JP5970712B2 - Biological information measurement circuit, apparatus, program, and method - Google Patents

Biological information measurement circuit, apparatus, program, and method Download PDF

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JP5970712B2
JP5970712B2 JP2012250938A JP2012250938A JP5970712B2 JP 5970712 B2 JP5970712 B2 JP 5970712B2 JP 2012250938 A JP2012250938 A JP 2012250938A JP 2012250938 A JP2012250938 A JP 2012250938A JP 5970712 B2 JP5970712 B2 JP 5970712B2
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biological information
acceleration sensor
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measurement
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JP2014097216A (en
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正道 泉田
正道 泉田
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セイコーエプソン株式会社
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  The present invention relates to a biological information measurement circuit capable of measuring a subject's breathing cycle or breathing frequency (the number of breaths per minute) based on a detection result of an acceleration sensor during running or jogging. The present invention also relates to a biological information measuring device including an acceleration sensor and a biological information measuring circuit. Furthermore, the present invention relates to a biological information measuring program and a biological information measuring method used in such a biological information measuring device.

  During running or jogging, it is desired to measure heart rate, respiratory cycle or frequency, number of steps, running speed, running distance, and the like. The heart rate is an important body index for knowing whether or not the load on the body is within a predetermined range. The heart rate can be measured by attaching a measuring device including a heart rate sensor to the chest of the subject. Further, the number of steps and the like can be measured by mounting a measuring device including an acceleration sensor on the subject's foot or arm.

  On the other hand, the respiratory cycle or the respiratory frequency is an important body index after the heart rate, and various measurement methods have been proposed. For example, a measurement method has been proposed in which an airflow sensor installed in the vicinity of the subject's nose and mouth detects the inflow or outflow of gas and grasps respiration. A thermocouple or the like is used as the air flow sensor. This measuring method is widely used in screening tests for sleep apnea syndrome.

  In addition, a measurement method has been proposed in which the movement of the lung is grasped by detecting the expansion and contraction of the belt wound around the subject's chest. As the sensor, a piezoelectric film that generates a voltage when a stress is applied, or a sensor that detects a change in inductance is used. Furthermore, a measurement method for measuring a subject's impedance by applying a high-frequency signal to the subject, and grasping respiration from the change, and a measurement method for grasping respiration by performing signal processing on fluctuations in the heartbeat signal have been proposed.

  In addition, a measurement method for grasping respiration by signal processing of fluctuation of the pulse wave propagation time signal, a measurement method for grasping respiration by processing an output signal of an array such as a pressure sensor provided in a bed or a sheet, and the like A measurement method for grasping respiration and heartbeat based on a reflected wave from a subject with respect to a high frequency in the GHz band has also been proposed.

  Although various measurement methods have been proposed for measuring the respiratory cycle or the respiratory frequency in this way, many measurement methods have been developed for medical use and should be used at rest or at bedtime. It is assumed. Therefore, there is a thing that is not suitable for measurement during intense exercise because it is necessary to connect a large measuring device to the sensor with a cable or accurate measurement cannot be performed under disturbance due to intense exercise such as running or aerobics. There were many.

  By the way, in the case of training applications such as running and jogging, it is very complicated to wear a plurality of measuring devices on a subject, and both measuring devices are provided with both a heart rate sensor and an acceleration sensor. It is convenient if the heart rate, the number of steps, the running speed, the running distance, and the like can be measured by attaching to the chest of the subject. Furthermore, it would be more convenient if the acceleration cycle could be used to measure the respiratory cycle or respiratory frequency.

  As a related technique, Patent Document 1 discloses a respiratory detection device that measures a respiratory cycle without causing a subject to feel abnormalities due to addition or restraint while performing normal office work. The respiratory detection device includes an acceleration sensor for detecting sound or movement generated by the heart at one or more points of a subject, and a signal in a period corresponding to one heartbeat in an electrical signal from the acceleration sensor. The amplitude maximum and / or minimum corresponding to a specific motion of the heart is extracted, and then the amplitude maximum and / or minimum corresponding to the same motion as the tip of the heart is obtained from a signal in a period corresponding to another heartbeat. Means for generating periodic signal information that modulates the attenuation characteristics of the organ from the heart to the acceleration sensor by respiration by performing extraction and means for interpolating and connecting the amplitude maximum value and / or minimum value. And respiration information is extracted from the information of the periodic signal.

