WO2003059426A2 - Procede de determination d'une pression de masque en vue de la regulation de la pression dans un appareil de cpap, procede de determination du flux d'air et / ou de la pression d'air dans un appareil de cpap, appareil de cpap et equipement de verification pour ledit appareil - Google Patents

Procede de determination d'une pression de masque en vue de la regulation de la pression dans un appareil de cpap, procede de determination du flux d'air et / ou de la pression d'air dans un appareil de cpap, appareil de cpap et equipement de verification pour ledit appareil Download PDF

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Publication number
WO2003059426A2
WO2003059426A2 PCT/DE2003/000015 DE0300015W WO03059426A2 WO 2003059426 A2 WO2003059426 A2 WO 2003059426A2 DE 0300015 W DE0300015 W DE 0300015W WO 03059426 A2 WO03059426 A2 WO 03059426A2
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WO
WIPO (PCT)
Prior art keywords
pressure
cpap device
cpap
motor
airflow
Prior art date
Application number
PCT/DE2003/000015
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German (de)
English (en)
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WO2003059426A3 (fr
Inventor
Martin Baecke
Harald Genger
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Seleon Gmbh
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 Seleon Gmbh filed Critical Seleon Gmbh
Priority to DE10390059T priority Critical patent/DE10390059D2/de
Priority to AU2003235692A priority patent/AU2003235692A1/en
Publication of WO2003059426A2 publication Critical patent/WO2003059426A2/fr
Publication of WO2003059426A3 publication Critical patent/WO2003059426A3/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
    • A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
    • A61M16/022—Control means therefor
    • A61M16/024—Control means therefor including calculation means, e.g. using a processor
    • A61M16/026—Control means therefor including calculation means, e.g. using a processor specially adapted for predicting, e.g. for determining an information representative of a flow limitation during a ventilation cycle by using a root square technique or a regression analysis

