WO2018033224A1 - Dispositif permettant de mettre un patient sous respiration artificielle et procédé pour faire fonctionner ce dispositif - Google Patents

Dispositif permettant de mettre un patient sous respiration artificielle et procédé pour faire fonctionner ce dispositif Download PDF

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Publication number
WO2018033224A1
WO2018033224A1 PCT/EP2017/000229 EP2017000229W WO2018033224A1 WO 2018033224 A1 WO2018033224 A1 WO 2018033224A1 EP 2017000229 W EP2017000229 W EP 2017000229W WO 2018033224 A1 WO2018033224 A1 WO 2018033224A1
Authority
WO
WIPO (PCT)
Prior art keywords
pump
pressure
frequency
membrane element
pumping arrangement
Prior art date
Application number
PCT/EP2017/000229
Other languages
German (de)
English (en)
Inventor
Hans-Ullrich Hansmann
Karsten Hiltawsky
Ulf Pilz
Sebastian Schröter
Original Assignee
Drägerwerk AG & Co. KGaA
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Drägerwerk AG & Co. KGaA filed Critical Drägerwerk AG & Co. KGaA
Publication of WO2018033224A1 publication Critical patent/WO2018033224A1/fr

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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
    • A61M16/20—Valves specially adapted to medical respiratory devices
    • A61M16/201—Controlled valves
    • A61M16/206—Capsule valves, e.g. mushroom, membrane valves
    • 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
    • A61M16/205—Proportional used for exhalation control
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00—Machines, pumps, or pumping installations having flexible working members
    • F04B43/02—Machines, pumps, or pumping installations having flexible working members having plate-like flexible members, e.g. diaphragms
    • F04B43/04—Pumps having electric drive
    • F04B43/043—Micropumps
    • F04B43/046—Micropumps with piezoelectric drive
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
    • F16K31/00—Actuating devices; Operating means; Releasing devices
    • F16K31/004—Actuating devices; Operating means; Releasing devices actuated by piezoelectric means
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
    • F16K31/00—Actuating devices; Operating means; Releasing devices
    • F16K31/12—Actuating devices; Operating means; Releasing devices actuated by fluid
    • F16K31/126—Actuating devices; Operating means; Releasing devices actuated by fluid the fluid acting on a diaphragm, bellows, or the like
    • F16K31/1266—Actuating devices; Operating means; Releasing devices actuated by fluid the fluid acting on a diaphragm, bellows, or the like one side of the diaphragm being acted upon by the circulating fluid
    • 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
    • A61M2016/0027—Accessories therefor, e.g. sensors, vibrators, negative pressure pressure meter
    • 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
    • A61M2205/07—General characteristics of the apparatus having air pumping means
    • 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

Definitions

  • the invention relates to a device for ventilating a patient, which has an expiratory valve with a membrane element for transmitting a positive end-expiratory pressure.
  • Devices for breathing a patient are z.
  • Patients wear a face mask that covers the mouth and nose, or a tube that is inserted into the patient's pharynx and trachea.
  • the face mask or the tube are connected via a Y-piece with a respirator or an anesthetic machine.
  • the Y-piece has three star-shaped via channels interconnected openings. One of the openings is fluid-communicating with the face mask.
  • the ventilator forces an inspiratory flow of respiratory gas into the patient's lungs through one of the two remaining orifices of the Y-piece. When exhaling, this inspiratory connection of the Y-piece to the respirator or anesthetic device is blocked, and the expiratory inspiratory gas flow produced as the patient exhales is directed across the other of the remaining openings of the Y-piece
  • a certain pressure remains in the lung, for example to increase the absorption of oxygen in the lungs.
  • a resistance in the form of a back pressure is provided at the end of the Y-piece from which flows the expiratory breathing gas flow. This back pressure is the positive end-expiratory pressure (PEEP).
  • the expiratory end of the Y-piece is connected to an expiration valve whose closing pressure can be adjusted. As long as the breathing gas flow has a higher pressure than the closing pressure, the valve opens. If the pressure of the breathing gas flow falls below the closing pressure, the valve closes.
