JP2022101213A - Biological signal processing system, biological signal processing method, and program - Google Patents

Abstract

To provide a biological signal processing system, a biological signal processing method, and a program capable of more reliably and continuously measuring and acquiring biological information.SOLUTION: A biological processing system (1) comprises: a transmission unit (10) which transmits a radio wave to a living body of a measurement object person (R); and a reception unit (20) which can be disposed independently of the transmission unit (10) and receives a reflection wave that is the radio wave originated by the transmission unit (10) and reflected by the living body.SELECTED DRAWING: Figure 1

Description

The present invention relates to a biological signal processing system, a biological signal processing method and a program.

Conventionally, there is a system that continuously measures and monitors vital information (life sign information) such as breathing and pulse of the subject and biological information such as body movement such as turning over. These include those that are worn by the subject and measured directly, and those that irradiate radio waves from a remote position and measure remotely by the reflected waves. There is a problem that it takes time and effort to deal with the case of removal or failure.

On the other hand, even in the case of remote measurement, the measurement may not be performed properly depending on the posture of the subject and the position of the bed. Patent Document 1 discloses a system in which monitoring devices are provided at a plurality of places on the bed and measurement can be continued regardless of the position and posture of the subject in the bed.

International Publication No. 2017/130646

However, when radio waves are transmitted and received by a conventional measuring device attached to a bed, there is a problem that the incident angle of the radio waves to the target person becomes deep and it is difficult to obtain appropriate measurement results.

An object of the present invention is to provide a biometric signal processing system, a biometric signal processing method and a program capable of measuring and acquiring biometric information more reliably and continuously.

In order to solve the above problems, the invention according to claim 1 is
A transmitter that emits radio waves to living organisms,
A receiving unit that can be arranged independently of the transmitting unit and receives the reflected wave of the radio wave transmitted by the transmitting unit by the living body.
It is a biological signal processing system characterized by being provided with.

The invention according to claim 2 is the biological signal processing system according to claim 1.
The sharpness of the directivity of the radio wave transmitted by the transmitting unit and the sharpness of the directivity related to the reception of the radio wave of the receiving unit are characterized by being different from each other.

Further, the invention according to claim 3 is the biological signal processing system according to claim 2.
The directivity of the receiving unit for receiving radio waves is characterized by being sharper than the directivity of the radio waves transmitted by the transmitting unit.

The invention according to claim 4 is the biological signal processing system according to any one of claims 1 to 3.
It is characterized by including a signal processing unit that acquires a biological signal related to the state of the living body based on the radio wave signal received by the receiving unit.

The invention according to claim 5 is the biological signal processing system according to claim 4.
The biological condition is characterized by including vital sign information including at least one of respiration and pulse rate.

The invention according to claim 6 is the biological signal processing system according to claim 4 or 5.
The state of the living body is characterized by including information on the movement and rotation of the living body.

The invention according to claim 7 is the biological signal processing system according to any one of claims 1 to 6.
It is characterized by having a plurality of the receiving units.

The invention according to claim 8 is the biological signal processing system according to any one of claims 4 to 6.
It is equipped with a plurality of the receiving units.
The signal processing unit is characterized in that at least a part of the obtained biological signals is selected and analyzed based on the reception intensity in the frequency band to be acquired.

The invention according to claim 9 is the biological signal processing system according to any one of claims 4 to 6 and 8.
It is equipped with a plurality of the receiving units.
The signal processing unit obtains a cross-correlation between each combination of the plurality of obtained biological signals, and analyzes the data obtained by combining the plurality of biological signals with a combination of phase differences in which the cross-correlation satisfies the standard. It is characterized by doing.

The invention according to claim 10 is the biological signal processing system according to any one of claims 1 to 9.
It is characterized in that at least one of the directivity direction of the transmitted radio wave of the transmitting unit and the directivity direction of the received radio wave of the receiving unit can be adjusted.