Definitions

  • Method for determining a mask pressure for pressure regulation in a CPAP device Method for determining the air flow and / or air pressure in a CPAP device, CPAP device and test apparatus therefor
  • the invention relates to a method for pressure regulation in a CPAP device according to the preamble of patent claim 1.
  • the invention relates to a method for determining the air flow in a CPAP device according to the preambles of claims 6 and 7 and a CPAP device according to the preamble of claim 13 and a test apparatus according to claim 14.
  • Obstructive respiratory disorders lead to apneas (Respiratory arrest) through which the sleeper awakens. Frequent apneas prevent the sleeping person from relaxing in deep sleep. People who suffer apneas during sleep are therefore no sleep during the day, which can lead to social problems in the workplace and in the worst case to fatal accidents, for example in professional drivers.
  • CPAP continuous positive airway pressure
  • a CPAP device generates a positive overpressure of up to about 30 mbar by means of a blower, which is also referred to as a compressor, compressor or turbine, and preferably applies this via a humidifier, via a breathing tube and a face or nose mask in the patient's airways , CPAP devices intended to be used with a nasal mask are also referred to as nCPAP devices, where n stands for "nasal.”
  • This overpressure is intended to ensure that the upper respiratory tracts remain completely open during the entire night and thus no apneas occur (DE 198 49 571 A1).
  • the required overpressure depends, among other things, on the sleep stage and the body position of the sleeping person.
  • a differential pressure sensor detects the pressure of the air delivered to the patient directly in the device.
  • the pressure difference is measured for a commonly used combination of breathing tube and mask at a medium flow rate. This difference value is subtracted from the pressure measured in the device and the result is interpreted as a mask pressure.
  • the pressure in the face mask or nasal mask during inhalation is lower than during exhalation. Therefore, especially in this form of pressure control, the patient has the feeling of having to breathe against resistance.
  • a change in the face mask due to compatibility issues, additional leakage due to damage, change in breathing tube length when replacing the breathing tube, and kinking in the tube will not cause the device to react, i. the mask pressure is not set correctly.
  • the pressure detection takes place in the vicinity of the end of the breathing tube in front of the mask or in the mask.
  • the pressure detection is very accurate, the pressure control compensates even leaks etc.
  • the pressure measurement itself can be carried out with a pressure sensor, the electrical connection wires with the breathing tube to the ventilator must be performed.
  • a separate thin tube from the measuring point to a pressure sensor located in the CPAP device.
  • a disadvantage of these variants is that special hoses are needed to allow the return of the connecting wires or the hose into the CPAP device.
  • These custom-made products are more expensive than normal breathing tubes.
  • their use with other CPAP devices is limited. Finally, the cleaning is more complicated.
  • DE 96 101 100 T2 discloses two embodiments for a long-term ventilatory support device. Both embodiments differ essentially by the position of the pressure measurement, namely according to the first embodiment in the mask and according to the alternative embodiment approximately in the middle of the air supply hose and by the flow measurement by a Pneumotachograp en s in the first embodiment in the vicinity the mask and in the alternative embodiment in the vicinity of a blower. Because of these differences, the alternative embodiment is the more relevant one.
  • the blower is driven by a blower motor driven by a motor servo controlled by a microprocessor to which the flow signal from a differential pressure transducer and the pressure signal from a pressure transducer are fed.
  • the mask has an outlet.
  • the air flow and the pressure at the outlet of the turbine is measured and the pressure in the mask is calculated taking into account the pressure drop at the air supply hose.
  • the following operations are executed every 20 milliseconds: measuring a flow at a flow sensor and a pressure at a pressure detection port; Calculating a mask pressure and a flow of the sensor pressure and the flow; Calculating a conductivity of the mask leak; Adding a loss of tube pressure to the EPAP pressure.
  • the hose pressure loss is calculated as tube resistance * flow 2 .
  • the conductivity of the leak is calculated from a low-pass filtered mask air flow and the low-pass filtered square roots of the mask pressure.
  • a blower unit in one embodiment, generates an overall constant volume of respirable gas per unit of time, which is selectively vented through a vent end or supplied to the patient.
  • the vent end can be closed by a valve element of different widths.
  • the valve element is rotated by a stepper motor.
  • a microprocessor controller To control the fan motor, a microprocessor controller generates a pulse width modulated signal. This is converted to an analog voltage by a low pass filter formed of a resistor and a capacitor which is fed to the motor driver.
