WO2022239317A1 - 呼吸測定方法、呼吸測定装置および呼吸測定システム - Google Patents
呼吸測定方法、呼吸測定装置および呼吸測定システム Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/087—Measuring breath flow
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/091—Measuring volume of inspired or expired gases, e.g. to determine lung capacity
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
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- A—HUMAN NECESSITIES
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- A61B5/725—Details of waveform analysis using specific filters therefor, e.g. Kalman or adaptive filters
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/74—Details of notification to user or communication with user or patient ; user input means
- A61B5/742—Details of notification to user or communication with user or patient ; user input means using visual displays
Definitions
- the present disclosure relates to a respiration measurement method, a respiration measurement device, and a respiration measurement system.
- Non-Patent Document 1 introduces a spirometer that can directly measure a ventilation volume by breathing by blowing into a mouthpiece.
- Patent Document 1 discloses a method for measuring respiratory sounds using a microphone.
- the present disclosure has been made in order to solve the above problems, and the purpose thereof is to provide a technique for easily grasping information corresponding to the ventilation volume even in an environment where the subject can act freely. is to provide
- a respiration measurement method includes the steps of acquiring respiratory signals with a detector attached to the human body, and extracting a first signal and a second signal corresponding to an expiratory phase from each of the acquired respiratory signals. and calculating information corresponding to respiratory ventilation based on the extracted first and second signals.
- the calculating step includes performing different operations on each signal of the group of respiratory signals when the signal is the first signal and when the signal is the second signal.
- a respiration measurement device includes a detector that acquires a respiration signal while attached to a human body, and a controller that processes the respiration signal.
- the controller extracts a first signal corresponding to the inspiratory phase and a second signal corresponding to the expiratory phase from each of the respiratory signal groups acquired by the detector.
- the control unit calculates information corresponding to the ventilation volume due to respiration based on the extracted first signal and second signal.
- the control unit performs different calculations on the signal that is the first signal and the signal that is the second signal in the group of respiratory signals.
- a respiration measurement system includes a respiration measurement device and a display device.
- the control unit outputs information corresponding to the calculated ventilation volume.
- the display device displays information corresponding to the output ventilation volume.
- the respiratory measurement method for each signal of the respiratory signal group, when the signal is the first signal corresponding to the inspiratory phase and when the signal is the second signal corresponding to the expiratory phase, perform different operations. By doing so, it is possible to easily grasp the information corresponding to the ventilation volume even in an environment where the subject can act freely.
- FIG. 4 is a graph showing an example of changes in respiratory signals over time;
- FIG. 4 is a diagram for explaining an integrated value of absolute values of respiratory signals and a correction method thereof;
- FIG. 4 is a diagram for explaining an integrated value of absolute values of respiratory signals and a correction method thereof;
- FIG. 4 is a diagram for explaining an integrated value of absolute values of respiratory signals and a correction method thereof;
- 7 is a graph showing an example of change over time of ventilation volume information before correction.
- FIG. 11 is a graph showing an example of temporal changes in ventilation volume information after correction;
- FIG. 4 is a flowchart for explaining data processing;
- FIG. 11 is a flowchart for explaining a ventilation amount information calculation process;
- FIG. 10 is a diagram showing an example of the overall configuration of a respiration measurement system according to a second embodiment;
- FIG. It is a figure which shows an example of a measuring device. It is a figure for demonstrating the state with which the human body was mounted
- FIG. 10 is a diagram showing a display example of output information;
- FIG. 1 is a diagram showing an example of the overall configuration of a respiration measurement system 1 according to the first embodiment.
- the respiration measurement system 1 calculates information corresponding to the ventilation volume based on the acquired respiration signal and displays the information on the display device 600 .
- the respiration measurement system 1 includes a respiration measurement device 10 and a display device 600.
- the respiration measurement device 10 includes a data processing device 500 and a measurement device 130 .
