JP2010063776A - Respiration state detection system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a respiration state detection system capable of reducing labors of processing data even if there are many subjects. <P>SOLUTION: Respective processes of a personal computer 83 are started when a start button 101 is selected after respective buttons 91-99 displayed on a menu screen are selected, and the processes are stopped when a stop button 103 is selected. Specifically, if a first button 91 is selected, data (such as ID numbers and respiration data) are read into the personal computer 83 one after another from a plurality of respiration state monitoring devices 5 mounted on a data collection device 35. If a second button 93 is selected, the process of analyzing the respiration data corresponding to the respective ID numbers is implemented, and the result of analysis is stored. If a third button 95 is selected, the result of the data analysis is printed. If a fourth button 97 is selected, the process of initializing internal data in the respiration state monitoring device 5 is implemented. If a fifth button 99 is selected, the respiration state monitoring device 5 is charged with electricity. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a respiratory state detection system that can detect a respiratory state of a person using a respiratory sensor using a piezoelectric element or the like.

  Conventionally, as a technique for detecting an apnea state during sleep, for example, a technique has been disclosed in which a flow sensor is attached to a nose and a signal from the flow sensor is stored in an apparatus main body via a relay box (Patent Literature). 1).

For example, a technique is disclosed in which a pressure sensor is attached to the nose and a signal from the pressure sensor is processed by a data processing device attached to the ear (see Patent Document 2).
JP 2000-31669 A JP 2005-137479 A

However, in the above-described conventional technique, when there are many subjects, a method for efficiently processing data of a large number of people has not been sufficiently studied.
The present invention has been made to solve the above-described problem, and an object of the present invention is to provide a respiratory state detection system that requires less time to process data even when there are many subjects.

  (1) The invention of claim 1 uses a data collection device capable of mounting a plurality of respiratory state monitoring devices for storing data from a respiratory sensor for detecting a human respiratory state, and is stored in the respiratory state monitoring device. In a respiratory condition detection system that captures the collected data into the data collection device or a storage device (for example, a storage device in a personal computer) connected to the data collection device, a control signal from an electronic control device (for example, a personal computer) Data stored in the respiratory state monitoring device is automatically taken into the storage device from the respiratory state monitoring device attached to the data collection device.

  In the present invention, for example, the data stored in the respiratory condition monitoring device attached to the data collecting device is automatically taken into the storage device of the personal computer, for example, by a control signal from the personal computer. Even when attached to the collection device, data can be efficiently captured and stored. Therefore, for example, since data can be efficiently captured simply by operating a simple switch, human labor is greatly reduced even when screening a large number of people, and human error due to automation can be reduced. There is an effect.

(2) The invention of claim 2 is characterized in that the data stored in the storage device is automatically analyzed in accordance with a control signal from the electronic control device.
In the present invention, even when a large number of respiratory condition monitoring devices are attached to the data collection device, data can be analyzed efficiently, so that human labor is greatly reduced and human error due to automation can be reduced. Has a remarkable effect.

(3) The invention of claim 3 is characterized in that the analysis result is automatically printed by a control signal from the electronic control unit.
In the present invention, even when a large number of respiratory condition monitoring devices are attached to the data collection device, data can be printed efficiently, so that human labor is greatly reduced, and human error due to automation can be reduced. Has a remarkable effect.

(4) The invention of claim 4 is characterized in that the internal data stored in the respiratory condition monitoring device is automatically initialized by a control signal from the electronic control device.
In the present invention, even when a large number of respiratory condition monitoring devices are attached to the data collection device, the internal data of the respiratory condition monitoring device can be initialized efficiently, so that human labor is greatly reduced and human error due to automation is reduced. Has a remarkable effect that can be reduced.

  (5) In the invention of claim 5, the respiratory condition monitoring device includes a rechargeable battery, and the rechargeable battery of the respiratory condition monitoring device attached to the data collecting device is controlled by a control signal from the electronic control device. The battery is automatically charged.

  In the present invention, even when a large number of respiratory condition monitoring devices are attached to the data collection device, the rechargeable battery of the respiratory condition monitoring device can be charged efficiently, so that human labor is greatly reduced and human error due to automation is reduced. There is a remarkable effect that it can be reduced.

