Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/10—Preparation of respiratory gases or vapours
  • A61M16/104—Preparation of respiratory gases or vapours specially adapted for anaesthetics
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/01—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes specially adapted for anaesthetising
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
  • A61M16/0816—Joints or connectors
  • A61M16/0841—Joints or connectors for sampling
  • A61M16/085—Gas sampling
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/10—Preparation of respiratory gases or vapours
  • A61M16/12—Preparation of respiratory gases or vapours by mixing different gases
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/20—Valves specially adapted to medical respiratory devices
  • A61M16/201—Controlled valves
  • A61M16/202—Controlled valves electrically actuated
  • A61M16/203—Proportional
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/22—Carbon dioxide-absorbing devices ; Other means for removing carbon dioxide
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
  • A61M2016/0015—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors
  • A61M2016/0018—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical
  • A61M2016/0024—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical with an on-off output signal, e.g. from a switch
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
  • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
  • A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
  • A61M2016/0039—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the inspiratory circuit
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
  • A61M16/10—Preparation of respiratory gases or vapours
  • A61M16/1005—Preparation of respiratory gases or vapours with O2 features or with parameter measurement
  • A61M2016/102—Measuring a parameter of the content of the delivered gas
  • A61M2016/1035—Measuring a parameter of the content of the delivered gas the anaesthetic agent concentration
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2202/00—Special media to be introduced, removed or treated
  • A61M2202/02—Gases
  • A61M2202/0208—Oxygen
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2202/00—Special media to be introduced, removed or treated
  • A61M2202/02—Gases
  • A61M2202/025—Helium
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2202/00—Special media to be introduced, removed or treated
  • A61M2202/02—Gases
  • A61M2202/0266—Nitrogen (N)
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2202/00—Special media to be introduced, removed or treated
  • A61M2202/02—Gases
  • A61M2202/0266—Nitrogen (N)
  • A61M2202/0275—Nitric oxide [NO]
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
  • A61M2205/502—User interfaces, e.g. screens or keyboards
  • A61M2205/505—Touch-screens; Virtual keyboard or keypads; Virtual buttons; Soft keys; Mouse touches
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2240/00—Specially adapted for neonatal use

Definitions

• the invention relates to a method and a device for applying at least one medical gas to a ventilated patient.
• a respirator generates a flow of breathing gas in a first conduit supplying breathing gas.
• a predetermined amount of a medical gas to be administered is added to the respiratory gas flow.
• At least the gas exhaled by the patient and the proportion of the breathing gas introduced by the ventilator into the first line and the medical gas introduced into a patient supply line, which have not been inhaled by the patient, are removed via a second line.
• EP 0 937 479 B1, EP 0 937 479 B1, US Pat. No. 5,558,083, EP 0 786 264 B1, EP 1 516 639 B1, and EP 0 723 466 B1 also disclose devices and methods for administering nitric oxide continuous and pulsed time courses known to a ventilated patient.
• control valves for adjusting the amount of nitrogen oxide are provided, which, however, each type of construction under specific given pressure conditions to pass a defined amount of gas per unit time.
• the medical gas is provided in a constellation suitable for the device and to provide the patient, in the opened state of the regulating means, with a suitable amount of gas for treatment.
• the object of the invention is to provide a method and a device for applying at least one medical gas to a patient ventilated by means of a ventilator, in which the amount of gas to be administered is easily adjustable.
• the medical gas is introduced into the respiratory gas flow generated by the ventilator in the first line via the two parallel regulating means and thus to the patient can be supplied.
• the quantity, in particular the volume of the medical gas introduced into the patient supply line can be adjusted with a corresponding choice of pulse length and pulse train. Initially, the onset of at least one inhalation phase of the patient determined. Subsequently, the regulating means are controlled with the aid of a control unit such that a gas pulse is introduced into the patient supply line at the determined beginning of the inhalation phase.
• the introduction can be understood to be exactly at the beginning of the inhalation phase or at a preset interval after the start of the integral phase.
• the temporal decency is chosen in this case in particular such that the gas pulses are introduced during the inhalation phase, preferably within the first third of the inhalation phase.