  • the expiratory valve is located either at the Y-piece, within the expiratory tubing, or within the ventilator or anesthesia machine at its expiratory inlet.
  • pneumatic drives are known. They are simpler than electric drives and direct the force across the valve plate. In this case, lateral forces are avoided in pneumatic drives.
  • pneumatic systems are generally slower and easier to oscillate than electric drives. This is due to the so-called compliance, which describes the relationship between the total gas volume of the pneumatic system and the gas volume to be changed.
  • fast pneumatic actuators require powerful pressure sources that can be varied quickly.
  • the pressure can be regulated quickly. This is especially necessary if the expiratory valve is to be opened against the continuously generated pressure of the pump.
  • These pumps are typically diaphragm or piston pumps operating at a frequency of 20 Hz to 100 Hz.
  • FIG. 2 shows the state of the art.
  • the ventilator has an expiratory valve 10 with a membrane element 11, which can occlude an expiratory channel 13 of the mask 18 with a Y-piece by means of a sealing component 12.
  • the membrane element 11 is arranged in an expiration outlet 15.
  • the membrane element 11 is connected to a pumping arrangement 2 by a flexible holding component 14 via a first connecting hose 32.
  • the pump arrangement 2 has an outlet opening 37 on a membrane or piston pump 35, through which the gas conveyed by a pump arrangement 2 is discharged.
  • the flexible mounting component 14 in this case connects the membrane element 1 1 with the outlet opening 37.
  • the pumping arrangement 2 furthermore has a large-volume pressure tank 33, which acts as a low-pass filter for the pumping surges of the pumping arrangement 2.
  • the pressure tank 33 is connected via a second connecting hose 34 with the diaphragm or piston pump 35. Further, a relief valve 16 is provided, which is used to control the positive end-expiratory pressure. Only the pressure tank 33 has a volume of at least about 30 ml, wherein the volume of the volume to be changed, over which the membrane element 1 1 is raised, is about 6 ml.
  • the object of the invention is to provide a lightweight, simply constructed and quickly controlled drive for an expiratory valve.
  • a device for ventilating a patient having an expiratory valve with a membrane element for transmitting a positive end-expiratory pressure and a pumping arrangement for generating the positive end-expiratory pressure, which is fluid-communicating connected to the membrane element it is provided according to the invention that the pumping arrangement High-frequency pump for generating the positive end-expiratory pressure has.
  • a high-frequency pump is understood to mean a pump which has a pump frequency of at least 600 Hz.
  • the pumping arrangement operates outside the system frequencies of the expiratory valve. As a result, no vibrations are generated in the system by the surge of the high-frequency pump. Therefore, one can dispense with a pressure tank that attenuates high frequencies that are within the system frequencies of the expiratory valve.
  • the compliance of the pump arrangement according to the invention is reduced to the compliance of the high-frequency pump and the connection channels with the membrane element. The pumping arrangement therefore no longer needs minimum compliance in order to avoid vibrations.
  • the compliance is significantly reduced compared to conventional pumping arrangements, so that a highly dynamic control of the positive end-expiratory pressure is made possible solely by the control of the high-frequency pump.
  • the vibration behavior is further improved. Because only a small volume is present in the pumping arrangement, only high-frequency vibrations of the membrane element are amplified by the pumping arrangement. The vibrations of the membrane element are not amplified by the pumping arrangement. This results in an improved vibration behavior of the expiratory valve.
  • the high frequency pump is a piezo pump.
  • Piezo pumps have the advantage that they are powerful and can be operated at frequencies in the kilohertz range.
  • piezo pumps are operated at a frequency above the high-frequency hearing threshold (about 21000 Hz), preferably at a frequency of 25000 Hz. At this frequency, piezo pumps are imperceptible to human hearing, so that neither the hospital staff nor the patient can perceive noises from the operation of the pumping arrangement.
  • piezo pumps are simply constructed and inexpensive to produce.