Next, an example (example) of the best mode for carrying out the present invention will be described.
[Example]
The respiratory state detection system of the present embodiment accumulates each individual's respiratory data by a screener, and takes this respiratory data into a personal computer via a data collection device, and analyzes respiratory conditions such as the number of apneas and hypopneas. The process is performed.

a) First, the configuration of a portable screener (respiratory state monitoring system) will be described with reference to FIGS.
As shown in FIG. 1, the screener 1 is a device for detecting a respiratory state. The respiratory sensor 3 attached to the subject and the respiratory sensor 3 are detachably attached to store signals from the respiratory sensor 3. The respiration state monitoring device 5 is configured.

  The respiration sensor 3 includes a base body 6 which is a substantially T-shaped cover, a detection element 8 attached to a central flat portion (ridge line portion of the mountain) 7 of the base body 6, and a pair of lead wires 9 extending from the detection element 8. 10 and an adhesive member 11 attached to the living body side (inside: back side) of the substrate 6. A sensor-side connector 12 (see FIG. 2) is attached to the tips of the lead wires 9 and 10.

  Among these, the said base | substrate 6 consists of a thin elastic film which consists of polyester, for example, and is a concave member bent in the shape of a mountain between the center flat part 7 and the both sleeve parts 13 and 14 on the left and right. A plurality of ventilation holes 15 are formed in the vicinity of the detection element 8 on the distal end side of the base 6.

  The detection element 8 is attached so as to extend from the front side of the central flat portion 7 to the back side of the front end side of the central flat portion 7. This detection element 8 is a piezo element provided with electrodes on both sides in the thickness direction of a rectangular PVDF film having functions of temperature sensitivity and piezoelectricity, and the outside of the electrode is covered with a moisture-proof film (not shown).

  The adhesive member 11 is a belt-like member used for attaching the respiration sensor 3 to a living body, and is longer than the length of the base 6 in the left-right direction. Accordingly, both ends of the adhesive member 11 protrude outward in the left-right direction from the left and right leg portions 16, 17 of the base 6.

  The adhesive member 11 is fixed by eyelets 18 and 19 at the leg portions 16 and 17, and is disposed on the back side of the base 6 so as to cross the left-right direction of the base material 3 and protrudes toward the base 6 side. It is curved to become. The adhesive member 11 is mainly composed of a strip-like flexible base member 20 and includes a double-sided tape (not shown) that adheres to a living body on the back side of the base member 20.

  On the other hand, the respiratory condition monitoring device 5 is a lightweight portable device that can be worn on an arm or the like, and is housed in a substantially rectangular parallelepiped plastic casing 21 as shown in FIG. And an electronic control unit 40 (see FIG. 4).

  A device-side upper connector (modular jack) 22 into which the sensor-side connector 12 is fitted is provided on the upper surface of the respiratory condition monitoring device 5, and the first to fifth LEDs 23 to 30 are covered with a translucent cover 31. Has been.

  Further, a measurement start switch 33 for starting / stopping the measurement (monitoring) of the breathing state and turning on / off the breathing state monitoring device 5 is disposed on the left side surface of the breathing state monitoring device 5. In order to connect the monitoring device 5 to the base device (data collection device) 35 (see FIG. 6), a device-side lower connector (D-SUB connector) 37 is disposed.

A barcode seal (storage unit) 41 indicating the ID number of the respiratory condition monitoring device 5 itself is attached to the back surface of the respiratory condition monitoring device 5.
b) Next, the electrical configuration of the respiratory condition monitoring device 5 will be described with reference to FIG.

  As shown in FIG. 4, the electronic control device 40 of the respiratory condition monitoring device 5 is backed up by a well-known A / D built-in microcomputer 43, nonvolatile memory 45, flash memory 47, serial communication line 49, and battery (rechargeable battery) 51. A real-time clock 53, a temperature sensor 55 for correction, and the like. The nonvolatile memory 45 stores an ID number corresponding to the barcode.

  The modular jack 21 is connected to a differential amplifier 57. The differential amplifier 57 is connected to a microcomputer 43 with a built-in A / D through a first low-pass filter 59, a gain AMP (amplifier) 61, and a gain AMP 63. To the A / D built-in microcomputer 43 via the notch filter 65, the second low-pass filter 67, and the peak detection circuit 69.

  Further, the A / D built-in microcomputer 43 includes the first LED 23 of the battery exhaustion indicator 71, the second to fourth LEDs 25 to 29 of the breathing flow indicator 73, and for preventing the measurement start switch 33 from being forgotten and for displaying the measurement completion. It is connected to the fifth LED 30 of the operation indicator 75.