  • the blower motor is equipped with a Hall effect converter, whose output pulses are fed to a frequency-voltage converter, which consists of several capacitors and resistors and a diode, so that the motor driver, a second voltage signal is supplied.
  • a gas humid CPAP system delivers humidified and compressed gases to a patient through a nasal mask connected to a humidified gaseous transport line or to a breathing tube.
  • a controller receives input signals from a set screw with which a user of the device e.g. sets a required value of the humidity or temperature of the gases.
  • the controller may also receive input signals from other sources, e.g. obtained from flow velocity sensors.
  • a respiration device comprises a CPAP device with a pressure generator and possibly an additional control circuit and an actuating device.
  • DE 199 40 070 A1 discloses a system for monitoring patients with sleep disorders.
  • therapy-relevant parameters are determined by means of sensors and can be transmitted via a communication network to a spatially separated monitoring, analysis and control device.
  • the therapy devices may be a CPAP device. It is an object of the invention to provide a method for a less expensive CPAP device, in which the pressure in the respiratory mask is regulated to a target pressure set in the CPAP device.
  • An advantage of the invention is that the manufacturing costs of the CPAP device decrease, because no special ventilation hoses must be used.
  • An advantage of measuring the pressure in the CPAP device at a point in time when the air flow is zero is that no pressure drops on the breathing tube and therefore the pressure in the mask is measured in the CPAP device.
  • An advantage of measuring the pressure at a time when the air flow is just equal to the average air flow, is that at this time of the breathing air flow from or to the patient is equal to zero.
  • An advantage of the determination of the air flow over an integer number of respiratory cycles is that the mean value is not falsified by inhalation or exhalation and thus the average value of the air flow even with a short averaging time is independent of the averaging time.
  • An advantage of using the negative spikes of the airflow dissipation to divide the airflow into respiratory cycles is that these peaks are particularly pronounced, allowing accurate separation of the respiratory cycles.
  • the advantage of determining the air flow from two of the measurements, motor voltage, motor current, fan speed, and the pressure supplied by the fan is that no additional flow sensor is required in an auto-CPAP device. This leads to a significant reduction in manufacturing costs, since unlike competing products, an expensive flow sensor in the device can be dispensed with.
  • An advantage of the evaluation of both the motor voltage and the motor current in addition to a pressure measurement is that thereby further fault conditions, such as wear, can be determined in a CPAP device.
  • the pressure in the CPAP device and the air flow can be determined from two of the measured quantities of motor voltage, current through the motor and engine speed using a characteristic field.
  • An advantage of the calculation of a characteristic field by the test apparatus, from which the air flow can be calculated at a given pressure and given motor voltage, is that the computing power required for this computation-intensive method does not have to be integrated in a CPAP device.
  • An advantage of a combination of the calculation of the air flow from the blower voltage and the measured pressure and the consideration of the falling pressure on the breathing tube is that without additional hardware, such as flow sensor, connection cable or hoses to the face mask, a target pressure in the mask can be maintained with high accuracy.
  • Fig. 1 shows a CPAP device in therapy use
  • Fig. 2 is a schematic diagram of a CPAP device
  • FIG. 3 shows the block diagram of a test apparatus according to the invention
  • FIG. 4 shows the block diagram of a test apparatus according to the invention with two turbines
  • FIG. 5 shows the block diagram of a test apparatus according to the invention with a lung simulator.
  • Fig. 1 shows a CPAP device 1 in therapy use.
  • the CPAP device 1 contains a blower 2.
  • a differential pressure sensor 3 is provided for measuring the overpressure generated by the blower relative to the ambient pressure.
  • the air conveyed by the fan is supplied via a breathing tube 4 to a face mask 5, which the patient 6 carries himself.
  • the face mask 5 can cover either mouth and nose or only nose.
  • an exhalation opening 7 is provided through which a continuous flow of air from the breathing tube takes place in the environment.
  • This air flow ensures that the air exhaled by the patient is vented to the environment and prevents the accumulation of 4 C0 2 in the breathing tube.
  • the pressure drop across a hose such as the breathing tube 4 can be calculated from the following formula (Technical Fluid Mechanics 1, VEB Deutscher Verlag für Grundstoffindustrie, für).
  • ⁇ p is the pressure falling on the hose
  • ⁇ is a pressure loss coefficient of the hose
  • ⁇ is a pipe friction value of the hose
  • I is the length of the hose
  • p is the density of the flowing medium, ie approx. 1.2 kg / m 3 for air for CPAP devices
  • v is the averaged cross-sectional flow velocity from the CPAP device toward the mask
  • a is 2 for turbulent flows and 1 for laminar flows.
  • a can also assume intermediate values because there is seldom an ideal-typical flow form. in the