  • Another advantage is that piezo-pumps have very small dimensions and thus significantly reduce the weight of the pumping arrangement, in contrast to the known systems. The pumping arrangement can thus be arranged directly on the expiratory valve.
  • the pumping arrangement has a two-way pump, which can be flowed through in two directions.
  • the gas flow in the pumping arrangement the regular from a Ansau-. Gö réelle is directed to an outlet opening, can be reversed in a two-way pump. Therefore, this pumping arrangement no longer has a dedicated suction opening or outlet opening.
  • the two-way pump has first and second two-way ports. In one inflow state, the fluid flows into the two-way pump through the first two-way port and out of the two-way pump through the second two-port port. In a reflux state, the fluid flows into the two-way pump through the second two-way port and out of the two-way pump through the first two-port port.
  • the membrane element can thus be opened only by the pressure of the expiratory breathing gas flow without the aid of a relief valve or other auxiliary components. It can be dispensed with a relief valve that would otherwise have reduced the pressure on the pump side in this case.
  • the pump assembly may conveniently further comprise a pump stack having a plurality of high frequency pumps.
  • the high-frequency pumps in the pump stack are connected in series. This means that the outlet opening of one pump is directed into the suction opening of the second pump.
  • the pump arrangement has a plurality of parallel-connected high-frequency pumps. In this case, the outlet ports of the high-frequency pumps are all directed to the same volume. If several high-frequency pumps are used, the other pumps can compensate for the missing pump power if one pump fails. Further, with a plurality of many small and inexpensive pumps, reliably high end pressures can be achieved. The dimensions of the pumping arrangement can be made flexible in this way.
  • the device has a control unit for the pumping arrangement, wherein the control unit is connected to a sensor for the control pressure on the membrane element.
  • the control unit controls the pumping arrangement as a function of the control pressure.
  • a common mode module is provided, which is designed to drive the plurality of high-frequency pumps in a common mode.
  • the plurality of high-frequency pumps each produce the same pump power.
  • the advantage of common mode drive is that the high frequency pumps are worn evenly.
  • the control unit has a cascade module which cascades the plurality of high-frequency pumps. By this is meant that the high-frequency pumps are switched on one after the other, as soon as higher powers are required.
  • the advantage of a cascade module is that power changes can be finer and faster tuned, since the power change is effected only by a high-frequency pump.
  • control unit has a status module that can determine the status of the expiratory valve and the pump arrangement. Furthermore, a communication module is provided for this purpose, which transmits the status signals between the pumps and the control unit. In this way, the control unit is enabled to determine the opening value of the expiratory valve and at the same time read out the power of the pumps. Thus, the control unit can at any time carry out a control of the pumps appropriate to the respective situation.
  • the pumping arrangement has a voltage source which supplies the pumping arrangement with two control voltages.
  • the pumping arrangement can be acted upon at any time with a low bias voltage. This low bias voltage is applied even when the pumping arrangement is not needed. As soon as power is then to be called up, the pump arrangement can provide power much faster than if no bias voltage were applied. This further increases the dynamics of the pumping arrangement.
  • the invention further relates to a retrofit kit for a device for ventilating a patient having an expiratory valve with a membrane element for transmitting a positive end-expiratory pressure, wherein the invention provides that the retrofit kit has a pumping arrangement for generating the positive end-expiratory pressure, the pumping arrangement for fluid-communicating connection with the membrane element is formed and has a high-frequency pump for generating the positive end-expiratory pressure.
  • the retrofit kit can advantageously have a coupling component with which the pumping arrangement can be connected to an expiratory valve of a device for ventilating a patient. Further developments of the retrofit kit can be taken from the above description.
  • the invention further relates to a control device for a pumping arrangement for a device for ventilating a patient according to the description given above, wherein the control device has an actual value signal input for an actual pressure signal and a desired value signal input for a desired pressure signal , wherein according to the invention it is provided that the control device is a comparator module, which is designed to determine the deviation between the actual pressure signal and the desired pressure signal, and a control signal output, which is designed to output a control signal to the pumping arrangement is, has.
