JP2006000131A - Medical device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a medical device which consumes a relatively small amount of electricity and uses a battery efficiently. <P>SOLUTION: A pressure fluctuation inside a cannula 3 due to breath of a patient is detected by a pressure sensor 5 via an electromagnetic valve 2. A CPU 8 blocks electric power supply to the pressure sensor 5 and an LED 16 and supplies driving power to the electromagnetic valve 2 when sensing the breath of the patient upon receiving signals from the pressure sensor 5. The CPU 8 supplies retained power smaller than the driving power and resumes electric power supply to the pressure sensor 5 and the LED 16 after supplying the driving power to the electromagnetic valve 2. Since the relatively large driving power to the electromagnetic valve 2 and the power supplied to the pressure sensor 5 and the LED 16 are not overlapped, a substantial voltage drop of the battery is prevented. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to a medical device such as a respiratory synchronizer that supplies oxygen in synchronism with respiration to a patient having a lung disease or the like.

  Conventionally, as this type of medical device, an oxygen supply port connected to an oxygen cylinder, a cannula port connected to a cannula worn by a patient, and a pressure sensor that detects the pressure in the cannula fluctuating depending on the patient's breathing And an electromagnetic valve that switches and communicates the cannula port with either the oxygen supply port or the pressure sensor, and a control circuit that controls switching of the electromagnetic valve based on a signal from the pressure sensor There is a home respiratory synchronizer (see, for example, Japanese Patent Application Laid-Open No. 2001-29472).

  The respiratory synchronizer operates as follows. That is, the solenoid of the solenoid valve is excited by the excitation signal from the control circuit, the valve body position of the solenoid valve is switched, and the pressure sensor communicates with the cannula. The pressure sensor detects the pressure in the cannula according to the patient's respiratory cycle. When the control circuit detects the start of inhalation of the patient based on the signal from the pressure sensor, the control circuit stops the excitation signal to the electromagnetic valve and demagnetizes the solenoid. Thereby, the valve body position of the solenoid valve is switched, and the cannula is communicated with the oxygen cylinder, and oxygen is supplied from the oxygen cylinder to the patient via the cannula. The control circuit outputs an excitation signal to the electromagnetic valve and switches the electromagnetic valve when the predetermined time has elapsed since the cannula communicated with the oxygen cylinder, and communicates the cannula with the pressure sensor. By repeating such switching of the solenoid valve, oxygen is intermittently supplied in synchronization with the patient's breathing.

  This type of respiratory tuner uses a commercially available dry cell with a rated voltage of 1.5 V as a power source, thereby facilitating battery replacement and reducing the weight of the respiratory tuner.

  However, when the cannula communicates with the pressure sensor, the breathing tuner continues to output the excitation signal to the solenoid valve, so that the power consumption is relatively large and the battery is consumed in a relatively short time. There is a problem of doing. This relatively large amount of power consumption is caused by supplying driving power to the pressure sensor in addition to the output of the excitation signal to the solenoid valve.

This problem becomes prominent when, for example, only one AA or AA battery is used with a relatively small battery capacity in order to improve the portability of the respiratory synchronizer.
JP 2001-29472 A

  Accordingly, an object of the present invention is to provide a medical device that consumes relatively little power and can use a battery efficiently.

In order to solve the above problems, the medical device of the present invention is
A solenoid valve interposed in the flow passage for supplying oxygen to the cannula;
A respiratory phase sensor for detecting the respiratory phase of the patient;
Sensor power supply means for supplying power to the respiratory phase sensor;
Switching control means for controlling switching of the solenoid valve based on the output of the respiratory phase sensor;
Electromagnetic valve power supply means for supplying driving power to the electromagnetic valve when switching the electromagnetic valve, and supplying holding power smaller than the driving power when holding the electromagnetic valve;
Sensor power supply means for supplying power to the respiratory phase sensor;
When the electromagnetic valve power supply means supplies the drive power to the electromagnetic valve, the electromagnetic valve power supply means includes a power cutoff means for cutting off power supply to the respiratory phase sensor by the sensor power supply means.

  In the above configuration, the respiratory phase of the patient is detected by the respiratory phase sensor. The respiratory phase sensor is preferably a pressure sensor that detects pressure fluctuations in the cannula via, for example, a cannula worn by the patient. The switching control unit controls switching of the electromagnetic valve based on an output signal from the respiratory phase sensor. For example, when the respiratory phase sensor detects that the patient's breathing has changed from exhalation to inspiration, the switching control means switches, for example, the closed electromagnetic valve to an open state. Thus, for example, an oxygen source connected to the flow passage is communicated with the cannula. Thus, the patient is properly supplied with oxygen.