  • Equation (1) is also known from Fluid Dynamics, J.H. Spurk, 4th edition, Springerverlag, Berlin, 1996, where ⁇ is referred to as a resistance number.
  • V v - ⁇ - (d / 2) 2 (2)
  • V itself stands for an air volume.
  • the dot denotes the derivative after time d / dt.
  • V can be detected by a flow sensor 9 or, as will be explained below, calculated from the pressure measured by the differential pressure sensor 3 and the motor voltage.
  • the constant C in equation (3) is first determined from the pressure loss coefficient ⁇ of the breathing tube. In this way, only equations (3) and (4), but not equation (1), need to be calculated frequently.
  • the CPAP device is equipped with a non-volatile memory in which the constant C or the pressure loss coefficient ⁇ are stored after their calculation.
  • the constant C 0 and / or the pressure loss coefficient ⁇ 0 for a standard breathing tube are stored in a read-only memory (ROM) in the event that the pressure loss at value ⁇ or the constant C are nevertheless deleted. As the patient exhales, there is a backflow of air in the air
  • the volume flow V assumes negative values for a short time.
  • the supplied by fan 2 airflow V is divided into a patient going
  • _ a direct function of the mask pressure p M. It flows out of a fixed opening 7 in the mask or in the vicinity of the mask and serves to dispose of the carbon dioxide exhaled by the patient.
  • the respiratory air flow VA is zero on average over time, as the patient inhales the same amount of air as exhales:
  • V A From V
  • VL ⁇ V- d ⁇ (6)
  • a suitable time interval T is in particular an integer number of breathing cycles.
  • the first derivative of the respiratory flow curve is estimated for the detection of individual breathing cycles. Due to noise in the measured airflow, the airflow curve is not only derived according to time, but additionally low-pass filtered.
  • the derivative and low pass filtering is done in a filtering step by suitable choice of the coefficients of a digital filter and is called the derivative of the derivative.
  • the negative peaks in the estimated derivative of the airflow have proven to be a robust demarcation criterion between the various breathing cycles.
  • the mask pressure p is just the pressure drop across the exhalation port.
  • _ the pressure loss coefficient ⁇ L can the leakage aperture by means of equation (1) or a corresponding value of C L in equation (3) can be determined.
  • the mask pressure becomes constant and equal to
  • the pressure loss coefficient ⁇ or the constant C for the breathing tube can be determined from the total volume flow V and the pressures p and p M
  • Leakage current VL can be used to check for leaks that may vary with time, such as a misplaced face mask or leaking or damaged connections.
  • the airflow V can be measured by a flow sensor in the CPAP device.
  • the air flow is determined by evaluating the supply voltage U for the motor for the device-internal fan 2, and measured in the device in the vicinity of the air outlet by the differential pressure sensor 3 pressure p.
  • a function of the volume flow over time is determined by means of the stored characteristic field.
  • a characteristic field can be recorded by the manufacturer by means of a test apparatus, which determines the relationship between motor voltage
  • V f (p, U) (6)
  • the characteristic field also covers a certain range of negative volume flows.
  • the characteristic field stores air flows Vjj, pressures Pi and voltages U j ,
  • FIG. 2 shows a block diagram of a preferred CPAP device.
  • the block diagram shows a central processing unit 23, to which the output signal of the differential pressure sensor 3 is supplied, which is digitized in the analog-to-digital converter 24.
  • the central processing unit 23 outputs a value proportional to the motor voltage 25 to the digital analog converter 22.
  • the analog voltage output from the digital-to-analog converter 22 is amplified by the motor driver 21 and supplied to the motor 11.
  • the motor 11 then drives the blower 2.
  • the rotor of the motor and the impeller or propeller of the fan are mounted on a shaft so that the engine speed is equal to the fan speed.
  • the central processing unit 23 is constantly running a program that compares the pressure measured by the pressure sensor 3 with a determined from equation (4) setpoint pressure and readjusted the motor voltage.
  • the program preferably implements a PID controller.
  • an electrical connection 26 may be provided, which is preferably designed as an RS-232 interface.
  • the CPAP device may include a resistor 27 for measuring the electrical current flowing through the motor 11. At the resistor 27 drops a current through the motor 11 proportional voltage. This is digitized in this embodiment by the digital-to-analog converter 28 and the central processing unit 23 is supplied. As will be explained in more detail below, from two of the measured quantities of motor voltage, by the motor
  • flow and fan speed determine both the pressure in the CPAP device and the airflow generated by the CPAP device.
  • a calculation of the pressure due to two of the measured quantities may make the pressure sensor 3 and the analog-to-digital converter 24 superfluous. Capture of two of the above metrics along with the pressure allows for a high degree of functional control of the CPAP device. So, for example