- the measuring device 130 includes a detector 132, a CPU (Central Processing Unit) 131, a storage device 133, and a transmitter 134 that wirelessly transmits signals.
- the data processing device 500 includes a control section 510 .
- the control unit 510 includes a CPU 511 and a storage device 512 .
- the detector 132 detects and acquires a respiratory signal while attached to the human body.
- Detector 132 is, for example, a microphone.
- measuring device 130 including detector 132 is attached to subject A's neck.
- the respiratory signal is a signal indicating the volume of respiratory sounds of the subject A (see FIG. 2 described later).
- the measuring device 130 (detector 132) is not limited to the neck, and may be attached to any position on the human body as long as it can detect breath sounds (for example, near the throat or ears).
- the measurement device 130 may be affixed to the human body or placed in a band around the neck, for example.
- the measuring device may be constructed by separating the main body and the sensor. By doing so, the measuring device can acquire the respiration signal while performing actions in daily life. For example, it is possible to continuously observe changes in breathing while performing fine work such as using the fingers or doing some work.
- the CPU 131 comprehensively controls the measuring device 130 .
- the storage device 133 stores respiratory signals and the like acquired by the detector 132 .
- the CPU 131 causes the storage device 133 to store the respiratory signal acquired by the detector 132 .
- the CPU 131 may perform preprocessing on the respiratory signal to remove blood vessel sounds, environmental sounds, and the like that may be included in the respiratory signal.
- preprocessing is a band-pass filter that removes frequencies other than the breathing sound.
- the measuring device 130 has a configuration in which a memory card 140, which is a removable external storage medium, can be inserted. Respiratory signals stored in storage device 133 can be retrieved by memory card 140 and read into data processing device 500 .
- the measuring device 130 is configured to be able to communicate with the data processing device 500 .
- the measurement device 130 can transmit the respiratory signal acquired by the detector 132 to the control unit 510 of the data processing device 500 in real time.
- Transmitter 134 wirelessly transmits the respiratory signal stored in storage device 133 to controller 510 .
- the data processing device 500 can acquire the respiratory signal acquired by the detector 132 by reading from the memory card 140 or communicating with the measuring device 130 .
- the acquired respiratory signal group can be fetched into the data processing device 500 after the fact.
- the acquired respiratory signal can be taken into the data processor 500 in real time.
- a control unit 510 included in the data processing device 500 controls the data processing device 500 as a whole.
- the CPU 131 performs arithmetic processing and stores the result in the storage device 133 .
- the control unit 510 acquires the respiratory signal acquired by the detector 132 by the method as described above.
- Control unit 510 calculates information corresponding to the ventilation volume due to respiration (hereinafter also referred to as “ventilation volume information”) based on the acquired respiratory signal.
- control unit 510 outputs the ventilation volume information.
- the control unit 510 may store the output ventilation volume information in the storage device 512, may output the ventilation volume information to the display device 600, or may output the ventilation volume information to another device (such as a mobile terminal). You may make it output ventilation volume information as communication data.
- the display device 600 displays the output ventilation volume information.
- ventilation volume information is displayed as waveform information, as shown in FIG. 5, which will be described later.
- control unit 510 transmits the ventilation volume information as communication data to a mobile terminal (not shown) capable of communicating with data processing device 500 so that the ventilation volume information is displayed on the mobile terminal.
- FIG. 2 is a graph showing an example of changes in respiratory signals over time. A plot of the respiratory signal (volume of respiratory sound) acquired by the detector 132 is shown in FIG. 2, for example.
- the signal corresponding to the inspiratory phase is called “inspiratory signal” or “first signal”.
- a signal corresponding to the expiratory phase is referred to as an “expiratory signal” or “second signal”. That is, the respiratory signal acquired when the subject A is inhaling is the inspiratory signal (first signal), and the respiratory signal acquired when the subject A is exhaling is the expiratory signal (second signal ).