• only this one gas pulse is introduced during the inhalation phase. While following the inhalation phase
• Respiratory arrest phase and the subsequent exhalation in particular, no medical gas is introduced.
• the medical gas is delivered in an impulsive manner at the beginning of the inhalation phase so that as much of the patient's medical gas as possible can be exempted from the beginning of the inhalation phase.
• the supplied amount of medical gas is supplied within a short time with a large volume flow.
• gas sources with different concentrations of the medical gas in this manner, without requiring any structural changes of the device for administering the medical gas.
• both the method and the device provide a variable adjustment of the amount of gas to be applied in large adjustment ranges and thus a broad concentration spectrum.
• the pulse-shaped partial pressure caused by the gas pulses can be measured down to the respiratory tract of the ventilated patient.
• the regulating means are controlled with the aid of a control unit or of the control unit such that a gas quantity fixed to a gas pulse and / or a gas volume fixed to a gas pulse is introduced into the patient supply line.
• a gas quantity fixed to a gas pulse and / or a gas volume fixed to a gas pulse is introduced into the patient supply line.
• the medical gas contains NO (nitrogen monoxide).
• the medical gas can in particular be provided as a gas mixture of NO (nitrogen monoxide) and N 2 (nitrogen).
• a gas mixture of NO (nitrogen monoxide) and He (helium) has proven to be particularly advantageous, since particularly short reaction and reaction times are achieved, in particular by helium.
• the parallel regulating means are preferably valves and are then also referred to as a valve bank.
• the first valve has a flow rate of 0.16 liters per minute
• the valve 2 a flow rate of 1.6 liters per minute
• the valves 3 and 4 each have a flow rate of 8 liters per minute with permanent opening (measured with medical air).
• regulating means which have a shortest possible opening time of ⁇ 7 milliseconds, preferably in the range of 4 milliseconds to 7 milliseconds.
• the control unit can open the valves individually or in any combination, so that in the specific embodiments, a maximum flow of 17.76 liters per minute is possible.
• control unit optimizes the opening of the regulating means in such a way that the shortest possible opening time within a single breath is achieved. This achieves a targeted injection of the medical gas into an initial part of the breath. Furthermore, this achieves a large, adjustable dosing range of the medical gas to be applied to the patient. In one embodiment, when opening only one valve with a flow rate of 0.16 liters per minute, 7 milliseconds opening time per gas pulse per breath, theoretically 18.60 microliters of the medical gas are applied. Due to the required valve lift and / or the response delay, however, 13 microliters are applied in practical experiments with these parameters.
• the invention provides a greater range of therapeutic concentration clinically available.
• the regulation means in the open state allow passage of different volume flows from the gas source to the patient supply.
• at least two of the regulating means in the opened state allow different volume flows to pass from the gas source to the patient supply.
• the regulating means each comprise at least one solenoid valve.
• at least one regulating means can be preceded and / or followed by an orifice plate or another throttling means for restricting the volume flow flowing through the regulating means.
• Solenoid valves are on the one hand inexpensive and on the other hand solenoid valves have relatively short response times. The solenoid valves are driven in particular binary, so that they are fully closed in a first operating state and fully open in a second operating state.
• Regulating means of the same type can be used by the throttling means for restricting the volumetric flow passing through the regulating means, in particular solenoid valves of the same type, wherein the volume flow flowing through the regulating means in the opened state is different by the provision of different flow resistances. As a result, different volume flows can be generated through the regulating means in a simple manner.
• the second line gas is removed. At least the proportion of the medical gas and / or the proportion of a reaction product of the medical gas in the withdrawn gas is determined.
• the gas can be taken from the second line via a measuring line and fed to an analysis unit for detecting at least the proportion of the medical gas and / or the proportion of a reaction product of the medical gas.
• the sampling and detection may be repeated once or several times during an inhalation process, preferably at each one Inhalation, be performed. Thereby, the concentration of the medical gas in the exhaled gas can be easily detected, monitored and / or regulated.
• the inner diameter of the measuring line is preferably smaller than the diameter of the first line, the second line and the patient supply line.
• the proportion of the medical gas in the exhaled gas is regulated to the preset desired value.