  • the invention also relates to a method for controlling a pumping arrangement for a device for ventilating a patient according to the preceding description, wherein the device has a pressure sensor on the membrane element, with the steps according to the invention: detection of an actual pressure signal the membrane element with the pressure sensor; Determining a difference signal from the deviation of the actual pressure signal from a provided desired pressure signal; Changing a control voltage for the high-frequency pump in response to the difference signal.
  • the high-frequency pump operates at a frequency of at least 600 Hz, preferably at least 1000 Hz, more preferably at least 10000 Hz, more preferably at least 21000 Hz, more preferably 25000 Hz.
  • FIG. 1a, b a schematic representation of a device for breathing a patient
  • Figure 2 a schematic representation of a pumping arrangement according to the prior
  • FIG. 3 shows a schematic representation of a pump arrangement with a high-frequency pump
  • Figure 4 is a schematic representation of a pumping arrangement with a piezo pump, which can be flowed through in two directions;
  • Figure 5a, b a schematic representation of the operation of a piezo pump, which can be flowed through in two directions;
  • FIG. 6 a schematic representation of a pump stack
  • Figure 7 a schematic representation of a plurality of parallel connected
  • Figure 8 a schematic representation of a retrofit kit.
  • a device for ventilating a patient is referenced in its entirety by reference numeral 1.
  • the device comprises a respirator 3, which is connected via an inspiratory tube 17 by means of a coupling piece to the respiratory passages of a patient.
  • the coupling piece is in this embodiment, a mask 18 with Y-piece.
  • a tube (not shown) of an intubated patient can also be used.
  • an anesthesia machine can also be provided.
  • the Exspirati- onsventil 10 forms together with a pumping arrangement 2, a PEEP valve.
  • FIG. 1a shows an arrangement of the expiration valve 10 on the Y-piece of the mask 18.
  • the expiratory valve 10 can be integrated in the ventilator 3, as shown in FIG.
  • the pump arrangement 2 has a high-frequency pump 21.
  • the outlet port 37 of the pump 21 is connected to the flexible support component 14.
  • the High-frequency pump 21 has a relief valve 16 in order to be able to open the expiratory pressure at the beginning of the expiration phase. Through the relief valve 16, the pressure exerted by the high-frequency pump 21 on the membrane element 11 can be reduced.
  • the high-frequency pump 21 is arranged directly on the expiratory valve 10.
  • the high-frequency pump 21 can be coupled without a connecting hose to the flexible support component 14.
  • the high-frequency pump 21 sucks air via a suction opening 36, which is then introduced into the volume formed by the flexible support component 14 and the membrane element 11.
  • the high-frequency pump 21 is connected via a pump signal line 44 to a control unit 4. Via the pump signal line 44, the high-frequency pump 21 is controlled by the control unit 4.
  • a pressure sensor 46 is provided on the membrane element 1 1.
  • the pressure sensor 46 determines a control pressure actual value between the expiratory breathing gas flow and the volume formed by the membrane element 11 and the flexible support component 14.
  • the pressure sensor 46 is connected to the control unit 4 via a sensor signal line 45.
  • the pump signal line 44 connects a control signal output 48 with the high-frequency pump 21.
  • the sensor signal line 45 connects the sensor 46 with an actual value input 47 of the control unit 4.
  • the control unit 4 comprises a setpoint input 43. By means of the setpoint Input 43, the control unit 4 a control pressure setpoint for the positive end expiratory pressure transmitted means.
  • the control pressure setpoint can be input manually by a user or transmitted via a control signal line from a higher-level control.
  • control unit 4 comprises a status module 42 which determines the opening status of the expiratory valve 10. Depending on the opening status of the exhalation valve 10 and the comparison made by the comparator module 41 between the control pressure set value transmitted by the setpoint input and the control pressure actual value transmitted by the pressure sensor 46, a control signal is transmitted to the high-frequency pump 21.
  • the high-frequency pump 21 may be formed as a piezo pump. Piezo pumps are characterized by being particularly small and at particularly high frequencies can be operated.