- the inspiratory signal in the period L4 (t3-t4) the expiratory signal, in the period L5 (t4-t5) the inspiratory signal, in the period L6 (t5-t6) the expiratory signal, period L7 ( An inspiratory signal is acquired during the period from t6 to t7, and an expiratory signal is acquired during the period L8 (t7 to t8).
- the volume of breathing sounds is proportional to the square of the flow velocity of breathing. From this, it is considered that by integrating the sound volume (breathing signal) of the expiratory phase and the inspiratory phase for each phase and seeing the change in the integrated value, it is possible to estimate the relative change in the ventilation volume of each phase.
- the ventilation volume information in the inspiratory phase is calculated based on the integrated value of the absolute values of the inspiratory signal (first signal), and the ventilation volume information in the expiratory phase is calculated based on the absolute value of the expiratory signal (second signal). It was decided to calculate based on the integrated value of the value.
- each acquired respiratory signal group is an inspiratory signal (first signal) corresponding to the inspiratory phase or an expiratory signal (second signal) corresponding to the expiratory phase. can do.
- first signal an inspiratory signal
- second signal an expiratory signal
- the above can be determined from the difference between the waveform shape of the expiratory phase and the waveform shape of the inspiratory phase.
- the above can be determined from the difference in frequency characteristics between the expiratory phase and the inspiratory phase.
- Document A shows that the cumulative power spectrum is 500-800 dB greater in the expiratory phase than in the inspiratory phase (FIGS. 3A-6). In this way, an inspiratory signal (first signal) and an expiratory signal (second signal) can be extracted from each of the acquired respiratory signal groups.
- 3A shows the integrated value of the absolute value of the exhalation signal (hereinafter also referred to as the “integrated exhalation value”) or the integrated value of the absolute value of the inspiratory signal (hereinafter, “ (also referred to as “integrated intake value”) are shown. Moreover, the result of determining whether each of L1 to L8 is exhalation or inhalation by the method described above is shown.
- the inspiratory integrated value indicates the amount corresponding to the ventilation volume (amount of breathing) in the inspiratory phase.
- the expiratory integrated value indicates the amount corresponding to the ventilation volume (the amount of exhalation) in the exhalation phase.
- the amount of breathing in inspiratory phase ventilation volume
- the amount of breathing out ventilation volume in expiratory phase
- the inspiratory and expiratory volumes should be approximately equal.
- Fig. 3B shows the total value obtained by dividing the integrated value in Fig. 3A into an inspiratory integrated value and an expiratory integrated value.
- the sum of the inspiratory integrated values is 1280 and the sum of the expiratory integrated values is 2010.
- the volume measured in the inspiratory and expiratory phases may not always be the same. . Both volumes differ depending on the part of the subject A to which the measuring device 130 is attached.
- the measurement device 130 is attached to the neck of the subject A, and in this case, the sound volume measured during the exhalation phase is larger than that during the inhalation phase.
- the correction coefficient K is used to perform correction so that the inspiratory integrated value and the expiratory integrated value are balanced.
- the correction coefficient K integrated intake value/integrated expiration value.
- the correction coefficient K ⁇ 1 because the sound volume measured in the expiratory phase is larger than that in the inspiratory phase.
- the respiratory volume information is obtained by integrating the absolute value of the inspiratory signal, and when the respiratory signal is an expiratory signal, the absolute value of the respiratory signal is calculated. Multiply by -1 and add up. In the following example, it is assumed that all acquired respiratory signals are positive values.
- time-series data of a respiratory signal group (A1, A2, A3, A4), where A1 and A2 are inspiratory signals and A3 and A4 are expiratory signals.
- the time-series data of the ventilation information before correction is (A1, A1+A2, A1+A2-A3, A1+A2-A3-A4).
- the expiration signal A3 is corrected to A3 ⁇ K
- A4 is corrected to A4 ⁇ K.
- the time-series data of the ventilation information corrected by the correction coefficient K is (A1, A1+A2, A1+A2-A3 ⁇ K, A1+A2-A3 ⁇ K-A4 ⁇ K).