  The device-side lower connector 37 is connected to the device-side upper connector 22 via the rechargeable battery 51, and the device-side upper connector 22 is connected to a power supply circuit 77 that supplies power to the electronic control device 40. Yes.

  Here, the circuit from the rechargeable battery 51 to the power supply circuit 77 is normally open by the device-side upper connector 22. That is, by attaching the sensor-side connector 12 of the respiration sensor 3 to the apparatus-side upper connector 22, power is supplied from the rechargeable battery 51 to the power supply circuit 77, and a signal from the respiration sensor 3 is transmitted to the respiration state monitoring device 5. It is configured to input to the A / D built-in microcomputer 43.

c) Next, a method of signal processing performed in the respiratory condition monitoring device 5 will be described with reference to FIG.
In this embodiment, the analog signal (base signal) obtained from the respiration sensor 3 is amplified by the differential amplifier 57 via the device-side upper connector 22, and the first low-pass filter 59 is used to extract the respiration signal. And is output to the notch filter 65 in order to extract a sound signal (vibration signal) due to snoring, and the following processing is performed.

Process for Extracting Respiration Signal Since the respiration sensor 3 is a sensor using the detection element 8 that is a piezo element, the base signal includes components of temperature and vibration associated with respiration. Therefore, it is necessary to extract a low-frequency signal that is considered to clearly indicate the respiratory action from the base signal.

Therefore, the base signal is processed by the first low-pass filter 59 that passes a signal of 7 Hz or less, and a respiration signal corresponding to respiration as shown in FIG. 5A is extracted.
・ Processing for Extracting Audio Signal Also, since the audio signal corresponding to snoring or the like has a higher frequency than the breathing signal, the base signal is processed by the notch filter 65 of 50 Hz and 60 Hz here. As shown in FIG. 5B, an audio signal corresponding to snoring or the like is extracted.

This audio signal is processed by the second low-pass filter 67 of 2 kHz or less, and high-frequency noise is cut.
Then, the audio signal from which the noise has been cut is processed by the peak detection circuit 69, and as shown in FIG. 5C, an audio signal (audio peak signal) consisting of an envelope connecting the peaks of the audio waveform is obtained. can get. Here, only a half wave is used.

  In other words, in this embodiment, the base signal is separated into the low-frequency respiratory signal and the high-frequency audio signal by the separation circuit including the differential amplifier 57 and the filters 59 and 65. It is stored in the flash memory 47 via 43.

  Specifically, in the flash memory 47, a respiratory signal and an audio signal (envelope data) are stored as a signal (amplitude value) data of 0.1 seconds along the time series of time. Is stored for the time required for the analysis (for example, at least 3 hours).

d) Next, the respiratory condition detection system will be described.
As shown in FIG. 6, the respiratory state detection system of the present embodiment includes a data collection device 35 that detachably mounts a plurality of respiratory state monitoring devices 5, and a barcode reader 81 that reads a barcode of the respiratory state monitoring device 5. And a personal computer 83 for controlling the data collection device 35, a keyboard 85, a display 87, a printer 89, and the like.

  When the breathing state monitoring device 5 is attached to the data collecting device 35, a dedicated communication terminal (not shown) for the base side connector (D-SUB connector) 79 of the data collecting device 35 and the device side lower connector 37 is provided. Through this, a signal such as data can be transmitted and received between the respiratory condition monitoring device 5 and the data collecting device 35, and the base side connector 79 of the data collecting device 35 is connected to the device side lower connector 37. The rechargeable battery 51 can be charged via a dedicated charging terminal (not shown).

  In this personal computer 83, as described below, for example, the respiratory state is determined using the respiratory signal and the audio signal read from the respiratory state monitoring device 5 to the storage device 80 such as a hard disk via the data collection device 35, for example. It is possible to notify the determination result using the display 87 and a speaker (not shown), print it with the printer 89, or control charging of the rechargeable battery 51 of the respiratory condition monitoring device 5.

e) Next, various processes performed by the personal computer 83 will be described.
Each process of the personal computer 83 is performed, for example, when the start button 101 is selected after the buttons 91 to 99 displayed on the menu screen as shown in FIG. Is canceled when is selected.

  Specifically, when the first button 91 is selected, data (ID number and respiration) are sequentially provided for each subject from the plurality of respiratory condition monitoring devices 5 attached to the data collecting device 35 via the data collecting device 35. Data) is read into the personal computer 83.