The invention according to claim 11 is the biological signal processing system according to any one of claims 4 to 6 and 8.
At least one of the directivity direction of the transmitted radio wave of the transmitting unit and the directivity direction of the received radio wave of the receiving unit can be adjusted.
The signal processing unit is characterized in that the directivity direction is adjusted so as to increase the gain of the obtained biological signal.

The invention according to claim 12 is the biological signal processing system according to any one of claims 1 to 11.
The receiving unit is characterized in that it is located on the side opposite to the transmitting unit with the measurement surface of the living body interposed therebetween.

The invention according to claim 13 is the biological signal processing system according to any one of claims 1 to 12.
The receiving unit is characterized in that it is located in a direction of assumed reflection of radio waves transmitted from the transmitting unit by the living body.

Further, the invention according to claim 14 is
A biological signal processing system including a transmitting unit that transmits radio waves to a living body and a receiving unit that can be arranged independently of the transmitting unit and receives reflected waves of the radio waves transmitted by the transmitting unit by the living body. It is a biometric signal processing method of
It is characterized by including an acquisition step of acquiring a biological signal related to the state of the living body.

The invention according to claim 15 is the biological signal processing method according to claim 14.
The receiving unit is characterized in that it is located on the side opposite to the transmitting unit with the measurement surface of the living body interposed therebetween.

The invention according to claim 16 is the biological signal processing method according to claim 14 or 15.
The receiving unit is characterized in that it is located in a direction of assumed reflection of radio waves transmitted from the transmitting unit by the living body.

Further, the invention according to claim 17 is
Computer,
It can be arranged independently of the transmitting unit that emits radio waves to the living body, and based on the radio signal received by the receiving unit that receives the reflected wave of the radio waves transmitted by the transmitting unit, it is in the state of the living body. It is a program characterized by functioning as an acquisition means for acquiring the biological signal.

According to the present invention, there is an effect that biological information can be measured and acquired more reliably and continuously.

It is a figure explaining the biological signal processing system of this embodiment. It is a figure explaining the functional structure of a transmitting part and a receiving part. It is a figure explaining the processing structure of a signal processing unit. It is a figure which shows typically the time change of the measured value of the phase change amount obtained based on the received data of each receiving part. It is a flowchart of the respiratory information acquisition control process executed by the respiratory information acquisition unit. It is a figure which shows the functional structure of the receiving part of the modification. It is a schematic diagram when the change pattern of the I-phase signal and the Q-phase signal when there is no deviation amount is shown by the orthogonal IQ coordinate system. It is a figure which shows another example of arrangement of a transmitting part and a receiving part.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
FIG. 1 is a diagram illustrating the biological signal processing system 1 of the present embodiment. FIG. 1A is a view of the side surface viewed from the side of the long side, and FIG. 1B is a view viewed from above.

The biological signal processing system 1 includes a transmission unit 10, a reception unit 20, and a signal processing unit 30. The transmission unit 10 transmits a microwave (radio wave) having a frequency f0. The receiving unit 20 receives the microwave transmitted by the transmitting unit 10. The signal processing unit 30 includes a computer that processes the microwave received by the receiving unit 20 and acquires information (biological signal and its evaluation, etc.) related to the state of the living body based on the microwave (radio wave signal). Here, the information related to the state of the living body to be acquired is, for example, vital information (life sign information) such as the respiratory rate of the measurement target person R (patient, care recipient, etc.) lying on the bed B, and the chest. The respiratory cycle is specified by using the change in the propagation distance of the microwave according to the movement from the abdomen to the abdomen (up and down movement according to the change in circumference). Since microwaves pass through clothing and futons, the presence or absence of these has almost no effect on measurement.