- FIG. 4 is a graph showing an example of temporal changes in ventilation volume information before correction. As shown in the figure, during the period of L1, which is the intake signal, the signal is integrated as a positive value, so the ventilation volume increases. On the other hand, during the period of L2, which is the expiration signal, the signal is integrated as a negative value, so the ventilation volume decreases.
- L1 which is the intake signal
- L2 which is the expiration signal
- the ventilation volume increases during the period of L3 (inspiratory signal), the ventilation volume decreases during the period of L4 (expiratory signal), the ventilation volume increases during the period of L5 (inspiratory signal), and L6 (expiratory signal).
- the ventilation volume decreases during the period of , the ventilation volume increases during the period of L7 (inhalation signal), and the ventilation volume decreases during the period of L8 (expiration signal).
- FIG. 5 is a graph showing an example of temporal changes in corrected ventilation volume information.
- the signals are integrated as positive values, so the ventilation volume increases.
- the signals are integrated as negative values, so the ventilation volume decreases.
- the information corresponding to the ventilation volume is waveform information.
- Data processing is a series of processes executed by control unit 510 from acquisition of a respiratory signal to final output of ventilation volume information.
- FIG. 6 is a flowchart for explaining data processing.
- data processing starts at the timing when measurement device 130 and data processing device 500 establish communication and detector 132 starts acquiring respiratory signals.
- the control unit 510 acquires the respiratory signal acquired by the detector 132 in S1 on the data processing device 500 side, and advances the processing to S2. Respiratory signals that have already been acquired are held as a respiratory signal group of time-series data. In S2, the control unit 510 adds the newly acquired respiratory signal to the respiratory signal group (time-series data), and advances the process to S3.
- the control unit 510 determines whether or not a predetermined condition is satisfied.
- the predetermined condition is a condition for determining to which of the inspiratory signal and the expiratory signal the newly acquired respiratory signal group belongs.
- the predetermined condition may be established at the timing when the respiratory signal value becomes 0 (breathing sound is interrupted). Alternatively, the predetermined condition may be established at predetermined time intervals.
- control unit 510 determines that the predetermined condition is satisfied (YES in S3), the process proceeds to S4. On the other hand, if the control unit 510 does not determine that the predetermined condition is satisfied (NO in S3), it returns the process to S1 and continues acquiring the respiratory signal until the predetermined condition is satisfied.
- the control unit 510 executes a ventilation amount information calculation process in S4, and advances the process to S5.
- the ventilation volume information is calculated by the ventilation volume information calculation process. Details will be described later with reference to FIG.
- the control unit 510 performs a process of outputting the calculated ventilation volume information to the display device 600, and advances the process to S6.
- the display device 600 displays ventilation information. For example, the ventilation volume information as shown in FIG. 5 is displayed on the display device 600 .
- the ventilation volume information is not displayed purely in real time, but is displayed on the display device 600 after a short time lag.
- the control unit 510 determines in S6 whether or not the termination condition is satisfied. For example, the termination condition is satisfied when subject A terminates acquisition of respiratory signals by detector 132 or when communication with measurement device 130 terminates.
- control unit 510 determines that the end condition is satisfied (YES in S6), it ends the data processing. On the other hand, when the control unit 510 does not determine that the end condition is satisfied (NO in S6), the process returns to S1. In this case, the control unit 510 continues to acquire the respiratory signal, and the ventilation volume information calculation process is performed at the next timing when the predetermined condition is satisfied.
- FIG. 7 is a flowchart for explaining the ventilation volume information calculation process.
- Control unit 510 executes a ventilation amount information calculation process.
- the control unit 510 determines in S11 whether each of the acquired respiratory signal groups is an inspiratory signal corresponding to the inspiratory phase or an expiratory signal corresponding to the expiratory phase, The process proceeds to S12. As described above, based on the waveform shape, it is determined whether the current phase is the expiratory phase or the inspiratory phase.