Japanese Patent No. 312757 (paragraphs 0007-0008)

  However, the respiration detection device of Patent Document 1 cannot measure the respiration cycle when a large acceleration occurs in the subject during running or jogging. Accordingly, one of the objects of the present invention is to provide a biological information measurement circuit or the like that can measure the breathing cycle or breathing frequency of a subject based on the output of an acceleration sensor even during running or jogging. .

  In order to solve the above problems, a biological information measurement circuit according to one aspect of the present invention measures at least a respiratory cycle based on a detection result of an acceleration sensor that detects at least a frontal acceleration generated in a chest of a subject. A biological information measuring circuit for measuring a cycle of one step or overlapping steps when a subject is walking or running based on measurement data representing acceleration detected by an acceleration sensor, and the cycle is a unit period A control unit that is set as a storage unit that stores measurement data representing acceleration in the front direction detected by the acceleration sensor at least in the unit period, and is detected by the acceleration sensor in the first unit period and stored in the storage unit Measurement data representing the acceleration in the front direction and the acceleration sensor in the second unit period different from the first unit period It obtains the difference data representing the difference between the measured data representative of the acceleration of the detected front direction I, and a calculation unit for obtaining a respiratory cycle on the basis of said difference data.

  According to one aspect of the present invention, at least frontal acceleration generated in a subject's chest is detected in a plurality of unit periods, and a difference between them is obtained, thereby reducing a fluctuation component of acceleration caused by walking or running. be able to. Therefore, even during training such as running or jogging, it is possible to measure the respiratory cycle while eliminating large waveforms caused by walking or running. Further, the only sensor required for this purpose is an acceleration sensor used during normal training.

  Here, the calculation unit may perform low-pass filter processing on the difference data to generate processing data, and detect the reference time point in the respiratory cycle by comparing the value of the processing data with a threshold value. By setting the cut-off frequency of the low-pass filter to be relatively high, it is possible to measure the respiratory cycle at a response speed close to real time.

  At this time, the calculation unit sets the first reference time when the value of the processing data exceeds the positive or negative threshold, and the value of the processing data again sets the threshold after the masking period has elapsed from the first reference time. You may make it obtain | require as a respiratory cycle the difference with the 2nd reference | standard time exceeded. By providing the masking period, erroneous detection at the second reference time can be prevented.

  Further, the calculation unit may adjust the length of the masking period for the next measurement based on the already measured respiratory cycle. Thereby, the length of the masking period can be adjusted according to the length of the respiratory cycle.

  A biological information measuring device according to one aspect of the present invention includes an acceleration sensor that detects at least a frontal acceleration generated in a chest of a subject, and a biological information measuring circuit according to any aspect of the present invention. By using the acceleration sensor, the respiratory cycle can be measured even during training such as running or jogging.

  A biological information measurement program according to one aspect of the present invention is a biological information measurement program for measuring at least a respiratory cycle based on a detection result of an acceleration sensor that detects at least frontal acceleration generated in a chest of a subject. Then, based on measurement data representing acceleration detected by the acceleration sensor, a procedure for measuring a cycle of one step or overlapping steps when the subject is walking or running and setting the cycle as a unit period (a ), A procedure (b) for storing measurement data representing the acceleration in the front direction detected by the acceleration sensor in the first unit period in the storage unit, and a measurement data stored in the storage unit in the procedure (b), Difference from measurement data representing acceleration in the front direction detected by the acceleration sensor in a second unit period different from the first unit period Obtaining the difference data representing the procedure (c), to perform the Procedure for obtaining a respiratory cycle on the basis of the difference data determined in (c) (d) to the CPU.