• the amount of medical gas to be administered to the patient can be monitored and / or kept constant in a simple manner. If, in addition to or as an alternative to the proportion of the medical gas, the proportion of a reaction product of the medical gas is analyzed, it is advantageous to determine the proportion of an oxidation product of the medical gas.
• nitric oxide (NO) is used as medical gas
• the proportion of the oxidation product nitrogen dioxide (NO 2 ) can be determined.
• the proportion of nitrogen dioxide detected can then be compared with a permissible target value.
• the introduction of the medical gas into the patient supply line can then be stopped or the volume of the introduced medical gas can be reduced. If the concentration of nitrogen dioxide in the respiratory gas is too high, the patient may be harmed and this should be avoided.
• the ventilator determines information about a flow profile of the respiration of the ventilated patient.
• the control unit determines the beginning of the inhalation phase as a function of this flow profile or determines the time of commencement of a future, preferably the next inhalation phase.
• the time start of several inhalation phases is determined. At the beginning of each inhalation phase, exactly one gas pulse is initiated. It is thus achieved that, at the beginning of each inhalation phase, the amount of medical gas necessary for receiving the amount of medical gas to be administered is provided, in particular, jerkily. Thus, with each breath, the patient can receive the optimal amount of medical gas for their therapy.
• At least one exhalation phase and / or at least one respiratory arrest phase are preferably determined in addition to the inhalation phase.
• a gas pulse with medical gas introduced into the patient supply line is a gas pulse with medical gas introduced into the patient supply line.
• data is determined with information about the times of at least two previous inspiration phases.
• the time start of the future inhalation phase is determined.
• the beginning of the future inspiration phase is determined on the basis of more than two previous inspiration phases.
• the beginning of the future inhalation phase is determined by adding this distance to the time of the beginning of the last inhalation phase.
• the beginning of the inhalation phase can also be determined from the gradient of the airfoil. In this case, not the beginning of a future inhalation phase, but the beginning of the current inhalation phase is determined.
• the gas volume of at least one previous inhalation phase is determined.
• the control unit determines the gas volume of the inhalation phase as a function of this gas volume and determines the amount of medical gas which is introduced via the gas pulse at the beginning of the inhalation phase as a function of the determined gas volume. It is advantageous if the gas volume of several preceding inhalation phases is determined and the gas volume of a future inhalation phase and thus also the amount of medical gas to be introduced during the inhalation phase as a function of the gas volume. lumina of the several previous inhalation phases. To determine the gas volume of the future inhalation phase, it is possible, for example, to use pattern recognition in preceding respiratory phases. Alternatively, the gas volume of the future inhalation phase can be determined by forming an average of the previous gas volumes of the preceding inhalation phases.
• the amount of medical gas to be introduced is determined in particular proportionally to the determined gas volume of the inhalation phase.
• the gas volume of the previous inhalation phase or the gas volumes of the preceding inhalation phases are in particular determined from the flow profile determined with the aid of the ventilator. Thus, no additional separate gas sensor to determine the gas volume must be provided.
• solenoid valves preferably reversible valves are used between a fully closed and a fully open position, which are controlled binary.
• the invention can be used in particular in neonatology for the treatment of pulmonary hypertension of a premature baby with nitric oxide. Nitric oxide is also applied to treat patients after organ transplants. However, the invention can also be used for the application of other gaseous drugs.
• a gas source for delivery of gaseous drugs may come from a gas source for delivery of gaseous drugs.
• a gas source is also known as additive gas Source, since it is provided in addition to a respiratory gas source or oxygen source.
• the prior art drawback that from the time of measuring the flow rate of the breathing gas used to inspiration the patient to the mechanical adjustment of a control valve used for the introduction of the medical gas results in a delay time and relatively high concentration variations of the applied medical gas in the patient provided Ventilation air occur in dynamic flow profiles is avoided by the invention.
• the control range of the medical gas passed through is relatively limited. For valves that allow a large flow of medical gas, low flow rates can be adjusted only relatively inaccurate.
• a discontinuous feed can be made by several gas pulses in the breathing air of the patient circuit of the ventilator comprising the first line, the second line, the patient supply line.