  The solenoid valve power supply means supplies drive power to the solenoid valve when the solenoid valve is switched. On the other hand, when the switching of the solenoid valve is completed and the solenoid valve is held open, holding power is supplied to the solenoid valve. Since this holding power is smaller than the driving power, the power consumption of the medical device is smaller than that of the conventional device. Therefore, when this medical device is driven by a battery, the consumption rate of the battery can be reduced, and the battery can be used for a longer time than before.

  The respiratory phase sensor is supplied with electric power by a sensor electric power supply means. The electric power supply to the respiratory phase sensor is interrupted when the electromagnetic valve electric power supply means supplies the driving electric power to the electromagnetic valve. Blocked by means. Thereby, it is possible to prevent the supply of the relatively large driving power to the electromagnetic valve and the power supply to the breathing phase sensor at the same time. Therefore, since it is possible to prevent the power consumption of the medical device from increasing significantly, for example, when a battery is used as a power source, it is possible to prevent an excessive voltage drop of the battery. As a result, the battery can be used for a longer time than before.

  The power shut-off means is not limited to stopping the power supply only to the respiratory phase sensor. For example, power supply to other components such as a battery warning or an LED indicating the operating state of the medical device is provided. May be stopped. As a result, it is possible to prevent the relatively large drive power supply and the power supply to the other components from being performed at the same time, so that an excessive voltage drop of the battery can be effectively prevented.

  The electromagnetic valve may be supplied with holding power when the closed state is maintained.

  In the medical device of one embodiment, the holding power supplied to the solenoid valve by the solenoid valve power supply means is power having a duty ratio smaller than the duty ratio of the drive power.

  According to the embodiment, the solenoid valve power supply means supplies the holding power having a duty ratio smaller than the duty ratio of the drive power to the solenoid valve. Therefore, the power consumption when maintaining the switching state of the solenoid valve is smaller than in the prior art. Further, since the holding power is made smaller than the driving power by changing the duty ratio, power loss when generating the holding power can be reduced. Therefore, for example, when the battery is used as a power source, the consumption amount of the battery can be effectively reduced.

  In the medical device according to an embodiment, the holding power supplied to the solenoid valve by the solenoid valve power supply unit is a power having a voltage value smaller than a voltage value of the driving power.

  According to the embodiment, the electromagnetic valve power supply means supplies the holding power having a voltage value smaller than the voltage value of the driving power to the electromagnetic valve. Therefore, the power consumption when maintaining the switching state of the solenoid valve is smaller than in the prior art. Therefore, it is possible to effectively reduce the amount of battery consumption when a battery is used as the power source.

  The voltage values of the driving power and the holding power are rated voltage values when the driving power or the like is alternating current.

  In the medical device according to one embodiment, the power cutoff unit supplies power to the respiratory phase sensor by the sensor power supply unit until a predetermined period elapses after the electromagnetic valve power supply unit outputs the holding power. Shut off.

  According to the embodiment, when the electromagnetic valve is switched and communication between the respiratory phase sensor and the cannula is interrupted, for example, the pressure value that the respiratory phase sensor should detect for a predetermined period after the switching of the electromagnetic valve. Becomes unstable. Here, until the predetermined period elapses after the electromagnetic valve power supply means outputs the holding power, the power cutoff means cuts off the power supply to the respiratory phase sensor by the sensor power supply means. For example, the respiratory phase sensor can be prevented from detecting unstable pressure. Therefore, it is possible to prevent the detection value of the respiratory phase sensor from becoming unstable.

  As described above, in the medical device of the present invention, the respiratory phase of the patient is detected by the respiratory phase sensor, and switching of the electromagnetic valve is controlled by the switching control means based on the output signal from the respiratory phase sensor. The electromagnetic valve power supply means supplies driving power to the electromagnetic valve when the electromagnetic valve is switched, while holding power is supplied to the electromagnetic valve when the electromagnetic valve is held. When the solenoid valve power supply means supplies the drive power to the solenoid valve, power supply to the breathing phase sensor by the sensor power supply means is interrupted by the power cutoff means. This prevents a relatively large amount of drive power from being supplied to the solenoid valve and power supply to the respiratory phase sensor at the same time, thus greatly increasing the power consumption of the medical device. For example, an excessive voltage drop can be prevented in a battery as a power source, and as a result, the battery can be used for a longer period of time than before.