  Furthermore, a biological information measuring method according to one aspect of the present invention is a biological information measuring method that measures at least a respiratory cycle based on a detection result of an acceleration sensor that detects at least frontal acceleration generated in a chest of a subject. (A) measuring a cycle of one step or overlapping steps when the subject is walking or running based on measurement data representing acceleration detected by the acceleration sensor, and setting the cycle as a unit period; (B) storing measurement data representing the acceleration in the front direction detected by the acceleration sensor in the first unit period in the storage unit, measurement data stored in the storage unit in step (b), The difference from the measurement data representing the acceleration in the front direction detected by the acceleration sensor in the second unit period different from the unit period of Comprising a step (c) determining the to difference data, and a step (d) to determine the breathing cycle based on the difference data determined in step (c).

  By performing the difference calculation as described above, it is possible to reduce the fluctuation component of the acceleration caused by walking or running. Therefore, even during training such as running or jogging, it is possible to measure the respiratory cycle while eliminating large waveforms caused by walking or running.

The schematic diagram which shows the structural example of the biological information measuring device which concerns on one Embodiment of this invention. The figure which shows the waveform of the output signal showing the acceleration of a X-axis direction at the time of the test subject's driving | running | working. The figure which shows the waveform of the output signal showing the acceleration of a Y-axis direction when a test subject is drive | working. The figure which shows the waveform of the output signal showing the acceleration of a Z-axis direction at the time of the test subject's driving | running | working. The block diagram which shows the structural example of the biometric information measurement circuit shown in FIG. The figure for demonstrating the process of the measurement data showing the acceleration of a Z-axis direction. The figure for demonstrating the process of the measurement data showing the acceleration of a Z-axis direction. The figure for demonstrating the process of the measurement data showing the acceleration of a Z-axis direction. The figure for demonstrating the process of the measurement data showing the acceleration of a Z-axis direction. The flowchart which shows the biometric information measuring method which concerns on one Embodiment of this invention.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. The biological information measuring apparatus according to the present invention can measure at least the respiratory cycle using an acceleration sensor that detects at least the acceleration in the front direction generated in the chest of the subject. Further, the biological information measuring apparatus according to the present invention may measure the number of steps, the running speed, the running distance, and the like during training such as running or jogging. In that case, it is desirable to use a triaxial acceleration sensor as the acceleration sensor. In the following embodiments, a biological information measuring device that further has a function of measuring a heart rate and is worn on the chest of a subject using a belt will be described as an example.

  FIG. 1 is a schematic diagram showing a configuration example of a biological information measuring apparatus according to an embodiment of the present invention. 1A is a front view, and FIG. 1B is a rear view. As shown in FIG. 1 (A), this biological information measuring device includes a three-axis acceleration sensor 10, a biological information measuring circuit 20, a wireless communication unit 30, and an antenna unit 40 on the first surface of the circuit board 1. Including. As shown in FIG. 1B, the biological information measuring apparatus includes heart rate measuring electrode terminals 51 and 52 and a battery socket 60 on the second surface of the circuit board 1.

  The triaxial acceleration sensor 10 detects acceleration in the lateral direction (X-axis direction) of the subject, acceleration in the vertical direction (Y-axis direction), and acceleration in the front direction (Z-axis direction) of the subject. Are generated. The front direction is a direction in which the subject moves forward when the subject walks or runs. When the triaxial acceleration sensor 10 is attached to the subject so that the Z-axis direction is different from the frontal direction of the subject, the frontal direction is estimated by estimating the frontal direction from the value of the triaxial acceleration of the triaxial acceleration sensor 10. The acceleration at may be obtained.

  The biological information measuring circuit 20 measures the breathing cycle or breathing frequency (number of breaths per minute), the number of steps, the running speed, the running distance, and the like based on the output signal of the three-axis acceleration sensor 10. The biological information measurement circuit 20 may measure the heart rate of the subject using the electrode terminals 51 and 52 for measuring the heart rate.

