can be at least partially discharged via the outlet (14-A).

47. Device (100) according to one of claims 45 or 46, characterized in that the breathing gas mixture (5) in the emergency mode (M5) can be conducted in the second circuit (K2), wherein the conveying energy for the breathing gas mixture (5) in the emergency mode (M5) is provided by the reservoir (12), wherein the reservoir (12) is designed as a hand bag. 48.Device (100) according to one of the preceding claims, characterized in that the APL valve (29) regulates to the last set inspiratory pressure (Pinsp) in emergency mode (M5) and / or that the pressure control valve (30) passively regulates the expiratory pressure (Pexsp) in emergency mode (M5).

49. Device (100) according to one of the preceding claims, characterized in that the chemical separating means (40) and / or the mechanical separating means (60) are active without energization.

50. Device (100) according to one of the preceding claims, characterized in that the safety valve (851) is closed in emergency mode (M5), wherein the safety valve (851) can be opened manually. 51.Device (100) according to one of the preceding claims, characterized in that the metering valves (88, 88i, 841) are not energized in the emergency mode (M5), so that the metering of fresh gas and / or oxygen O2 and / or volatile anesthetics (VA) and / or sweep gas (64) is maintained at the last set value. P580 52. Device (100) according to one of the preceding claims, characterized in that the valve (88i) for metering sweep gas (64) in emergency mode (M5) sets the sweep gas metering to 1.2 to 2 times the last set minute volume, preferably to 1.5 times.

53. Device (100) according to one of the preceding claims, characterized in that fresh gas and / or oxygen O2 are supplied to the breathing gas mixture (5) in emergency mode (M5) via the metering valves (88).

54. Device (100) according to one of the preceding claims, characterized in that the fresh gas and / or oxygen O2 are each provided in at least one compressed gas cylinder (89), wherein the pressure of the compressed gas cylinders provides the delivery energy for the fresh gas and / or oxygen O2. 55.Device (100) according to one of the preceding claims, characterized in that the volatile anesthetics (VA) are provided in at least one tank (900) each, wherein a pressure is present in the tanks (900), wherein the pressure in the tanks (800) is at least 100 kPa, preferably at least 180 kPa, wherein the pressure in the tanks (800) provides the conveying energy for the volatile anesthetic (VA).

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