  Hereinafter, the present invention will be described in detail with reference to the illustrated embodiments.

  FIG. 1 is a schematic diagram showing a respiratory tuner as a medical device according to an embodiment of the present invention.

  This respiratory synchronizer is a respiratory synchronizer used for home treatment of patients with lung diseases, for example, and is connected to an oxygen cylinder 1 as an oxygen supply source and a cannula 3 that supplies oxygen from the oxygen cylinder 1 to the patient. It has come to be. The respiratory tuner includes a pressure sensor 5 as a respiratory phase sensor and an electromagnetic valve 2 that switches the cannula 3 to the oxygen cylinder 1 or the pressure sensor 5 for communication. The pressure sensor 5 and the electromagnetic valve 2 are connected to a CPU 8 as switching control means. The pressure sensor 5 detects fluctuations in the phase of exhalation and inspiration of the patient, and the CPU 8 controls switching of the electromagnetic valve 2 based on a detection signal from the pressure sensor 5. The CPU 8 also functions as sensor power supply means for supplying operating power to the pressure sensor 5.

  The pressure sensor 5 has a communication pipe communicating with the atmosphere, and the cannula 3 is based on a differential pressure between the atmospheric pressure from the communication pipe and the pressure in the cannula 3 connected by the electromagnetic valve 2. The pressure inside is detected. A throttle 6 communicating with the atmosphere is connected between the electromagnetic valve 2 and the pressure sensor 5.

  The solenoid valve 2 is a three-port two-position solenoid valve having a valve body driven by a solenoid, and the valve body is biased by a spring when the solenoid is demagnetized to connect the cannula 3 and the oxygen cylinder 1. It is a normally-off type solenoid valve that turns off.

  A pressure reducing valve 11 for reducing the pressure of oxygen from the oxygen cylinder and a flow rate regulator 12 for adjusting the flow rate of oxygen are interposed between the oxygen cylinder 1 and the electromagnetic valve 2. A safety relief valve 14 is connected between the cannula 3 and the electromagnetic valve 2.

  The CPU 8 includes a power switch (not shown) that receives a power on / off command from the patient, a mode switch that receives a command of the operation mode from the patient, an LED 16 that displays a current operation mode, a power on display, an inhalation detection display, and the like. And a buzzer 17 for notifying the operating state of the respiratory tuner and warning of battery consumption. When the power switch is turned on, the CPU 8 starts supplying power from a battery (not shown), and controls the solenoid valve 2, the pressure sensor 5, the LED 16, and the buzzer 17 in accordance with the mode specified by the mode switch.

  This breathing tuner uses only one AA type dry battery having a rated voltage of 1.5V as a power source. This makes it possible to reduce the weight of the breathing synchronizer so that it can be easily carried and to easily replace the battery when the battery is exhausted.

  The respiratory tuner configured as described above operates as follows. That is, the breathing tuner is activated by the operation of the power switch, and the pressure sensor 5 communicating with the cannula 3 via the electromagnetic valve 2 detects the pressure fluctuation in the cannula 3 due to the patient's breathing. When the start of inhalation of the patient is detected from the detection value of the pressure sensor 5, the CPU 8 switches the electromagnetic valve 2 to communicate the oxygen cylinder 1 with the cannula 3. That is, in FIG. 1, the communication mode of the solenoid valve 2 is switched from the symbol S1 to the symbol S2. As a result, oxygen is supplied from the oxygen cylinder 1 to the cannula 3, and the oxygen is inhaled by the patient. The CPU 8 switches the solenoid valve 2 to allow the cannula 3 to communicate with the pressure sensor 5 when a predetermined time has elapsed since the oxygen cylinder 1 communicated with the cannula 3. That is, in FIG. 1, the communication mode of the solenoid valve 2 is switched from the symbol S2 to the symbol S1. By repeating such switching of the electromagnetic valve 2, oxygen is intermittently supplied to the patient in synchronization with the patient's breathing.

  FIG. 2 is a flowchart showing the processing executed by the CPU 8. With reference to FIG. 2, the control of the solenoid valve 2, the pressure sensor 5 and the LED 16 by the CPU 8 will be described in detail.