  The wireless communication unit 30 wirelessly transmits the measurement result obtained by the biological information measurement circuit 20 to an external device such as a wristwatch type display device or a smartphone using the antenna unit 40. The external device that has received the measurement result displays the measurement result on a display or stores it in a storage medium. Thereby, the subject can visually confirm the measurement result.

  The wireless communication unit 30 may be configured by a semiconductor integrated circuit device (IC). The antenna unit 40 is configured by a wiring pattern formed on the circuit board 1, for example. In that case, it is desirable that other wiring patterns are not formed in the region 1 a around the antenna unit 40 on the first and second surfaces of the circuit board 1. Inside the battery socket 60, a CR battery (coin-type lithium battery) that supplies power to each part of the biological information measuring device is mounted.

  FIG. 2 is a diagram illustrating a waveform of an output signal representing the acceleration in the X-axis direction generated by the three-axis acceleration sensor when the subject is running. FIG. 3 is a diagram illustrating a waveform of an output signal representing acceleration in the Y-axis direction generated by the three-axis acceleration sensor when the subject is running. FIG. 4 is a diagram illustrating a waveform of an output signal representing the acceleration in the Z-axis direction generated by the three-axis acceleration sensor when the subject is running.

  2 to 4, the horizontal axis represents time (seconds), and the vertical axis is an arbitrary unit. The period of one step of the subject is about 0.4 seconds. In the present application, “one step” refers to an operation from when a heel on one side (for example, a heel on the left foot) contacts the ground until the next heel (for example, the heel on the right foot) contacts the ground. In addition, “overlapping” refers to an operation from the grounding of one side to the next grounding of the same side.

  As shown in FIG. 2, it can be seen that the acceleration in the X-axis direction can be correlated with the cycle of overlapping steps. On the other hand, as shown in FIGS. 3 and 4, it can be seen that the acceleration in the Y-axis direction and the acceleration in the Z-axis direction can be correlated with the cycle of one step. Therefore, it is possible to detect the cycle of overlapping steps based on the acceleration in the X-axis direction. In addition, the cycle of one step or overlapping steps can be detected based on the acceleration in the Y-axis direction or the Z-axis direction.

  However, the acceleration in the Z-axis direction includes acceleration due to respiration in addition to acceleration due to running. When a subject walks or runs, a large waveform due to walking or running overlaps with a waveform due to breathing, so even if the motion of the lungs due to breathing is detected by an acceleration sensor, the waveform due to breathing is buried in the waveform due to walking or running. End up.

  The frequency of the waveform due to walking or running is mainly about 2 Hz to 4 Hz, but the frequency of the waveform due to breathing is a slow frequency of about 0.5 Hz. Therefore, when trying to extract a waveform due to respiration with a normal low-pass filter, the time constant of the low-pass filter becomes very large, and it takes a long time for the output of the low-pass filter to stabilize and measure the respiration cycle.

  However, since the pace may be changed during training, it is desirable that the respiratory cycle can be measured with a response speed close to real time. Therefore, in the present embodiment, during running or jogging, the cycle of one step or overlapping steps when the subject walks or runs is used as a unit period for measuring the respiratory cycle. Considering the case where the walking cycle of the left foot and the walking cycle of the right foot do not match, it is desirable to set the cycle of overlapping steps as a unit period.

  FIG. 5 is a block diagram showing a configuration example of the biological information measurement circuit shown in FIG. As shown in FIG. 5, the biological information measurement circuit 20 includes an input unit 21, a storage unit 22, a calculation unit 23, and a control unit 24. The biological information measurement circuit 20 may further include a heart rate sensor unit 25. In the configuration of the biological information measurement circuit shown in FIG. 5, some of the components may be connected to the biological information measurement circuit 20 from the outside. For example, at least a part of the storage unit 22 may be a memory device provided outside the biological information measurement circuit 20.

  The input unit 21 inputs three output signals respectively representing accelerations detected in the X-axis direction, the Y-axis direction, and the Z-axis direction by the three-axis acceleration sensor 10, and amplifies and samples the output signals. To generate three types of measurement data. The generated measurement data is supplied to the storage unit 22 to the control unit 24 as necessary. The storage unit 22 can store measurement data representing acceleration in the Z-axis direction detected by the triaxial acceleration sensor 10 at least in a unit period.