• FIG. 1 shows a schematic representation of a device for applying at least one medical gas to a ventilated by means of a ventilator patient according to a first embodiment; a schematic representation of components of a lizier réelles for application of the medical gas; a schematic representation of a device for applying at least one medical gas to a ventilated by means of a ventilator patient according to a second embodiment of the invention; a representation of the time course of the breathing of the ventilated patient and the application of the medical gas according to the first and second embodiments of the invention;
• FIG. 5 a schematic representation of a device for the application of at least one medical gas to a patient ventilated by means of a ventilator according to a third exemplary embodiment of the invention
• FIG. 6 is an illustration of the time course of the respiration of a ventilated patient and the application of the medical gas according to the third embodiment of the invention.
• FIG. 7 shows an illustration of the temporal course of the respiration of a ventilated patient and the application of the medical gas according to a fourth exemplary embodiment of the invention
• 8 shows a schematic representation of a device for applying at least one medical gas to a with
• FIG. 9 shows a schematic representation of a device for applying at least one medical gas to a with
• FIG. 10 shows a representation of the time course of the respiration of a ventilated patient and the application of the medical gas with the aid of the device according to FIG. 8 or FIG. 9.
• FIG. 1 shows a schematic representation of a device 10 for applying at least one medical gas to a patient 14 ventilated by means of a respirator 12 according to a first exemplary embodiment of the invention.
• NO nitrogen monoxide
• This gas is provided in a gas cylinder 16 as a gas mixture (NO / N 2 ) comprising N 2 nitrogen and NO nitrogen monoxide.
• NO / N 2 gas mixture
• the gas mixture NO / N 2 a metering device 20 via a connection hose 22 with a preset pressure regulator 18 target pressure at the connecting piece C of the metering device 20 is supplied.
• From the respirator 12 performs a first designed as a breathing air hose line 24 to a running as Y-piece connecting element 26.
• a second tube designed as an exhaust air line 28 and a patient supply line 30 connected to the connecting element 26.
• the patient supply line 30 is in the present embodiment with a test lung simulating the patient 14 in the form of an inflatable balloon 32 connected.
• the end of the patient supply line 30 leading to the patient 14 is connected to a breathing mask or a tube inserted into the respiratory tract of the patient 14.
• the exhaust hose 28 is guided back to the respirator 12, wherein the flowing back through the exhaust hose 28 gas mixture is either dissipated or reprocessed in the ventilator 12.
• the respirator 12 is connected in the present embodiment via a connecting hose 34 with a formed as a gas cylinder 36 gas source.
• the gas cylinder 36 contains an oxygen (O 2 ) and nitrogen (N 2 ) comprising gas mixture (O 2 / N 2 ).
• the gas mixture O 2 / N 2 is limited by means of a pressure regulator 38 to a preset desired value and fed via the connecting tube 34 to the ventilator 12.
• oxygen and nitrogen may also be provided by separate gas sources 36, particularly via a central gas supply to a hospital.
• the ventilator 12 generates a constant flow of respiratory gas in the breathing air tube 24.
• the medical gas mixture NO / N 2 intended for the treatment of the patient is supplied to this constant breathing gas flow via the connecting line 40.
• the metering device 20 continuously generates gas pulses having a pulse frequency which is at least independent of the respiratory rate of the patient.
• a measuring line 41 is connected to the patient supply line 30 and leads at least a portion of the gas mixture in the patient supply line 30 to the connecting piece A of the metering device 20. Das der Dosing device 20 via the connection piece A supplied gas mixture is analyzed by a measuring / evaluation unit 44 of the metering device 20.
• FIG. 2 shows a schematic representation with components of the metering device 20 according to FIG.
• the metering device 20 is also referred to as NO application device due to the nitrogen monoxide used in the exemplary embodiment as a medical gas.
• the metering device 20 has a first module 42 with a measuring / evaluation unit 44, which analyzes the proportion of NO in the gas mixture (O 2 / N 2 / NO) supplied via the connecting piece A and sends a corresponding measured value to a control unit 48 arranged in the second module 46 transfers.
• the control unit 48 is connected to a control unit 50 designed as a human-machine interface.