  • the central processing unit 23 in cooperation with the digital-to-analog converter 22 and the motor driver 21 generates the motor voltage, it is not necessary to measure the motor voltage itself. Rather, the motor voltage can be calculated from the value output to the digital-to-analog converter 35 22 by the central processing unit.
  • a pulse width modulated signal is output, instead of the digital / analog converter Transducer output value, the duty cycle of the pulse width modulated signal can be used as a motor voltage proportional signal.
  • the characteristic field can be stored so that instead of the measured pressure and the measured motor voltage read out by the analog-to-digital converter 24 pressure value and the output to the digital-to-analog converter 22
  • Fig. 3 shows a schematic diagram of a test apparatus according to the invention.
  • the test apparatus comprises an air connection 31, with which the test apparatus can be connected via a breathing tube 4 with a CPAP device.
  • the test apparatus has a flow sensor 36 and an electrically controllable valve 32.
  • the valve 32 can be controlled via a digital-to-analog converter 33 by a central processing unit 34.
  • the flow sensor 36 forms with the resistors 37 to 39, a measuring bridge whose detuning amplified by the differential amplifier 40, digitized in the analog-to-digital converter 41 and the central processing unit 34 is supplied.
  • a keyboard 43 for input and a display 42 for displaying the operating state of the test apparatus are provided.
  • an electrical interface 35 is provided for data exchange with the CPAP device to be tested.
  • a test method may be as follows. In an outer loop, different resistance values W
  • Characteristic field preferably a characteristic curve described above field Vy for the pressures pi and the voltages U j in the test apparatus by the central processing unit 34 calculated.
  • the bilinear interpolation explained above with reference to equation (7) can be used if the measurement points W k and pi are close enough. Since sufficient computing power is generally available in the test apparatus, more sophisticated higher-order interpolation methods than bilinear interpolation can also be implemented.
  • Test apparatus are stored, which are already chosen so that the resistance value W k
  • Characteristic field Vy for the CPAP device Due to the manufacturing tolerances in the manufacture of the CPAP devices, the resistance values W w can not be selected so that the voltages U w for all the corresponding pressures p k are the same for all CPAP devices. That's why
  • Vy can not be waived.
  • is recalculated based on the old resistance values W k
  • the calculated characteristic field is preferably stored in the CPAP device.
  • the electric current I can also be used by the motor 11. Equations 6 and 7 remain valid, but the voltage U is to be replaced by the current I. Also in the characteristic curves, the motor voltage U w is to be replaced by the current l w and U j by l j .
  • Equation 8 Equation 8
  • V g (l, U) (8)
  • test method similar to that described above, which can be carried out, for example, in the context of a final inspection, can at the valve of the test apparatus different resistance W k and in the CPAP device different motor voltages U
  • W k different resistance
  • U different motor voltages
  • Pressure in equation (7) is to replace the flow V by the pressure p, the pressure p by the current I and the function f by the function h.
  • CPAP devices Another size that is easy to measure with some CPAP devices is the speed of the fan and the motor driving the fan. These CPAP devices are often equipped with a contactless 3-phase DC motor.
  • the motor has Hall sensors that provide output signals to drive the motor windings in phase. To determine the speed of the motor either the signals supplied by the Hall sensors or the voltage applied to the motor windings voltages can be used.
  • the engine speed can replace the current I in equations 8 and 9 to give equations 10 and 11:
  • V g (n, U) (10)
  • the pressure p is, in a good approximation, proportional to the working range of CPAP devices
  • Test equipment or on the CPAP device can be set one after the other.
  • Test equipment or on the CPAP device can be set one after the other.
  • a resistance field W w can also be specified so that the rotational speed n k
  • U j can be calculated so that air flow V and pressure p can be calculated quickly by means of bilinear interpolates (see equation (7)). The latter fields are then stored in the CPAP device.
  • the speed may be used in conjunction with the current I.
  • V g (n, l) (12)
  • resistance values W k and voltage values U be set one after the other on the test apparatus or on the CPAP device.
  • W k and voltage values U be set one after the other on the test apparatus or on the CPAP device.
  • Characteristic fields namely one each for the air flow Vkl, for the pressure p Ml for the current through the motor l M and the engine speed n w measured.
  • Vkl the air flow
  • p Ml the pressure of the air flow
  • n w the engine speed
  • Resistance values W w and for voltage values U w are given so that the measured currents l k
  • resistance values W w and voltage value U M can also be specified so that the currents I k for fixed I and the speeds n M for fixed k are approximately the same.
  • the resistance field W w and the voltage field U w can be like
  • the CPAP device typically provides an air inlet filter and silencer with soundproofing foam in the air inlet area.