  • the inner volume of the high-frequency pump 21 is less than 1 ml, preferably less than 0.5 ml. In this way, the compliance of the pumping arrangement 2 can be particularly reduced. Furthermore, the weight and cost savings are further increased.
  • FIG. 4 shows a further embodiment of the pump arrangement 2.
  • the high-frequency pump 21 has a two-way pump 20, which can be flowed through in two directions.
  • the pump geometry is chosen so that the pump assembly 2 no longer requires a relief valve.
  • the pumping arrangement 2 has a first two-way passage opening 22.
  • a fluid can either flow into the pumping arrangement 2 or flow out of the pumping arrangement 2 through the first two-way passage opening 22.
  • a two-way pump 20 is explained in more detail.
  • the two-way pump 20 is shown in a cross-sectional view.
  • the two-way pump 20 comprises an outer housing 24 with a second two-way passage opening 23.
  • the outer housing 24 has the first two-way passage opening 22.
  • the first two-way passage opening 22 is disposed on the opposite side of the second two-way passage opening 23 on the outer housing 24.
  • a piezo pump 29 is arranged within the outer housing 24.
  • the piezo pump 29 has a two-way pump opening 291.
  • the two-way pump opening 291 is arranged in alignment with the second two-way passage opening 23.
  • the two-way pumping port 291 and the second two-way port 23 have a common axis, so that a gas flow passing through the two-way pumping port 291 is directed through the second two-port port 23.
  • the piezo pump 29 is mounted in the outer housing 24 such that a flow channel 282 is formed between the first two-way passage opening 22 and the second two-way passage opening 23.
  • the piezo-pump 29 further has a piezo-element 27 which is mounted on a spring element 28 and fixedly connected to it.
  • the spring element 28 is connected via flexible connecting elements 281 with the piezo pump 29.
  • the spring element 28 and the piezo element 27 are connected via oscillator lines 251 to an AC voltage generator 25.
  • the piezo pump 29 is connected to a cover plate 26 of the two-way pump 20. As a result of the alternating voltage which is applied by the AC voltage generator 25 between the spring element 28 and the piezo element 27, the length extension changes.
  • the gas or fluid in the piezo-pump 29 is expelled through the two-way pumping opening 291. This creates a directed current. This is illustrated by the arrows according to FIG. 5b.
  • the directed fluid flow is expelled through the second two-way port 23. Due to the directed movement of the flow, the flow does not flow through the flow channel 282.
  • FIG. 6 shows a pump arrangement 2 which has a plurality of high-frequency pumps 21. These high-frequency pumps 21 are designed as two-way pumps 20.
  • the second two-way ports 23 of the two-way pumps 20 are respectively aligned with the first two-way ports 22 of a respective following two-way pump 20. Only the above two-way pump 20 has first two-way passage openings 22, which is not fed by a second two-way passage opening 23 of another two-way pump 20. Furthermore, the lowermost two-way pump 20 has a second two-way passage opening 23, which is not directed to a first two-way passage opening 22 of another two-way pump 20. Since each of the two-way pumps 20 has a free flow channel 282, only a single two-way pump 20 can be operated without blocking flow paths between the ambient air and the membrane element 11. The flow channels 282 form in this way a bypass around the piezo-pumps 29 in the two-way pump 20.
  • Each of the two-way pump 20 is connected to its own AC voltage generator 25 via an oscillator line 251.
  • the AC voltage generators 25 are connected to the control unit 4 via pump signal lines 44.
  • the AC voltage generators 25 are thus controlled via the control unit 4, the AC voltage generators 25 being controlled separately via a cascade module 52.
  • the two-way pumps 20 can produce a certain pressure in any combination.
  • a single two-way pump 20 may be operated at its maximum power, and another half-power pump or two three-quarters power pumps may be operated.
  • a common mode module 51 can be provided, with which the pumps are controlled so that all pumps operate with the same power.
  • the two-way pumps 20 are arranged in this embodiment in a stack housing 5.
  • the stack housing 5 is designed so that the two-way pumps 20 generate a common fluid flow.