  First, the CPU 8 activated by turning on the power switch (step S1) starts supplying power to the pressure sensor 5 and the LED 16 and turns it on (step S2).

  In response to the signal from the pressure sensor 5, observation of pressure fluctuation in the cannula 3 due to patient breathing is started (step S3).

  The pressure in the cannula 3 is compared with a predetermined inspiratory pressure value to determine whether or not the patient has changed from exhalation to inspiration (step S4). This step S4 is repeated until the patient changes from exhalation to inspiration.

  If the pressure in the cannula 3 exceeds the inspiratory pressure, it is determined that the patient has inhaled, and the process proceeds to step S5.

  In step S5, power supply to the pressure sensor 5 and the LED 16 is stopped.

  Thereafter, drive power is output to the electromagnetic valve 2 to activate the electromagnetic valve 2 (step S6). The drive power is power having a voltage for driving the solenoid of the solenoid valve 2. Upon receipt of the driving power, the valve body of the electromagnetic valve 2 is driven by a solenoid, and the cannula 3 communicates with the oxygen cylinder 1. Thereby, the oxygen supply from the oxygen cylinder 1 to the patient via the cannula 3 is started. When the driving power is supplied to the electromagnetic valve 2, the power supply to the pressure sensor 5 and the LED 16 is stopped, so that the power consumption of the breathing tuner does not increase significantly. Therefore, a large voltage drop of the battery is prevented. Thus, the CPU 8 functions as a power interruption unit.

  Time counting is started after the electromagnetic valve 2 is activated, and it is determined whether or not this time exceeds a predetermined time (step S7). This step S7 is repeated until the timed time exceeds a predetermined time. The predetermined time is a time necessary and sufficient for driving the valve body of the electromagnetic valve 2 by the solenoid.

  When the timed time exceeds a predetermined time, the output power to the solenoid valve 2 is switched from the driving power to the holding power, and duty control is started (step S8). The holding power is a power that holds the valve body position by energizing and holding the solenoid, and is a pulse-shaped power having a predetermined duty ratio while having substantially the same voltage as the driving power. The power is smaller than the driving power. The duty ratio may be set according to the characteristics of the solenoid. The holding power may be made smaller than the driving power by reducing the pressure value in addition to changing the duty ratio with respect to the driving power. Here, the CPU 8 functions as electromagnetic valve power supply means. An amplifier that outputs driving power and holding power to the electromagnetic valve 2 based on a command from the CPU 8 may be provided as electromagnetic valve power supply means.

  Thereafter, power supply to the LED 16 is resumed (step S9). The LED 16 that supplies power is an intake detection LED that indicates that intake air has been detected in response to the detection of intake air in step S4, in addition to the LED that indicates power-on.

  Timekeeping is started from the time of switching to the duty control, and it is determined whether or not this time has exceeded a predetermined time set in advance (step S10). This step S10 is repeated until the timed time exceeds a predetermined time. The predetermined time is set based on the respiratory cycle and the number of times of the patient.

  When the timed time exceeds a predetermined time, the duty control of the electromagnetic valve 2 is terminated, and the intake detection LED of the LEDs 16 is turned off (step S11). When the duty control of the solenoid valve 2 is finished, the supply of the holding power to the solenoid of the solenoid valve 2 is finished, the solenoid is demagnetized, and the valve body of the solenoid valve 2 is returned to the initial position by the return spring. As a result, the connection between the cannula 3 and the oxygen cylinder 1 is turned off, and the supply of oxygen to the cannula 3 is completed.

  The intake detection LED does not need to be turned off at the same time as the duty control of the solenoid valve 2 is turned off. For example, the intake detection LED is turned off when 200 ms elapses after the intake detection LED is turned on in step S9. Furthermore, it may be turned off with the passage of a fixed time regardless of the patient's respiratory cycle or the like.

  Following the step S11, the pressure sensor 5 is turned on (step S12).

  It is determined whether or not the patient has an off command to the power switch (step S13). If there is no off command, the process returns to step S4 to continue the series of processes.

  In step S13, when an off command is issued by the patient via the power switch, the power supply from the battery is terminated and the operation of the respiratory tuner is terminated.

  In the respiratory tuner of the above embodiment, power is supplied to the pressure sensor 5 in all periods other than the period in which driving power is supplied to the electromagnetic valve 2. Here, the pressure detected by the pressure sensor 5 and on the pressure sensor 5 side of the solenoid valve 2 may be disturbed when the solenoid valve 2 is switched.