  • the air inlet filter may become clogged with dust in the ambient air over time, such that it has a slowly increasing air resistance over time.
  • the soundproofing foams can also change, for example due to water retention, and thus change the air resistance of the air inlet.
  • the pressure p and the air flow V can be calculated from the engine speed n and the
  • Characteristic field l k and a current characteristic field I , be calculated and stored so that an (original) current value in dependence on the engine speed n and the motor voltage U from the field l, j can be calculated. This can then be compared with the measured current value I.
  • Motor voltage U, current through the motor I and motor speed n can not be excluded that an increase in the measured current I compared to a calculated current value due to aging in the air inlet area.
  • the four variables pressure p, motor voltage U, current be measured by the engine I and engine speed n, so information about the Aging of the air intake, in particular the air inlet filter and the engine and fan bearings, are obtained.
  • the test apparatus is equipped with a differential pressure sensor that measures the differential pressure between the pressure generated by the CPAP device and the ambient pressure .
  • a pressure sensor may be arranged, for example, in the vicinity of the flow sensor 36.
  • the electrical output signal of the pressure sensor is digitized by a further analog-to-digital converter and fed to the central processing unit 34. If the characteristic curves are recorded with the breathing tube, which is also used during the therapy use of the CPAP device, the pressure sensor of the testing device essentially measures the pressure which is established in the mask during the therapy. Thus, a correction for the decreasing pressure on the breathing tube, as explained above with reference to equations (1) to (4) omitted.
  • the characteristics fields stored in the CPAP device are calculated in such a way that the characteristic fields result in mask pressure.
  • the pressure in the CPAP device is first determined from equations (1) to (4) and the constant C or the pressure loss coefficient ⁇ for the respiratory flow used in the recording of the characteristic curves calculated.
  • the pressure map which is finally stored in the CPAP device, is calculated to give the pressure in the CPAP device.
  • the pressure calculated from the characteristic field is then corrected by the pressure drop across the breathing tube, as explained above. If the pressure loss coefficient of the respiration tube used in the therapy is known when recording the characteristic fields, a characteristic field can be calculated and stored in the CPAP device during or immediately after the recording of the characteristic curves from which the mask pressure results directly.
  • FIG. 4 A further preferred embodiment of the test apparatus is shown in FIG. 4.
  • This embodiment has, in addition to a test apparatus according to FIG. 3, the fans 51 and 53.
  • the speed of the fans can be controlled by the central processing unit 34.
  • the digital-to-analogue converters 52 and 54 are shown in FIG. 34 for this purpose.
  • the air connection 31 can be connected either to the blower 51 or to the blower 53.
  • the control of the two-way valve 50 via the digital control lines 55 and 56 by the central processing unit 34.
  • the inhalation of the patient is simulated by the blower 53, which can generate a negative pressure relative to the ambient pressure.
  • the exhalation of the patient is simulated by the blower 51.
  • This fan creates an overpressure against the Ambient pressure and provides a negative flow when the pressure generated by the blower 51 is higher than the overpressure generated by the blower of the CPAP device.
  • this test apparatus contains a lung simulator 60.
  • the lung simulator consists essentially of a cylinder in which a piston can be moved up and down in a controlled manner. This can be done for example by the wheel 63 eccentrically mounted connecting rod. The wheel 63 may be driven, for example, by a DC or stepper motor.
  • the digital-to-analog converter 61 for controlling a DC motor is shown as an example.
  • the throttle valve 32 is shown in Fig. 5, which can be controlled via the digital-to-analog converter 62.
  • the throttle valve 32 simulates different sized exhalation openings 7 in or at the mask 5 of the patient.
  • an equally large pressure and flow range can be traversed for calculating the characteristic field (s).
  • a particular advantage of the embodiment according to FIG. 5 is that few breathing cycles simulated by the lung simulator 60 are sufficient to determine a sufficiently dense characteristic field for a CPAP device.
  • the piston in the lung simulator can be moved up or down at a constant speed
  • closed valve 32 of the air flow V can be calculated, so that the flow sensor 36, the resistors 36 to 39, the differential amplifier 40 and the analog-to-digital converter 41 can be omitted.
  • an additional pressure sensor may preferably be provided in the vicinity of the flow sensor 36.
  • Such a pressure sensor makes it possible to calibrate the pressure sensor used in the CPAP device, that is to record a characteristic for the pressure sensor in the CPAP device, for example. This allows the use of less accurate and thus cheaper pressure sensors in the CPAP devices.
  • this additional pressure sensor also allows a functional check of the pressure sensor in the CPAP device to be tested.