- the control unit 510 determines whether or not the correction coefficient update flag is ON. In this embodiment, when a predetermined value is used as the correction coefficient, the correction coefficient update flag is set to OFF. On the other hand, when determining the correction coefficient based on the measured values of the respiratory signal group, the correction coefficient update flag is set to ON.
- the control unit 510 can calculate ventilation volume information with higher accuracy based on the measured values.
- the control unit 510 does not calculate the correction coefficient, so the processing load on the data processing device 500 can be reduced.
- the setting of the correction coefficient update flag may be changeable by the user, or ON or OFF may be set in advance for each product.
- control unit 510 determines that the correction coefficient update flag is set to ON (YES in S12), the process proceeds to S13. On the other hand, when control unit 510 does not determine that the correction coefficient update flag is set to ON (NO in S12), the process proceeds to S15.
- the correction coefficient K is a value obtained by dividing the integrated value of the absolute values of the inspiratory signals in the respiratory signal group by the integrated value of the absolute values of the expiratory signals in the respiratory signal group.
- the correction coefficient may be calculated using all measured respiratory signals, or may be calculated using some respiratory signals.
- an inspiratory phase+expiratory phase may be set as one set, and calculation may be performed using all measured sets, or calculation may be performed using a plurality of most recent sets.
- the control unit 510 updates the correction coefficient K in S14, and advances the process to S16. Specifically, the correction coefficient K calculated last time is replaced with the correction coefficient K calculated this time for updating. In this way, control unit 510 updates correction coefficient K each time a predetermined condition is satisfied (S3).
- control unit 510 reads a predetermined correction coefficient K, and advances the process to S16.
- the correction coefficient K a predetermined value is used as the correction coefficient K.
- the control unit 510 corrects each exhalation signal of the respiratory signal group by multiplying it by the correction coefficient K, and advances the process to S17. On the other hand, the control unit 510 does not correct the inspiratory signal in the respiratory signal group. In this way, the control unit 510 performs different calculations for the signal that is an inspiratory signal and the signal that is an expiratory signal in the group of respiratory signals.
- control unit 510 converts each respiratory signal belonging to the inspiratory phase into a positive value, converts each respiratory signal belonging to the expiratory phase into a negative value, and advances the process to S18. Specifically, control unit 510 converts a respiratory signal belonging to the inspiratory phase into a positive value by taking the absolute value of the respiratory signal (inspiratory signal). As for the respiratory signal belonging to the expiratory phase, the control unit 510 takes the absolute value of the respiratory signal (expiratory signal) and multiplies it by -1 to convert it into a negative value. In S18, the control unit 510 calculates the integrated value of the post-conversion respiratory signal group at each time as the ventilation volume information, and terminates the ventilation volume information calculation process.
- control unit 510 calculates information corresponding to the ventilation volume due to respiration based on the extracted inhalation signal and exhalation signal. Specifically, the control unit 510 performs correction using the correction coefficient K, and then integrates the respiratory signal group with one of the inspiratory signal and the expiratory signal as a positive value and the other as a negative value, thereby obtaining the ventilation volume. The information corresponding to is calculated.
- FIG. 8 is a flowchart for explaining data processing according to the modification.
- the data processing in this modified example is assumed to be executed after the measurement of all respiratory signals is completed.
- the user stores the respiratory signal group in the memory card 140 after all measurements are completed. Then, this memory card 140 is read into the data processing device 500 . User action initiates data processing using respiratory signal groups on memory card 140 .
- control unit 510 acquires all respiratory signal groups on the memory card 140 in S31, and advances the processing to S32.
- control unit 510 executes the ventilation amount information calculation process (see FIG. 7), and advances the process to S33.
- the control unit 510 may set the correction coefficient update flag to ON and calculate the correction coefficient K for all respiratory signal groups.
- the control unit 510 performs a process of outputting the calculated ventilation volume information to the display device 600, and ends the data processing.