  The control unit 24 determines, based on at least the measurement data representing the acceleration in the Z-axis direction, whether the subject is in motion, i.e., whether the subject is walking or running, or whether the subject is resting or sleeping. May be. The control unit 24 may set the unit period according to the determination result and control the operations of the storage unit 22 and the calculation unit 23.

  When the subject is walking or running, the control unit 24 detects a plurality of maximum values of measurement data representing acceleration in the X-axis direction, and measures the period of the overlapping steps based on them. Alternatively, the control unit 24 detects a plurality of maximum values of measurement data representing acceleration in the Y-axis direction or the Z-axis direction, and measures the period of one step or overlapping steps based on them. Instead of detecting the maximum value, the minimum value may be detected.

  Next, the control unit 24 sets a cycle of one step or overlapping steps as a unit period. By performing the difference calculation of the measurement data in the two unit periods set in such a manner, the fluctuation component of the acceleration caused by walking or running can be reduced.

  The control unit 24 may count the number of overlapping steps based on measurement data representing acceleration in the X-axis direction, or may calculate the number of steps or overlapping steps based on measurement data representing acceleration in the Y-axis direction or Z-axis direction. You may count. Here, the “number of overlapping steps” refers to the number of operations from the time when a heel on one side is grounded to the time when the same heel is grounded again. The count result is output to the calculation unit 23.

  On the other hand, when the subject is in a resting state or a sleeping state, the control unit 24 may use the unit period that has already been set as it is, or may use a unit period different from this. However, in consideration of the accuracy and speed of measurement, the unit period is preferably a period of about 1/8 to 1/2 of a general respiratory cycle (about 2 seconds).

  Under the control of the control unit 24, measurement data D11 to D1n representing acceleration in the Z-axis direction detected by the triaxial acceleration sensor 10 in the first unit period are stored in the storage unit 22. Further, under the control of the control unit 24, the measurement data D11 to D1n stored in the storage unit 22 are supplied to the calculation unit 23 in the second unit period following the first unit period, and the second Measurement data D21 to D2n representing the acceleration in the Z-axis direction detected by the three-axis acceleration sensor 10 in the unit period are supplied to the calculation unit 23.

  The computing unit 23 includes measurement data D11 to D1n representing acceleration in the Z-axis direction detected in the first unit period, measurement data D21 to D2n representing acceleration in the Z-axis direction detected in the second unit period, and The difference data representing the difference is obtained. The calculation unit 23 obtains a respiratory cycle based on the difference data. Further, the calculation unit 23 may obtain the respiration frequency (the number of respirations per minute) by dividing 60 (seconds) by the respiration cycle (seconds). The above operation is repeated for a plurality of unit periods.

  Here, the first unit period and the second unit period do not necessarily have to be temporally continuous periods. For example, the second unit period may be started after a lapse of a predetermined period from the first unit period. Alternatively, when there is an abnormality such as noise in the data of the first unit period, data of the unit period without an abnormality may be adopted as the data of the first unit period. Furthermore, the data of the first unit period may be average data of a plurality of unit periods. The same applies to the second unit period.

  By performing the difference calculation as described above, a large waveform mainly due to walking or running disappears. This is because, when a human walks or runs, the correlation of acceleration for each step or every overlapping step is very high. Accordingly, the calculation unit 23 performs a light low-pass filter process on the obtained difference data to generate process data, and detects a reference time point in the breathing cycle of the subject by comparing the value of the process data with a threshold value. Also good.

  For example, when the sampling frequency when sampling the output signal of the triaxial acceleration sensor 10 is 100 Hz, the cut-off frequency of the low-pass filter may be about 25 Hz to 33 Hz, which is 1/4 to 1/3 of the sampling frequency. . Thus, the respiratory cycle can be measured using a low-pass filter having a cutoff frequency that is approximately 50 times higher than the frequency of respiration. This makes it possible to measure the respiratory cycle or the respiratory frequency at a response speed close to real time.