• the operating unit 50 is preferably designed as a touch screen. Parameters of the metering device 20, in particular setpoint values, can be set via the operating unit 50.
• setting values, measured values and operating values can be output via a display unit of the operating unit 50.
• the control unit 48 is preferably connected via a data line (not shown) to a control unit of the ventilator 12. Via this data line, relevant parameters measured values and further information between the control unit 48 and the control unit of the ventilator 12 can preferably be transmitted bidirectionally.
• the metering device 20 has a third module 52, which in the present exemplary embodiment comprises four magnetic valves 54 to 60, to which the respective medical gas mixture NO / NO 2 is supplied via the connecting piece C.
• the solenoid valves 54, 56 are each a metering orifice 62, 64 for limiting the flow through the respective solenoid valve 54, 56 upstream.
• the output sides of the solenoid valves 54 to 60 are connected to the port B, so that the solenoid valves 54 to 60 are connected in parallel.
• the control unit 48 of the metering device 20, the solenoid valves 54 to 60 individually control, ie open individually or in combination.
• valve bank 52 it is possible to achieve a gas flow between the connecting piece C and the connecting piece B by opening a valve 54 to 60 and thus to introduce medical gas NO via the connecting line 40 into the breathing gas line 24.
• the flow rate between the connecting piece C and the connecting piece B can be increased by the simultaneous opening of several valves 54 to 60.
• the applied amount, ie the amount of medical gas NO introduced into the breathing gas line 24 can be adjusted by a suitable choice of the pulse duration and / or by a suitable choice of the pulse frequency.
• the gas pulses generated by the individual valves 54 to 60 may have a different pulse duration at preferably the same pulse frequency.
• the third module with the parallel arrangement of a plurality of valves 54 to 60 is also referred to as valve bank 52.
• the valve bank 52 with the four solenoid valves 54 to 60 allows a large adjustable metering range and a flexible adaptation of the amount of gas to be applied when using gas sources 16 with different starting concentrations of the medical gas.
• the initial concentration is preferably preset as a parameter via the operating unit 50 and taken into account in the calculation of the pulse duration and pulse frequency for generating the quantity to be applied.
• the solenoid valve 54 has a flow rate of 0.16 liters per minute
• the solenoid valve 56 has a flow rate of 1.6 liters per minute
• the solenoid valves 58 and 60 respectively a flow of 8 liters per minute measured with medical air.
• the pulse frequency, ie the clock rate is 104 gas pulses per minute, ie 104 beats per minute. If smaller amounts of the medical gas NO are to be applied or if, for other reasons, a lower clock rate or a lower pulse frequency are selected, this is preferably reduced to 52 gas pulses per minute or 26 gas pulses per minute. If a higher pulse frequency is to be selected, this can also be increased to 208 gas pulses per minute.
• initial maximum dosages of 40 ppm are applied in adult patients and initial maximum dosages of 20 ppm in children. In neonates or preterm infants, the initial maximum dosage may be lower.
• the dosage is lowered to weaning the patient gradually or continuously down to 0.5 ppm in preterm infants to 0.1 ppm.
• the initial concentration of the medical gas in the gas source 26 is preferably 1,000 ppm. All dosage data refer to the air supplied to the Y-piece 26 with the introduced medical gas.
• valve bank 52 having a plurality of valves 54 to 60 arranged in parallel, it is possible to use gas sources 16 with higher starting concentrations of the medicinal gas, in particular of up to 2,000 ppm or up to 4,000 ppm, with currently customary amounts of application. Compared with gas sources with 1,000 ppm of the same amount of gas, the service lives are doubled when the initial concentration is doubled.
• the use of the valve bank 52 provides a greater therapeutic Concentration range.
• the minimum opening duration of the solenoid valves 54 to 60 in the present embodiment is 7 milliseconds.
• FIG. 3 shows a schematic representation of a device 100 for applying at least one medical gas to a patient ventilated by means of a ventilator 12 in accordance with a second exemplary embodiment of the invention.
• the device 100 is structurally and functionally consistent with the device 10 of FIG.
• the medical gas nitrogen monoxide (NO) is provided as a gas mixture comprising nitrogen monoxide (NO) and helium (He).