- the display device 600 displays ventilation information. For example, the ventilation volume information as shown in FIG. 5 is displayed on the display device 600 .
- information corresponding to the ventilation volume is calculated based on the respiratory signal group acquired by the detector 132 attached to the human body.
- Document B discloses a belt-type respirometer for estimating the amount of ventilation due to respiration by attaching a detector to the human body.
- control unit 510 outputs information corresponding to the ventilation volume calculated based on the respiratory signal group acquired by the detector 132 attached to the human body, so that the subject can act freely. also facilitates data measurement. Further, the control unit 510 performs different calculations on each signal of the respiratory signal group depending on whether the signal is an inhalation signal or an exhalation signal. , the information corresponding to the ventilation volume can be calculated. As a result, even in an environment where the subject can act freely, the information corresponding to the ventilation volume can be easily grasped.
- the configuration is not limited to this, and a configuration including a plurality of detectors is also possible. Differences from the first embodiment will be described below, and descriptions of common parts will be omitted.
- FIG. 9 is a diagram showing an example of the overall configuration of a respiration measurement system 1a according to the second embodiment.
- the respiration measurement system 1 a includes a respiration measurement device 10 a and a display device 600 .
- the respiration measurement device 10 a includes a data processing device 500 and a measurement device 230 .
- a data processing device 500 and a display device 600 are the same as in the first embodiment.
- FIG. 10 is a diagram showing an example of the measuring device 230. As shown in FIG.
- the measurement device 230 includes a main body 231, arms 232 and 233, and detectors 240-246.
- An arm 232 and an arm 233 extend from both ends of the body portion 231 .
- Each of the arms 232 and 233 has a shape that curves and extends along the head of the subject A when the measuring device 230 is worn.
- the arms 232 and 233 are extended in a substantially semicircular shape.
- the subject A's ear is put on the arc portion of this approximately semicircle.
- Main body 231 and each of detectors 240 to 246 are connected by wiring.
- FIG. 11 is a diagram for explaining a state in which the measuring device 230 is attached to the human body (subject A).
- Detector 240 acquires a respiratory signal, like detector 132 of the first embodiment.
- Detectors 241 to 246 also acquire biosignals such as myoelectric potential of the face, body temperature, and heart rate.
- detectors 241, 242, 244, and 245 are attached to subject A's face. These sensors are attached to, for example, the zygomaticus muscle or corrugator muscle, and acquire the myoelectric potential of the zygomatic muscle or the myoelectric potential of the corrugator muscle.
- Detector 243 is a sensor that measures Subject A's heart rate.
- Detector 246 is a sensor that acquires subject A's body temperature.
- FIG. 12 is a diagram showing a display example of output information.
- the control unit 510 can output a biological signal different from the ventilation volume information together with the ventilation volume information.
- biomedical signals biomedical signals such as the above-described body temperature and heart rate are output.
- the screen 160 displays ventilation information.
- a graph of signal waveforms is displayed as ventilation volume information.
- screen 160 shows that the current breathing rate is 16 breaths/minute.
- the ventilation information it is possible to grasp the subject's respiratory status. For example, by observing the signal waveform, it is possible to grasp whether the person is in a deep and slow breathing state or a shallow and rapid breathing state. If the breathing is deep and slow, it can be determined that the subject is in a relaxed state. In addition to this, a tense state, a concentrated state, and the like can be determined as biometric information.
- biological information such as "relaxed state”, “tensed state”, and “concentrated state” can be calculated and obtained from the signal waveform.
- the biological information shown in the present embodiment is information indicating the state of autonomic nerves.
- the fact that the user is in a "relaxed state” is displayed as biometric information.
- one signal waveform may be generated from the acquisition result of the detector 240 that acquires the respiratory signal, or information indicating the state of the autonomic nervous system may be generated.
- the data processing device 500 can estimate the emotion corresponding to the four myoelectric potentials using the table in which the four myoelectric potentials and emotions are associated. Information estimated in this way may be displayed on the screen 160 .