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  • Health & Medical Sciences (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measuring Volume Flow (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Measuring Fluid Pressure (AREA)

Abstract

Procédé de régulation de la pression dans un appareil de ventilation spontanée en pression positive (CPAP). Pour ajuster la pression effective dans un masque facial afin d'obtenir une pression thérapeutique, la chute de pression produite par un flux d'air dans un tube respiratoire est calculée et sur la base de cette valeur, une pression désirée pour un capteur de pression logé dans le boîtier de l'appareil CPAP est calculée de manière répétée. La présente invention concerne en outre un procédé de calcul d'un flux d'air à partir de la surpression produite par la soufflante d'un appareil de CPAP et de la tension de moteur du ventilateur, ce qui permet d'économiser un capteur de pression. La présente invention concerne enfin un appareil de CPAP ainsi qu'un équipement de vérification correspondant.
PCT/DE2003/000015 2002-01-04 2003-01-02 Procede de determination d'une pression de masque en vue de la regulation de la pression dans un appareil de cpap, procede de determination du flux d'air et / ou de la pression d'air dans un appareil de cpap, appareil de cpap et equipement de verification pour ledit appareil WO2003059426A2 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
DE10390059T DE10390059D2 (de) 2002-01-04 2003-01-02 Verfahren zur Bestimmung eines Maskendrucks zur Druckregelung in einem CPAP-Gerät, Verfahren zur Bestimmung des Luftstroms und/oder Luftdrucks in einem CPAP-Gerät, CPAP-Gerät sowie Prüfapparatur dafür
AU2003235692A AU2003235692A1 (en) 2002-01-04 2003-01-02 Method for determining a mask pressure, air flow and/or air pressure in a cpap device, cpap device and corresponding test equipment

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10200183A DE10200183A1 (de) 2002-01-04 2002-01-04 Verfahren zur Bestimmung eines Maskendrucks zur Druckregelung in einem CPAP-Gerät, Verfahren zur Bestimmung des Luftstroms und/oder Luftdrucks in einem CPAP-Gerät, CPAP-Gerät sowie Prüfapparatur dafür
DE10200183.9 2002-01-04

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WO2003059426A2 true WO2003059426A2 (fr) 2003-07-24
WO2003059426A3 WO2003059426A3 (fr) 2004-01-15

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DE69101100T2 (de) 1990-10-22 1994-08-11 Kuhn Sa Landwirtschaftliche Bodenbearbeitungsmaschine mit einem quer zur Arbeitsrichtung angeordneten Rotor.
DE69132030T2 (de) 1990-12-21 2000-10-19 Puritan Bennett Corp Drucksystem für atmungswege
DE19928003A1 (de) 1998-06-19 2000-02-17 Fisher & Paykel Atmungsunterstützungsvorrichtung
DE19849571A1 (de) 1998-10-27 2000-05-04 Map Gmbh Verfahren zur Beurteilung des anliegenden Luftdrucks bei der automatisierten Beatmung durch positiven Luftdruck auf die Atemwege
WO2000066207A1 (fr) 1999-05-04 2000-11-09 MAP Medizintechnik für Arzt und Patient GmbH & Co. KG Dispositif pour acheminer un gaz de respiration en surpression et systeme de commande pour le piloter
DE19940070A1 (de) 1999-08-24 2001-03-22 Mpv Truma Ges Fuer Medizintech Anlage zur Überwachung von Patienten mit Schlafstörungen
DE10103973A1 (de) 2001-01-30 2002-08-01 Peter L Kowallik Verfahren und Vorrichtung zur Schlafüberwachung

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104069574A (zh) * 2013-03-29 2014-10-01 北京谊安医疗系统股份有限公司 一种以控制输出压力为目标的涡轮控制方法及控制装置

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WO2003059426A3 (fr) 2004-01-15

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