  FIG. 3 is a diagram showing the pressure value detected by the pressure sensor 5 and the switching state of the electromagnetic valve 2 using a common time axis. As shown in FIG. 3, when the pressure sensor 5 detects that the inspiratory pressure has reached a predetermined set value P1 at a time t1 immediately after the patient switches from exhalation to inspiration, the control of the CPU 8 Thus, driving power is supplied to the electromagnetic valve 2. As a result, the valve body of the electromagnetic valve 2 is driven to cut off the communication between the cannula 3 and the pressure sensor 5, while the cannula 3 is connected to the oxygen cylinder 1. When the valve body of the electromagnetic valve 2 is driven, oxygen may flow into the pressure sensor 5 from the oxygen cylinder 1 through a communication path formed between the valve body and the housing. Due to the inflow of oxygen or the like, as shown in FIG. 3, the pressure S detected by the pressure sensor 5 may fluctuate and become unstable. In FIG. 3, the fluctuation of the pressure A actually generated by the intake air in the cannula 3 is shown by being overlapped with a broken line.

  Therefore, in the breathing tuner of another embodiment, the power supply to the pressure sensor 5 is stopped during a predetermined period T1 from the time t1 when the driving current is supplied to the electromagnetic valve 2. Thereby, it is possible to prevent the detection value of the pressure sensor 5 from becoming unstable. Hereinafter, the respiratory tuner of the other embodiment will be described.

  The respiratory tuner of this embodiment has the same components as the respiratory tuner of the embodiment of FIG. 1, and only the control program executed by the CPU 8 is different. In the present embodiment, only differences from the above-described embodiment will be described.

  In the breathing tuner of the present embodiment, power is supplied to the pressure sensor 5 under the control of the CPU 8 after a predetermined period T1 has elapsed since the drive current was supplied to the electromagnetic valve 2. At this time, the pressure sensor 5 detects the pressure corresponding to the atmospheric pressure through the throttle 6 since the electromagnetic valve 2 is disconnected from the cannula 3. Based on the detected pressure value, the pressure sensor 5 is calibrated. The calibration does not necessarily have to be performed for every intake, and may be performed every 10 seconds, for example. When the calibration is not performed, power consumption can be reduced by stopping the power supply to the pressure sensor 5 during the period from inspiration to expiration.

  When the period T2 elapses after the period T1 elapses and the time t2 is reached, the supply of the holding power to the electromagnetic valve 2 is stopped, the electromagnetic valve 2 is switched, and the cannula 3 is replaced with the oxygen cylinder 1 To the pressure sensor 5. Thereby, the detection at the time of the patient's inhalation start via the cannula 3 is started by the pressure sensor 5. Thus, the electromagnetic valve 2 is in an ON state in which the driving power and the holding power are supplied over the total period T0 of the period T1 and the period T2.

  FIG. 4 is a flowchart showing processing executed by the CPU 8 in the respiratory tuner of the embodiment. 4, the same steps as those in FIG. 2 are denoted by the same reference numerals, and only steps different from those in FIG. 2 will be described.

  In FIG. 4, when the power supplied to the solenoid valve 2 is switched from driving power to holding power and switched to duty control (step S8), it is determined whether calibration of the pressure sensor 5, that is, measurement of an offset value is necessary. (Step S21). Whether or not this calibration is necessary may be determined based on the elapsed time since the last calibration, or may be determined based on a change in the average value of the detection values of the pressure sensor 5 or the like. Good.

  If it is determined in step S21 that the pressure sensor 5 needs to be calibrated, power supply to the pressure sensor 5 and the LED 16 is started, and the pressure sensor 5 and the LED 16 are turned on (step S22).

  The pressure sensor 5 is turned on, and offset measurement is performed by measuring the atmospheric pressure with the pressure sensor 5 via the throttle 6 (step S24), and the pressure sensor 5 is calibrated based on the measured value.

  Thereafter, the duty control is terminated (step S25), the electromagnetic valve 2 is switched, and the communication between the cannula 3 and the oxygen cylinder 1 is shut off.

  Thereafter, similarly to the process of FIG. 2, it is determined whether or not the patient has an off command to the power switch (step S13). If there is no off command, the process returns to step S4 to continue the series of processes.