• the gas mixture (NO / He) preferably consists of nitrogen monoxide (NO) and helium (He), with the exception of customary impurities.
• This gas mixture (NO / He) is provided via a gas source formed as a gas cylinder 102 and fed via the pressure regulator 18 and the connecting line 22 in the connecting piece C of the metering device 20.
• a gas source formed as a gas cylinder 102 and fed via the pressure regulator 18 and the connecting line 22 in the connecting piece C of the metering device 20.
• NO nitrogen monoxide
• He helium
• FIG. 1 Representations of the temporal courses of the respiration of the ventilated patient 14 as well as the application of the medical gas in the form of gas pulses are shown in FIG.
• the time course of the patient's breathing 14 is shown as the volume flow Q.
• a first inhalation phase of the patient 14 takes place.
• a respiratory arrest of the patient 14 occurs.
• a first exhalation phase of the patient 14 takes place and between the times t3 and t4 second inhalation phase, which is shorter than the first inhalation phase.
• a second exhalation phase takes place.
• the gas pulses introduced into the breathing air supply line 24 with the aid of the metering device 20 are represented as the volume flow of the relevant portion of the medical gas NO.
• the delivery of the medical gas takes place in this embodiment by gas pulses having a constant pulse frequency and thus independent of the respiratory rate of the patient 14.
• solenoid valves preferably reversible valves are used between a fully closed and a fully open position, which are controlled binary.
• the invention can be used in particular in neonatology for the treatment of pulmonary hypertension of a premature baby with nitric oxide. Nitric oxide is also applied to treat patients after organ transplants. However, the devices 10, 100 described in the exemplary embodiments can also be used for the application of other gaseous medicaments.
• FIG. 5 shows a schematic illustration of a further device 200 for applying at least one medical gas to a patient 14 ventilated by means of a ventilator 12 in accordance with a third exemplary embodiment of the invention.
• the metering of the medical gas NO into the patient circuit part of the ventilator 12 takes place. H. in the breathing air hose 24 proportional to
• gas pulses having different gas volumes are generated as a function of the respiratory phase and / or the course of the respiratory phase.
• a data and / or signal line 202 is provided between the respirator 12 and the metering device 20, via which the control unit 48 of the metering device 20 transmits information about a real-time flow profile of the respiration of the ventilated patient 14 with the aid of signals and / or data.
• a real-time-capable bus system such as a CAN-BUS or a serial interface, such as a USB interface or RS232 interface
• a real-time data transmission protocol can be used for data transmission.
• the introduction of the medical gas into the breathing air supply line 24 then takes place in such a way that during the breathing phases of the patient a higher concentration of the medical gas is contained in the supplied ventilation air.
• the gas pulses are delivered at a constant pulse frequency, wherein the amount of gas delivered per gas pulse is greater during the inhalation phases than during respiratory arrest phases and during the exhalation phases of the patient 14.
• the pulse frequency during the inhalation phases may be higher than during the exhalation phases and during respiratory arrest.
• the delivery of the medical gas through the metering device 20 may be interrupted. It is advantageous with the aid of an optimization of the gas pulses and pulse frequency carried out by the control unit 44 or a control unit of the ventilator 12 to require a relatively long opening time of the activated valves 54 to 60 within the defined pulse frequency.
• the pulse frequency is preferably 104 gas pulses per minute.
• valve bank 52 First when the gas flow of the medical gas required by the valve bank 52 is greater than or equal to the maximum flow through a valve 54-60, such that the flow through that valve 54-60 would not be sufficient to apply the required amount of the medical gas; or the valve 54-60 would no longer close and thus would no longer generate gas pulses, an additional additional valve 54-60 or, instead of the first valve 54-60, a second higher-flow valve 54-60 is opened by the control unit 48 driven.
• the medical gas NO is not provided as a gas mixture of nitrogen monoxide and nitrogen (NO / N 2 ), but as a gas mixture of nitrogen monoxide (NO) and helium (He).
• NO nitrogen monoxide
• He nitrogen monoxide
• the advantages associated with this gas mixture (NO, He) have already been explained in connection with FIG.
• the gas pulses are generated in this fourth exemplary embodiment as described for the third exemplary embodiment in conjunction with FIG.