  When the second button 93 is selected, after processing similar to the processing by the first button 91 (or using data that has already been read), analysis of respiratory data corresponding to each ID number is performed. The processing is performed and the analysis result is stored. That is, a process for detecting a sleep apnea state, which will be described later, from the respiratory data indicating a voltage signal corresponding to exhalation or inspiration, and storing the number of times of hypopnea, apnea, and the like are performed.

  When the third button 95 is selected, after the same processing as the processing by the first button 91 and the second button 93 (or using the analysis result of the data already stored), the data The process of printing the analysis result is performed. For example, the ID number and the number of sleep apneas per hour corresponding to the ID number are printed.

When personal data such as the name of the subject is stored in association with the ID number when the ID number is read by the percode reader, the personal data may also be printed.
When the fourth button 97 is selected, the internal data of the respiratory condition monitoring device 5 is initialized.

  When the fifth button 99 is selected, the rechargeable battery 51 of the respiratory condition monitoring device 5 is charged. In addition, in order to fully charge, you may charge several times, for example, leaving a predetermined period in one night.

Hereinafter, each process will be described sequentially.
<Data reading process from the respiratory condition monitoring device 5>
Here, one or more desired processes of the first button 91 to the fifth button 99 are selected and the start button 101 is pressed to execute the process. Note that processing can be canceled by a cancel button 103.

  First, when the first button 91 is selected, as shown in FIG. 8, in step (S) 100, it is determined whether or not the cancel button 103 is ON (on). If it is not ON, the process proceeds to step 110.

In step 110, for example, data for one person is read in order from the smallest ID number.
In the following step 120, the read data (ID number, respiration data, etc.) is stored in the storage device 80 such as a hard disk of the personal computer 83.

In the following step 130, it is determined whether or not the cancel button 103 is ON. If the cancel button 103 is ON, the process is temporarily terminated. If not, the process proceeds to step 140.
In step 140, it is determined whether or not all data from the respiratory condition monitoring device 5 has been stored. If the data has been stored, the process is temporarily terminated, and if not, the process returns to step 110.
<Analysis processing of read data>
When the second button 93 is selected, as shown in FIG. 9, in step 200, it is determined whether or not the cancel button 103 is ON. Proceed to

In step 210, it is determined whether or not there is already read and stored data. If there is, the process proceeds to step 230. If not, the process proceeds to step 220.
In step 220, as shown in FIG. 8, processing for reading and storing data is performed, and the flow proceeds to step 230.

In step 230, for example, data for one person is analyzed in order from the smallest ID number.
In the subsequent step 240, the analysis result is stored in the storage device 80 of the personal computer 83.

In the following step 250, it is determined whether or not the cancel button 103 is ON. If the cancel button 103 is ON, the process is temporarily terminated. If not, the process proceeds to step 260.
In step 260, it is determined whether or not all analysis results have been stored. If the analysis results have been stored, the process is temporarily terminated. If not, the process returns to step 230.
<Analysis result printing process>
When the third button 95 is selected, as shown in FIG. 10, in step 300, it is determined whether or not the cancel button 103 is ON. If it is ON, this processing is once terminated. Proceed to

In step 310, it is determined whether there is data that has already been analyzed and stored. If there is, the process proceeds to step 340, and if not, the process proceeds to step 320.
In step 320, as shown in FIG. 8, data is read and stored.

In the subsequent step 330, as shown in FIG. 9, a process of analyzing the data is performed, and the process proceeds to step 340.
In step 340, for example, processing of printing analysis results is performed in order from the smallest ID number.

In the following step 350, it is determined whether or not the cancel button 103 is ON. If the cancel button 103 is ON, the process is temporarily terminated. If not, the process proceeds to step 360.
In step 360, it is determined whether or not all the analysis results have been printed. If the analysis results have been printed, the process is temporarily terminated. If not, the process returns to step 340.
<Internal data initialization process>
When the fourth button 97 is selected, as shown in FIG. 11, in step 400, it is determined whether or not the cancel button 103 is ON. If it is ON, this processing is once terminated. Proceed to

In step 410, for example, the internal data of the respiratory condition monitoring device 5 is initialized in order from the smallest ID number.
In the following step 420, it is determined whether or not the cancel button 103 is ON. If the cancel button 103 is ON, the present process is temporarily terminated. If not, the process proceeds to step 430.