  If it is determined in step S21 that calibration of the pressure sensor 5 is unnecessary, power is supplied only to the LED 16 (step S26), and it is determined whether or not a predetermined time has elapsed (step S27). When the predetermined time elapses, the duty control is ended and the solenoid valve 2 is switched, and the power supply to the pressure sensor 5 is started (step S28), and the measurement of the patient's expiration is started.

  Subsequently, the process proceeds to step S13, and it is determined whether or not there is an off command to the power switch by the patient.

  In this way, when the solenoid valve 2 is switched and the communication between the pressure sensor 5 and the cannula 3 is interrupted, it is possible to effectively prevent the detection value by the pressure sensor 5 from becoming unstable. The operation of the respiratory synchronizer can be stabilized. Further, the pressure sensor 5 can be calibrated based on a stable detection value.

  In the embodiment described above, the CPU 8 may supply driving power to the buzzer 17 each time the intake pressure is detected by the pressure sensor 5 and cause the buzzer 17 to ring for a predetermined period. Further, the battery voltage may be measured, and the buzzer 17 may be sounded when the battery voltage falls below a predetermined value to warn of the battery consumption. In any case, a large voltage drop of the battery can be prevented by supplying power to the buzzer 17 at a timing other than when driving power is supplied to the electromagnetic valve 2.

  In the above embodiment, the solenoid valve 2 is a self-holding type solenoid valve that requires power supply when maintaining communication between the cannula 3 and the oxygen cylinder 1. The solenoid valve may be used. Even when a self-holding solenoid valve is used, the power supply to the pressure sensor 5 and the LED 16 is stopped when the driving power is supplied to the solenoid valve, thereby preventing a significant voltage drop of the battery. The service life can be extended more than before.

  Moreover, in the said embodiment, although the single 2 type dry battery whose rated voltage is 1.5V was used as a power supply, the number of the batteries used may be two or more. Moreover, it is not restricted to a single 2 type dry battery, A rated voltage may not be 1.5V. The present invention can effectively prevent battery consumption, particularly when a battery having a rated voltage of 4 V or less is used as a power source.

  Moreover, in the said embodiment, although the respiratory tuner was comprised as a medical device, medical devices like oxygen concentrators etc. other than a respiratory tuner may be sufficient. Further, the medical device is not limited to being used at home, and may be a medical device used in a medical institution as long as the medical device is driven by a battery.

It is a block diagram which shows the respiratory tuner as a medical device of embodiment of this invention. It is a flowchart which shows the process performed with CPU. It is the figure which showed the detection value of the pressure sensor, and the switching state of the solenoid valve using a common time axis. It is a flowchart which shows the process performed with CPU of the respiration tuner of other embodiment.

Explanation of symbols

1 Oxygen cylinder 2 Solenoid valve 3 Cannula 5 Pressure sensor 6 Aperture 8 CPU
11 Reducing valve 12 Flow regulator 14 Relief valve 16 LED
17 Buzzer

Claims (4)

A solenoid valve (2) interposed in a flow path for supplying oxygen to the cannula (3);
A respiratory phase sensor (5) for detecting the respiratory phase of the patient;
Switching control means (8) for controlling switching of the electromagnetic valve (2) based on the output of the respiratory phase sensor (5);
Electromagnetic valve power supply means (8) for supplying driving power to the electromagnetic valve (2) when switching the electromagnetic valve, and supplying holding power smaller than the driving power when holding the electromagnetic valve (2); ,
Sensor power supply means (8) for supplying power to the respiratory phase sensor;
When the electromagnetic valve power supply means (8) supplies the drive power to the electromagnetic valve (2), the power supply to the respiratory phase sensor (5) by the sensor power supply means (8) is cut off. A medical device comprising a power interruption means (8). The medical device according to claim 1,
The medical device, wherein the holding power supplied to the solenoid valve (2) by the solenoid valve power supply means (8) is a power having a duty ratio smaller than a duty ratio of the driving power. The medical device according to claim 1,
The medical device, wherein the holding power supplied to the solenoid valve (2) by the solenoid valve power supply means (8) is a power having a voltage value smaller than a voltage value of the driving power. The medical device according to any one of claims 1 to 3,
The power shut-off means (8) includes the respiratory phase sensor (5) by the sensor power supply means (8) until a predetermined period has elapsed after the electromagnetic valve power supply means (8) outputs the holding power. Medical device characterized by cutting off power supply to

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