  6A to 6D are diagrams for explaining processing of measurement data representing acceleration in the Z-axis direction when the subject is traveling. 6A to 6D, the horizontal axis represents time (seconds), and the vertical axis represents acceleration values (4096 = 1G). 6A shows the waveform of the measurement data supplied from the input unit 21, and FIG. 6B shows the waveform of the measurement data obtained by delaying the time series of the measurement data shown in FIG. 6A by the period of the overlapping steps. 6C shows a waveform of difference data obtained by subtracting the measurement data shown in FIG. 6B from the measurement data shown in FIG. 6A. FIG. 6D shows a low-pass filter process applied to the difference data shown in FIG. 6C. The waveform of the processed data is shown.

  In FIG. 6D, the cutoff frequency of the low-pass filter is 30 Hz, the threshold value is −500, and the length of the masking period M is 0.4 seconds. As shown in FIG. 6D, the calculation unit 23 sets the processing data value to the threshold value again after the first reference time point T1 when the processing data value exceeds the threshold value, and after the masking period M has elapsed from the first reference time point T1. The difference from the second reference time point T2 exceeding the threshold value may be obtained as the respiratory cycle P. In the example shown in FIG. 6D, the calculation unit 23 determines whether or not the value of the processing data has exceeded the negative threshold value, but whether or not the value of the processing data has exceeded the positive threshold value. May be determined.

  By providing the masking period M in the detection of the reference time point in the respiratory cycle, erroneous detection of the second reference time point can be prevented. The length of the masking period M may be a preset value (for example, 0.4 seconds to 1.0 seconds). Alternatively, the initial value of the masking period M may be set in advance, and the calculation unit 23 illustrated in FIG. 5 may adjust the length of the masking period M based on the already measured respiratory cycle. For example, the calculation unit 23 may set a period of 1/5 to 1/2 of the measured respiratory cycle P as the masking period M for the next measurement. Thereby, the length of the masking period can be adjusted according to the length of the respiratory cycle.

  In this way, the calculation unit 23 obtains the difference between the first reference time T1 and the second reference time T2 as the respiratory cycle, and then the difference between the second reference time T2 and the third time T3. Is obtained as a respiratory cycle, and the difference between the third time point T3 and the fourth time point T4 is obtained as a respiratory cycle, and such an operation is repeated.

  In addition, the calculation unit 23 may obtain the running speed by multiplying the set value of the step per step by the number of steps per unit time, or may integrate the running speed or set the set value of the step per step. The travel distance may be obtained by multiplying the number of steps. Considering that the left and right stride are different, it is desirable to use an average value of the left foot stride and the right foot stride as a step per step.

  Alternatively, the calculation unit 23 may obtain the traveling speed by multiplying the set value of one cycle width by the number of overlapping steps per unit time, with the sum of the left foot stride and the right foot stride being one cycle width, The travel distance may be obtained by integrating the speed or multiplying the set value of one cycle width by the number of overlapping steps.

  On the other hand, the heartbeat sensor unit 25 generates a heartbeat detection signal by measuring the myoelectric potential of the heart via the electrode terminals 51 and 52, and outputs the generated heartbeat detection signal to the calculation unit 23. The calculation unit 23 converts the input heartbeat detection signal into a heart rate per unit time, and outputs data representing the heart rate to the wireless communication unit 30. Further, the calculation unit 23 compares the heart rate with the target heart rate range stored in the storage unit 22 and outputs a warning signal to the wireless communication unit 30 when the heart rate is outside the target heart rate range. Anyway.

  The wireless communication unit 30 wirelessly transmits the measurement result and / or warning signal obtained by the calculation unit 23 to an external device such as a wristwatch type display device or a smartphone. The external device displays the measurement results and / or warnings on a display or stores them in a storage medium. The external device may emit a warning sound in response to the warning signal.