In step 430, it is determined whether or not the internal data of all the respiratory condition monitoring devices 5 has been initialized. If it has been implemented, the process is temporarily terminated. If not, the process returns to step 410.
<Charging process of the rechargeable battery 51>
When the fifth button 99 is selected, as shown in FIG. 12, in step 500, it is determined whether or not the cancel button 103 is ON. If it is ON, this processing is once terminated. Proceed to

In step 510, for example, the rechargeable battery 51 of the respiratory condition monitoring device 5 is charged in order from the smallest ID number.
In the following step 520, it is determined whether or not the cancel button 103 is ON. If the cancel button 103 is ON, the process is temporarily terminated. If not, the process proceeds to step 530.

  In step 530, it is determined whether or not the rechargeable batteries 51 of all the respiratory condition monitoring devices 5 have been charged. If yes, the process is temporarily terminated. If not, the process returns to step 510.

f) Next, the analysis process will be described in more detail.
First, an apnea determination algorithm will be described.
As shown in FIG. 13A, a respiration signal is obtained corresponding to respiration. For example, in the case of apnea (or hypopnea), the amplitude of the respiration signal becomes small.

  Therefore, for example, when the maximum value of the amplitude of the respiratory signal in the past 2 minutes is X, if the period in which the amplitude is ½ of X (ie, S1) continues for 10 seconds or more, apnea (or hypopnea) It is conceivable to judge that has occurred.

  By the way, when noise occurs, a signal having a large amplitude (a signal larger than the determination value S1) may be detected at a timing different from that of respiration. In this case, the noise may be erroneously determined as respiration.

  Therefore, in this embodiment, when a signal with a large amplitude that seems to be breathing is detected (for example, at the peak time t1), as shown in FIG. 13B, before and after the time t1 (t1). It is checked whether or not an audio signal larger than the determination value S2 is detected at time ΔT) centered on, and if that signal is detected, it is determined that respiration has occurred.

  This is because when snoring (or hypopnea) changes to normal breathing, it usually accompanies snoring. Therefore, snoring is determined based on the audio signal, and if snoring occurs, breathing occurs. It is determined.

-Next, specific processing contents will be described.
As shown in the flowchart of FIG. 14, first, in step 600, it is determined whether or not the amplitude X of the respiratory signal is less than the determination value S1. If an affirmative determination is made here, the process proceeds to step 610. If a negative determination is made on the other hand, the present process is once terminated.

In step 610, a counter timer (count value Z) is started.
In the following step 620, it is determined whether or not the amplitude X of the respiratory signal is greater than or equal to the determination value S1. If an affirmative determination is made here, the process proceeds to step 630, whereas if a negative determination is made, the process waits until this condition is satisfied.

In step 630, the count value Z is substituted into the intermediate counter Y. In the subsequent step 640, it is determined whether the detected signal having a large amplitude is a normal respiratory signal or noise. Specifically, it is determined whether or not the width of the signal detected this time (noise width Δn: time from the upper peak to the lower peak of the cycle) exceeds the noise determination value NH. If an affirmative determination is made here, that is, it is determined that there is a high possibility that the signal is a respiration signal since it is a signal with a long cycle, the routine proceeds to step 650. On the other hand, if a negative determination is made, that is, since it is a pulse-like steep signal with a short cycle, it is determined that there is a high possibility of noise, the process returns to step 620.

  In step 650, it is determined whether or not the counter value Z exceeds 10 seconds, that is, whether or not 10 seconds have elapsed since the amplitude of the respiratory signal has decreased. If an affirmative determination is made here, the process proceeds to step 660, whereas if a negative determination is made, the process proceeds to step 670.

  In step 670, since it is within 10 seconds after it is determined in step 600 that the amplitude of respiration has decreased, it is determined that it is not the normal respiration range, that is, apnea / hypopnea, and this processing is performed once. Exit.

On the other hand, in step 660, since 10 seconds have passed since the amplitude of respiration became small, there is a possibility of apnea / hypopnea.
Specifically, whether snoring occurred when resuming breathing by determining whether the amplitude OW of the audio signal is equal to or greater than the determination value S2 and the length L of the signal is longer than the determination value Δt. Determine whether or not. In addition, as L, the period when the signal more than the said determination S2 was obtained is employable, for example. If an affirmative determination is made here, the process proceeds to step 680, while if a negative determination is made, the process proceeds to step 690.