- a respiration measurement method includes the steps of acquiring respiration signals by a detector attached to a human body; and calculating information corresponding to respiratory ventilation based on the extracted first and second signals.
- the calculating step includes performing different operations on each signal of the group of respiratory signals when the signal is the first signal and when the signal is the second signal.
- the respiratory measurement method described in item 1 for each signal of the respiratory signal group, when the signal is the first signal corresponding to the inspiratory phase and when the signal is the second signal corresponding to the expiratory phase Perform different calculations at different times. By doing so, it is possible to easily grasp the information corresponding to the ventilation volume even in an environment where the subject can act freely.
- the information corresponding to the ventilation volume includes waveform information.
- the information corresponding to the ventilation volume includes biological information obtained by calculation.
- the step of calculating is a step of multiplying each of the second signals of the group of respiratory signals by a correction coefficient to correct them. , calculating information corresponding to ventilation by integrating the group of respiratory signals with one of the first signal and the second signal having a positive value and the other having a negative value.
- each of the second signals is multiplied by the correction coefficient to correct the characteristics of the first signal corresponding to the inspiratory phase and the second signal corresponding to the expiratory phase. Errors due to differences can be corrected.
- the correction coefficient is the integrated value of the absolute value of the first signal in the respiratory signal group, and the integrated value of the absolute value of the second signal in the respiratory signal group. is a value divided by
- errors can be corrected by matching the total amount of ventilation due to inspiration and the total amount of ventilation due to expiration.
- the correction coefficient is a predetermined value.
- (Item 8) The respiration measurement method according to any one of items 1 to 7, further comprising a step of outputting information corresponding to the calculated ventilation volume, wherein the outputting step corresponds to the ventilation volume. outputting a biomedical signal different from the information corresponding to the ventilation with the information corresponding to the ventilation.
- biological information can be grasped not only from information corresponding to the ventilation volume, but also from information different from this.
- a respiration measurement device includes a detector that acquires a respiration signal while attached to a human body, and a controller that processes the respiration signal.
- the controller extracts a first signal corresponding to the inspiratory phase and a second signal corresponding to the expiratory phase from each of the respiratory signal groups acquired by the detector.
- the control unit calculates information corresponding to the ventilation volume due to respiration based on the extracted first signal and second signal.
- the control unit performs different calculations on the signal that is the first signal and the signal that is the second signal in the group of respiratory signals.
- the respiration measurement device for each signal of the respiratory signal group, when the signal is the first signal corresponding to the inspiratory phase and when the signal is the second signal corresponding to the expiratory phase Perform different calculations at different times. By doing so, it is possible to easily grasp the information corresponding to the ventilation volume even in an environment where the subject can act freely.
- the detector includes a storage unit that stores the acquired respiratory signal, and a transmitter that wirelessly transmits the respiratory signal stored in the storage unit to the control unit. include.
- the respiration measurement device of item 10 by configuring wireless communication between the detector that acquires the respiration signal and the control unit that processes the respiration signal, an environment in which the subject can freely act , information corresponding to the ventilation volume can be easily grasped.
- a respiration measurement system includes the respiration measurement device according to Item 9 or 10, and a display device.
- the control unit outputs information corresponding to the calculated ventilation volume.
- the display device displays information corresponding to the output ventilation volume.