  • the high-frequency pumps 21 are connected in parallel.
  • Each of the high-frequency pumps 29 generates its own fluid flow.
  • the high-frequency pumps 21 can be designed as two-way pumps 20.
  • the two-way pumps 20 each include its own AC generator 25, which is connected in each case via its own oscillator 251 to the respective two-way pump 20.
  • the AC generators 25 are connected via pump signal lines 44 to a control unit 4.
  • the control unit 4 can thus independently control the pumping power of each of the two-way pumps 20 by means of a cascade module 52 in this embodiment as well.
  • a common mode module 51 can be provided, with which the pumps are controlled so that all pumps operate with the same power.
  • an equally clocked or a cascaded control of the two-way pump 20 is also possible in this embodiment.
  • the invention is designed as a retrofit kit, which has a pumping arrangement 2 with a high-frequency pump 21.
  • the pumping arrangement 2 further has a coupling module 50, which is designed to provide a fluid-communicating, gas-tight connection with a membrane element 11 of a device 1 for ventilating a patient. to generate.
  • a retrofit kit is shown in FIG.
  • the retrofit kit 6 can be used to replace existing pneumatic actuators of membrane elements 11 of devices for breathing 1.
  • the connector 31 and the connecting tube 32 are removed and instead the retrofit kit 6 with the coupling module 50 attached to the flexible support component 14.
  • the retrofit kit 6 can also be equipped with a control unit 4.
  • the retrofit kit can also be designed for connection to an already existing control unit 4.
  • the retrofit kit further has a control signal input 53.
  • the method for controlling the pumping arrangement 2 may be performed by the control unit 4. Initially, the actual pressure on the membrane element 1 1 is detected by the pressure sensor 46 and converted into an actual pressure signal. The actual pressure signal of the pressure sensor 46 is transmitted to the control unit 4. Further, the control unit 4 is provided a target pressure signal. The control unit 4 then compares the desired pressure signal with the actual pressure signal by means of the comparator module 41. From the deviation between the two signals, the control unit 4 then determines a control signal for the control voltage of the high-frequency pumps 21 in order to minimize the deviation between the actual pressure signal and the desired pressure signal.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Engineering & Computer Science (AREA)
  • Mechanical Engineering (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Anesthesiology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Pulmonology (AREA)
  • Emergency Medicine (AREA)
  • Reciprocating Pumps (AREA)

Abstract

L'invention concerne un dispositif et un procédé de respiration artificielle sur un patient, lequel dispositif comprend une valve d'expiration (10) comprenant un élément membrane (11) destiné à transmettre une pression positive de fin d'expiration et un ensemble pompe (2) destiné à générer la pression positive de fin d'expiration, lequel est relié à l'élément membrane (11) de façon à assurer une communication fluidique, l'ensemble pompe (2) comprenant une pompe à haute fréquence (21) destinée à générer la pression positive de fin d'expiration. Grâce à cette invention, l'ensemble pompe (2) peut être fabriqué en petit format et de manière avantageuse. Par ailleurs, la structure du dispositif (1) est simplifiée.
PCT/EP2017/000229 2016-08-15 2017-02-17 Dispositif permettant de mettre un patient sous respiration artificielle et procédé pour faire fonctionner ce dispositif WO2018033224A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102016009833.3 2016-08-15
DE102016009833.3A DE102016009833A1 (de) 2016-08-15 2016-08-15 Vorrichtung zum Beatmen eines Patienten und Verfahren zum Betreiben der Vorrichtung

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WO (1) WO2018033224A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN112188911A (zh) * 2018-05-31 2021-01-05 德尔格制造股份两合公司 呼吸机和用于运行呼吸机的方法
DE102021111431A1 (de) 2020-06-29 2021-12-30 Dräger Safety AG & Co. KGaA Überwachungssystem

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102018005318A1 (de) * 2018-07-05 2020-01-09 Dräger Safety AG & Co. KGaA Verfahren und System zum Sensieren eines Gases, Steuerungseinrichtung mit einer Implementation des Verfahrens

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