In step 680, since it is considered that snoring has occurred, it is determined that breathing has been resumed, it is determined that there is one apnea / hypopnea, and this process is temporarily terminated.
On the other hand, in step 690, the occurrence of snoring due to the audio signal cannot be confirmed, but since the amplitude of respiration increases again after the amplitude of respiration decreases, and the possibility of respiration from the long cycle is high, here, One apnea / hypopnea in the value of the intermediate counter Y (for example, when Y is 10 seconds or more in Y seconds), and then in ZY seconds (when ZY is 10 seconds or more) It is determined that one apnea / hypopnea has occurred. That is, it is determined that a total of two apneas / hypopneas have occurred, and the process is temporarily terminated.

  g) As described above, in this embodiment, in response to a command from the personal computer 83, the data stored in the respiratory condition monitoring device 5 attached to the data collecting device 35 is automatically taken into the storage device 80 of the personal computer 83. Since data analysis and printing are performed, even when a large number of respiratory condition monitoring devices 5 are attached to the data collection device 35, data processing can be performed efficiently. Therefore, it is possible to process data efficiently only by a simple switch operation, so that even when performing screening of a large number of people, human labor is greatly reduced, and human error due to automation can be reduced. Has an effect.

Further, in this embodiment, even when a large number of respiratory condition monitoring devices 5 are attached to the data collecting device 35, the internal data of the respiratory condition monitoring device 5 can be initialized efficiently.
Furthermore, even when a large number of respiratory condition monitoring devices 5 are attached to the data collecting device 35, the rechargeable battery 51 of the respiratory condition monitoring device 5 can be charged efficiently.

Needless to say, the present invention is not limited to the above-described embodiments and can be carried out in various modes without departing from the technical scope of the present invention.
For example, instead of controlling the data collection device from a personal computer, the above-described processes may be performed by incorporating an electronic control device, a storage device, or a display having the same functions as a personal computer into the data collection device itself.

It is explanatory drawing which shows the screener of an Example. It is explanatory drawing which shows the mounting state to the respiration condition monitoring apparatus of a respiration sensor. The respiratory condition monitoring apparatus is shown, (a) is a top view, (b) is a front view, (c) is a bottom view, (d) is a left side view, and (e) is a rear view. It is a block diagram which shows the electric constitution of the respiratory condition monitoring apparatus of an Example. (A) is a graph showing a respiration signal, (b) is a graph showing an audio signal without peak detection, and (c) is a graph showing an audio signal with peak detection. It is explanatory drawing which shows the system configuration | structure of the respiratory condition detection system of an Example. It is explanatory drawing which shows the menu screen of a display. It is a flowchart which shows the process sequence when a 1st button is selected. It is a flowchart which shows the process sequence when a 2nd button is selected. It is a flowchart which shows the process sequence when a 3rd button is selected. It is a flowchart which shows the process sequence when a 4th button is selected. It is a flowchart which shows the process sequence when a 5th button is selected. (A) It is a graph which shows a respiration signal, (b) It is a graph which shows an audio | voice signal. It is a flowchart which shows the process sequence which detects sleep apnea.

Explanation of symbols

1 ... Screener (Respiratory condition monitoring system)
DESCRIPTION OF SYMBOLS 3 ... Respiration sensor 5 ... Respiration state monitoring device 35 ... Data collection device 80 ... Storage device 83 ... Personal computer 87 ... Display 89 ... Printer

Claims (5)

Using a data collection device capable of mounting a plurality of respiratory condition monitoring devices that store data from a respiratory sensor that detects a person's respiratory state, the data stored in the respiratory condition monitoring device is stored in the data collection device or In a respiratory condition detection system for capturing in a storage device connected to the data collection device,
A breathing state, wherein the data stored in the breathing state monitoring device is automatically taken into the storage device from the breathing state monitoring device mounted on the data collecting device by a control signal from an electronic control unit Detection system.   The respiratory state detection system according to claim 1, wherein analysis of data stored in the storage device is automatically performed by a control signal from the electronic control device.   The respiratory state detection system according to claim 1 or 2, wherein the analysis result is automatically printed by a control signal from the electronic control unit.   The respiratory state detection system according to any one of claims 1 to 3, wherein the internal data stored in the respiratory state monitoring device is automatically initialized by a control signal from the electronic control unit. The respiratory condition monitoring device includes a rechargeable battery,
The respiration according to any one of claims 1 to 4, wherein the rechargeable battery of the respiratory condition monitoring device attached to the data collection device is automatically charged by a control signal from the electronic control device. Condition detection system.

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