  The biological information measurement circuit 20 illustrated in FIG. 5 may be configured with a digital circuit or an analog circuit, or may be configured with a microcomputer. The storage unit 22 is configured by a memory such as a DRAM or an SRAM. At least a part of the storage unit 22 may be configured as a memory device provided outside the biological information measurement circuit 20. Moreover, the calculating part 23 and the control part 24 may be comprised by the central processing unit (CPU) and the recording medium which recorded the software (biological information measurement program) for making CPU perform various processes. As the recording medium, a memory (USB memory, memory card, nonvolatile memory, RAM, or the like), a hard disk, a flexible disk, MO, or MT can be used.

  Moreover, when using a system (for example, PC, cloud system, etc.) separate from the biological information measurement circuit 20 worn by the subject, the program may be recorded on a recording medium included in the system. When a PC or the like is used, it is not generally assumed that the subject wears the PC or the like, so sensor information is acquired by wireless communication or the like from the acceleration sensor 10 configured separately, and the sensor information Software processing is performed based on the program recorded on the recording medium. Moreover, it is good also as a structure which implement | achieves a part of process of the said software as a hardware. In the case of a cloud system, a configuration may be adopted in which a part of biological information measurement processed by the biological information measurement circuit 20 is executed and processed on data wirelessly transmitted from the biological information measurement circuit 20 based on a program of the cloud system. good.

  According to this embodiment, at least frontal acceleration generated in the chest of the subject is detected in a plurality of unit periods, and the difference between them is obtained, thereby reducing the fluctuation component of acceleration caused by walking or running. . Therefore, even during training such as running or jogging, it is possible to measure the respiratory cycle while eliminating large waveforms caused by walking or running. Moreover, as a sensor required for that, it can measure using the acceleration sensor used at the time of training. In the present embodiment, the respiratory cycle of the subject is measured based on at least the detection result of the acceleration sensor that detects the acceleration in the front direction. When any one axis of the acceleration sensor does not coincide with the front direction, the acceleration in the front direction may be obtained by synthesizing the three axis acceleration measurement values of the acceleration sensor.

  Next, a biological information measuring method used in the biological information measuring apparatus according to the present embodiment will be described with reference to FIGS. FIG. 7 is a flowchart showing a biological information measuring method according to an embodiment of the present invention.

  In step S <b> 1 shown in FIG. 7, the control unit 24 measures the cycle of one step or multiple steps when the subject is walking or running based on the measurement data representing the acceleration detected by the triaxial acceleration sensor 10. The period is set as a unit period.

  In step S <b> 2, the control unit 24 stores measurement data representing the acceleration in the front direction detected by the triaxial acceleration sensor 10 in the first unit period in the storage unit 22.

  In step S3, the calculation unit 23 calculates the acceleration in the front direction detected by the triaxial acceleration sensor 10 in the second unit period that is different from the measurement data stored in the storage unit 22 in step S2 and the first unit period. Difference data representing a difference from the measurement data to be represented is obtained.

  In step S4, the calculating part 23 calculates | requires a respiratory cycle based on the difference data calculated | required in step S3. For example, the calculation unit 23 performs low-pass filter processing on the difference data to generate processing data, and detects the reference time point in the respiratory cycle by comparing the value of the processing data with a positive or negative threshold value. The calculation unit 23 then includes a first reference time when the value of the processing data exceeds the threshold value, and a second reference time point when the value of the processing data exceeds the threshold value again after the masking period has elapsed from the first reference time point. The difference between and is determined as the respiratory cycle.

  In step S <b> 5, the calculation unit 23 calculates the respiration frequency (the number of respirations per minute) by dividing 60 (seconds) by the respiration cycle (seconds).

  By performing the difference calculation of the measurement data as described above, a large waveform mainly caused by walking or running disappears, so that it is easy to detect acceleration due to respiration. Therefore, since the respiratory cycle can be measured using a low-pass filter having a cutoff frequency considerably higher than the respiratory frequency, the respiratory cycle or the respiratory frequency can be measured at a response speed close to real time. .