• FIG. 6 shows a representation of the time course of the respiration of the ventilated patient 14 and the time profile of the application of the medical gas (NO / N 2 ) / (NO / He).
• the respiratory air flow of the ventilated patient 14 is shown in the upper diagram, similar to FIG. 4, and the lower diagram shows the time course of the gas pulses through which the medical gas NO or the gas mixture (NO / N 2 ), (NO / He) is fed into the breathing gas supply line 24.
• the gas flow through the valves 54 to 60 or through the valve bank 52 at a constant pulse width by a targeted selection and / or combination of different valves 54 to 60 is varied.
• FIG. 7 shows a representation of the time course of the respiration of the ventilated patient 14 and the application of the medical gas according to a fourth exemplary embodiment of the invention.
• the fourth embodiment differs from the exemplary embodiment shown in FIG. 6 in that during the inhalation phases gas pulses having a greater pulse width than during the exhalation phases are applied.
• the applied amount of medical gas is increased.
• it can thereby be achieved even at high flow velocities of the respiratory gas that the amount of medical gas applied is proportional to the flow velocity.
• the amount of gas applied in a gas pulse can be further varied by the fact that the individual pulse widths, with which the valves 54 to 60 are driven to generate a gas pulse, are different, so that at least two valves 54 to 60 deliver gas pulses of different pulse width. As a result, a total gas pulse is generated, which has been generated from two partial pulses of different pulse width. The Ges amt impulse has then a gradual course of the respiratory gas supply 24 is initiated.
• the pulse frequencies during the inhalation phases are twice as high as in the exhalation phase.
• the pulse frequency during the inhalation phase may be 208 gas pulses per minute and during the exhalation phase 104 gas pulses per minute.
• the pulse frequency during the inhalation phase may be 104 gas atmospheres. pulse per minute and during the exhalation 52 gas pulses per minute.
• the length of inspiration 14 of patient 14 and / or the course of patient inspiration 14 may be empirical, depending on the flow at the beginning of the inspiratory process and / or the course of the gas flow be determined and determined in accordance with the estimated course for each gas pulse during a Einatemzugs a to be initiated by this gas pulse in the breathing gas supply line 24 gas quantity of the medical gas.
• the fixed amount of gas is then introduced by a suitable control of the solenoid valves 54 to 60 in the breathing gas supply line 24.
• a closed loop system is formed so that the gas mixture exhaled by the patient 14 remains in the closed loop system.
• the medical gas not absorbed by the patient also remains in the circulatory system.
• Such closed circuits are used in particular during anesthesia of the patient 14.
• the patient 14 is connected to an anesthesia machine.
• the control unit 48 is connected via an interface with the anesthetic machine.
• the anesthesia machine comprises at least one sensor for determining the beginning of a breath of the patient 14 and a sensor for determining the volume of gas mixture inhaled in this breath.
• the anesthesia machine communicates via the interface with information about the beginning of the breath and the inspired volume of gas mixture to the control unit 48, which determines in dependence of this data, the amount of the valves 54 to 60 injecting medical gas such that so much medical gas inji- It is noted that this is absorbed in the breath completely or at least almost completely by the patient 14, so that there is no accumulation of the medical gas in the gas mixture of the closed-loop system.
• the control unit 48 controls the solenoid valves 54 to 60 in particular such that the amount of medical gas to be injected is injected within a short time at the beginning of the breath. Thus, an accumulation of the medical gas in the gas mixture is avoided, thereby avoiding, for example, reactions with other substances in the closed-loop system.
• FIG. 8 shows a schematic illustration of a device 300 for administering a medical gas NO to a patient 14 ventilated by means of a ventilator 12 in accordance with a fifth embodiment of the invention.
• FIG. 9 shows a schematic illustration of a device 400 for applying at least one medical gas NO according to a sixth embodiment of the invention.
• N2 nitrogen
• He helium
• Embodiments 5 and 6 the medical gas NO is supplied directly to the patient supply line 30 via the gas line 40 and not to the respiratory gas line 24. This ensures that the medical gas is supplied to the patient 14 as close as possible, so that it can be taken by the patient 14 directly after being fed via the gas supply line 40 without a long time delay. This is particularly advantageous in the treatment of infants where it is very important that the medical nical gas NO is administered to infants at the specified times during respiration.