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Abstract
Description
まず、第1実施形態に係る呼吸測定システム1について説明する。図1は、第1実施形態に係る呼吸測定システム1の全体構成の一例を示す図である。呼吸測定システム1は、取得した呼吸信号に基づき換気量に対応する情報を算出し、当該情報を表示装置600に表示するものである。
図3A~図3Cは、呼吸信号の絶対値の積算値およびその補正方法を説明するための図である。図3Aには、図2で示したL1~L8の各期間において、呼気信号の絶対値の積算値(以下、「呼気積算値」とも称する)または吸気信号の絶対値の積算値(以下、「吸気積算値」とも称する)をそれぞれ算出したものが示されている。また、上述のような手法により、L1~L8のそれぞれが、呼気および吸気のいずれであるかが判定された結果が示されている。
ベルト型呼吸計は、ベルトを胸部に巻いて、呼吸によるベルト長の変化を検出して、胸部の立体的変化から換気量を推定する。しかしながら、ベルト型呼吸計は胸部の拘束感が強いため、被験者が自由に行動できる環境において換気量の計測を行えているとは言いがたい。
第1実施形態においては、1つの検出器を備える構成とした。しかし、これに限らず、複数の検出器を備える構成としてもよい。以下、第1実施形態と異なる点について説明し、共通する部分については説明を省略する。
(第1項)一態様に係る呼吸測定方法は、人体に取り付けた検出器によって呼吸信号を取得するステップと、取得した呼吸信号群の各々から第1信号および呼気相に対応する第2信号を抽出するステップと、抽出した第1信号および第2信号に基づき、呼吸による換気量に対応する情報を算出するステップとを備える。算出するステップは、呼吸信号群の各々の信号に対して、当該信号が第1信号であるときと第2信号であるときとで異なる演算を行うステップを含む。
Claims (11)
- 人体に取り付けた検出器によって呼吸信号を取得するステップと、
取得した呼吸信号群の各々から吸気相に対応する第1信号および呼気相に対応する第2信号を抽出するステップと、
抽出した前記第1信号および前記第2信号に基づき、呼吸による換気量に対応する情報を算出するステップとを備え、
前記算出するステップは、前記呼吸信号群の各々の信号に対して、当該信号が前記第1信号であるときと前記第2信号であるときとで異なる演算を行うステップを含む、呼吸測定方法。 - 前記換気量に対応する情報は、波形情報を含む、請求項1に記載の呼吸測定方法。
- 前記換気量に対応する情報は、計算により求めた生体情報を含む、請求項1に記載の呼吸測定方法。
- 前記算出するステップは、
前記呼吸信号群のうち前記第2信号の各々に補正係数を乗じて補正するステップと、
前記第1信号および前記第2信号の一方を正の値とし他方を負の値として前記呼吸信号群を積算することにより、前記換気量に対応する情報を算出するステップとを含む、請求項1に記載の呼吸測定方法。 - 前記補正係数は、前記呼吸信号群のうち前記第1信号の絶対値の積算値を、前記呼吸信号群のうち前記第2信号の絶対値の積算値で除した値である、請求項4に記載の呼吸測定方法。
- 所定条件が成立するごとに前記補正係数を更新するステップをさらに備える、請求項5に記載の呼吸測定方法。
- 前記補正係数は、予め定められた値である、請求項4に記載の呼吸測定方法。
- 算出した前記換気量に対応する情報を出力するステップをさらに備え、
前記出力するステップは、前記換気量に対応する情報とともに、前記換気量に対応する情報とは異なる生体信号を出力するステップを含む、請求項1に記載の呼吸測定方法。 - 人体に取り付けた状態で呼吸信号を取得する検出器と、
前記呼吸信号を処理する制御部とを備え、
前記制御部は、
前記検出器が取得した呼吸信号群の各々から吸気相に対応する第1信号および呼気相に対応する第2信号を抽出し、
抽出した前記第1信号および前記第2信号に基づき、呼吸による換気量に対応する情報を算出し、
前記呼吸信号群のうち前記第1信号である信号と前記第2信号である信号とで異なる演算を行う、呼吸測定装置。 - 前記検出器は、
取得した前記呼吸信号を記憶する記憶部と、
前記記憶部に記憶された前記呼吸信号を前記制御部に無線で送信するトランスミッタとを含む、請求項9に記載の呼吸測定装置。 - 請求項9に記載の呼吸測定装置と、
表示装置とを備え、
前記制御部は、算出した前記換気量に対応する情報を出力し、
前記表示装置は、出力された前記換気量に対応する情報を表示する、呼吸測定システム。
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