  In the above embodiment, the biological information measuring device used during running, jogging, etc. has been described, but the present invention is not limited to the above described embodiment. For example, the present invention can be applied to medical applications such as screening tests for sleep apnea syndrome, and many variations can be made within the technical idea of the present invention by those who have ordinary knowledge in the technical field. It is.

  DESCRIPTION OF SYMBOLS 1 ... Circuit board, 1a ... Area | region, 10 ... Triaxial acceleration sensor, 20 ... Biological information measurement circuit, 21 ... Input part, 22 ... Memory | storage part, 23 ... Calculation part, 24 ... Control part, 25 ... Heart rate sensor part, 30 ... Wireless communication part, 40 ... Antenna part, 51, 52 ... Electrode terminal, 60 ... Battery socket

Claims (7)

  1. A biological information measurement circuit for measuring at least a respiratory cycle based on a detection result of an acceleration sensor that detects at least frontal acceleration generated in a chest of a subject,
    Based on measurement data representing acceleration detected by the acceleration sensor, a control unit that measures the cycle of one step or multiple steps when the subject is walking or running, and sets the cycle as a unit period;
    A storage unit for storing measurement data representing acceleration in a front direction detected by the acceleration sensor at least in a unit period;
    Measurement data representing the acceleration in the front direction detected by the acceleration sensor in the first unit period and stored in the storage unit, and detected by the acceleration sensor in a second unit period different from the first unit period Calculating difference data representing a difference from measurement data representing acceleration in the front direction, and calculating a respiratory cycle based on the difference data;
    A biological information measuring circuit including:
  2.   The biological information measurement according to claim 1, wherein the calculation unit performs low-pass filter processing on the difference data to generate processing data, and detects a reference time point in a respiratory cycle by comparing the value of the processing data with a threshold value. circuit.
  3.   A first reference time at which the value of the processing data exceeds a positive or negative threshold, and a value at which the value of the processing data exceeds the threshold again after a masking period has elapsed from the first reference time. The biological information measurement circuit according to claim 2, wherein a difference from the two reference time points is obtained as a respiratory cycle.
  4.   The biological information measurement circuit according to claim 3, wherein the calculation unit adjusts a length of a masking period for the next measurement based on the already measured respiratory cycle.
  5. An acceleration sensor for detecting at least frontal acceleration generated in the chest of the subject;
    The biological information measuring circuit according to any one of claims 1 to 4,
    A biological information measuring device including:
  6. A biological information measurement program for measuring at least a respiratory cycle based on a detection result of an acceleration sensor that detects at least frontal acceleration generated in a chest of a subject,
    A procedure (a) for measuring a cycle of one or multiple steps when the subject is walking or running based on measurement data representing acceleration detected by the acceleration sensor, and setting the cycle as a unit period; ,
    A procedure (b) of storing measurement data representing acceleration in the front direction detected by the acceleration sensor in the first unit period in a storage unit;
    A difference representing a difference between the measurement data stored in the storage unit in step (b) and the measurement data representing the acceleration in the front direction detected by the acceleration sensor in a second unit period different from the first unit period. A procedure (c) for obtaining data;
    A procedure (d) for obtaining a respiratory cycle based on the difference data obtained in the procedure (c);
    Is a biological information measurement program for causing a CPU to execute.
  7. A biological information measurement method for measuring at least a respiratory cycle based on a detection result of an acceleration sensor that detects at least frontal acceleration generated in a chest of a subject,
    (A) measuring a cycle of one or multiple steps when the subject is walking or running based on measurement data representing acceleration detected by the acceleration sensor, and setting the cycle as a unit period; ,
    Storing measurement data representing acceleration in the front direction detected by the acceleration sensor in the first unit period in a storage unit (b);
    A difference representing a difference between the measurement data stored in the storage unit in step (b) and the measurement data representing the acceleration in the front direction detected by the acceleration sensor in a second unit period different from the first unit period. Obtaining data (c);
    A step (d) for obtaining a respiratory cycle based on the difference data obtained in step (c);
    A method for measuring biological information.
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