• the embodiments 5 and 6 differ from the first three embodiments in that the measuring line 41 does not remove the gas mixture to be analyzed from the patient supply line 30 but from the exhaust air line 28. Via the measuring line 41, the gas of the measuring and evaluation unit 44 of the metering device 20 is supplied.
• the supply of the medical gas NO in the fifth and sixth embodiments of the invention is each jerked by a single gas pulse 402, 404 at the beginning of each inhalation phase.
• the amount of medical gas NO to be received by the patient 14 is initiated so that it is immediately available for patient 14 to receive.
• much of the medical gas NO can be taken up, so that it can penetrate deep into the lungs and thus be readily absorbed by the patient 14.
• this jerky supply of the entire amount of medical gas NO at the beginning of each inhalation phase has the advantage that as little as possible of medical gas NO is supplied unused during a respiratory arrest phase and / or exhalation phase during which it can not be received by the patient 14.
• FIG. 10 shows a first inhalation phase between time 0 and time t 1 and a second inhalation phase between time t 3 and time t 4.
• the supply of the medical gas takes place through the designated 402, the gas pulse.
• the supply of the medical gas by the gas pulse 404 takes place.
• a flow profile of the respiration of the patient 14, as shown in the upper diagram in FIG. 10, is determined. From the flow profile, the time of a future or a current inhalation phase is determined as a function of the times (0, t3) of at least two immediately preceding inhalation phases.
• the control unit 48 controls the solenoid valves 54 to 60 in such a way that at the beginning of the determined inhalation phase, the gas quantity to be introduced of the medical gas NO is initiated in an impulsive manner via a gas pulse 402, 404.
• the gas volume of at least one previous inhalation phase, preferably several previous inhalation phases is determined.
• the gas volume of the future or current inhalation phase is determined and, depending on this, the amount of medical gas NO to be introduced into the patient supply line 30 is established.
• the amount of medical gas NO to be introduced is determined in such a way that it is greater, the greater the expected gas volume of the future or current inhalation phase.
• the gas volume of the previous inhalation phases is determined in particular from the flow profile. For this purpose, in particular, the area enclosed by the determined curve during the inhalation phase and the t-axis is determined.
• the expected gas volume of the future or current inhalation phase is determined in particular by averaging a preset number of preceding inhalation phases. Alternatively, the expected gas volume of the future or current inhalation phase can also be determined with the aid of pattern recognition of the preceding inhalation phases, by means of which, for example, periodically recurring fluctuations in the respiration of the patient 14 can be determined.
• the gas volume of the first inhalation phase (0 to t1) is greater than the gas volume of the second inhalation phase (t3 to t4).
• the control unit 48 controls the solenoid valves 54 to 60 such that the first gas pulse 402 is greater than the second gas pulse 404.
• the size of the gas pulses 402, 404, so the amount of medical gas, with the respective gas pulse 402, 404 of the Patient supply line 30 is supplied, can be adjusted by the pulse duration of the gas pulses 402, 404 and by the flow volume of the medical gas during the respective gas pulses 402, 404.
• the medical gas is taken up in a carrier gas, in particular helium.
• a carrier gas in particular helium.
• the ventilator 12 comprises a sensor for calculating the gas volume of a breath of the patient 14 and a sensor for determining the time of beginning of a breath.
• the respirator 12 is connected via a data interface with the metering device 20, wherein via the interface data with information about the volume of the last Breath of the patient 14 and data with information about the times of at least the last two breaths of the patient 14 are transmitted.
• the control unit 48 determines in response to this data in real time the beginning of the next breath of the patient 14 and controls depending on the calculated start of the breath and at least the gas volume of the last breath, the solenoid valves 54 to 60 such that the injecting amount of medical gas to Beginning of the next breath is injected jerkily.
• jerky injection is meant in particular that the medical gas is injected within the shortest possible time.
• the control unit 48 opens the solenoid valves 54 to 60 as far as possible at the beginning of the breath.
• N2 nitrogen
• He helium

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