The transmitting unit 10 and the receiving unit 20 have separate housings and can be independently arranged and attached to the bed B. Here, the transmitting unit 10 is located on the head side (headboard or frame) of the bed B, and the receiving unit 20 is located on the leg side (footboard or frame) of the bed B. The microwave is transmitted from the transmitting unit 10 to the living body with directivity from the chest to the abdomen of the living body, which is a measurement range and is a reflection surface of the microwave. When the transmitting unit 10 is attached to the bed B, the incident angle θ of the microwaves on the living body becomes large, and most of the mirror-reflected microwaves go toward the legs opposite to the incident head direction. The receiving unit 20 is located on the opposite side of the transmitting unit 10, that is, the microwave, with the assumed reflection position (measurement surface) of the measurement target person R (living body) in a plan view of the bed B and the measurement target person R from above. By being located on the side where the wave is reflected (assumed reflection direction), the microwave (reflected wave) reflected from the living body (especially near the measurement range) is efficiently received.

It should be noted that some deviations that may occur due to changes in the body shape of the measurement target R and the position of the head (pillow) may or may not be taken into consideration strictly in the assumed reflection direction. That is, the assumed reflection direction may be within an accuracy range that is determined based on the reference position when the measurement target person R having an average body shape is lying on his / her back. The received microwave is phase-modulated according to the movement of the living body due to the respiration of the living body (phase difference component φm (t). T means time, that is, the value of the phase difference component φm (t) is the reception time. It depends on the time).

Further, in the present embodiment, a plurality of, for example, three receiving units 20a, 20b, and 20c (collectively receiving units 20) are provided, and microwaves are received at different locations (three locations). The living body on the bed B may be off-center due to turning over. The microwave transmitted from the transmitting unit 10 can be received by at least one receiving unit 20 with sufficient intensity depending on the position of the living body.

The transmitting unit 10 and the receiving unit 20 are not limited to the case where they are attached to the bed B, but by attaching to the bed B, the positional relationship with the living body is easily maintained even if the bed B is moved. The transmitting unit 10 and the receiving unit 20 each have a battery, for example, a dry battery or a secondary battery (which may be a dedicated one), and can operate independently of each other. These may be attached at a position where they can be attached according to the fence (frame) of the bed B, and may have the same height or different heights.

The signal processing unit 30 is attached to, for example, any of the receiving units 20a to 20c. The biological signals received by the receiving units 20a to 20c may be sent to the signal processing unit 30 by wire or wireless communication. The signal processing unit 30 may receive power from a battery that operates the receiving unit 20 to which the signal processing unit 30 is attached, or may have a separate battery.

The directivity of the microwave transmitted from the transmission unit 10 may be loosely (widely) determined as shown by the dotted line in FIG. 1 (a). As described above, since the position of the living body can be moved with respect to the bed B, the microwave can be appropriately reached by the living body by taking a wide transmission directivity. On the other hand, the receiving unit 20 may be capable of determining the directivity of the microwave to be received sharper (narrower) than the directivity of the transmitting unit 10. As a result, it is possible to prevent the receiving unit 20 from directly receiving the microwave transmitted from the transmitting unit 10 or mixing (interference) between those reflected multiple times and those received by diffuse reflection at a plurality of places. can.

FIG. 2 is a diagram illustrating a functional configuration of the transmitting unit 10 and the receiving unit 20.
As shown in FIG. 2A, the transmission unit 10 includes an oscillation unit 11, an amplification unit 12, an antenna 13, and the like. The oscillating unit 11 generates a signal having a predetermined frequency f0 (microwave band, for example, 24 GHz), for example, a sine wave signal. The amplification unit 12 amplifies the signal input from the oscillation unit 11. The amplified signal is transmitted from the antenna 13 as a microwave.

The transmission unit 10 also has an operation reception unit (switch) that accepts an operation for switching whether or not to transmit microwaves, a control unit that controls the operation according to the operation content and the input voltage from the battery, and an operation status. It may have a display unit such as an LED lamp indicating. Further, when receiving operation control from an external device, it may be provided with a communication unit that communicates with the external device.

As shown in FIG. 2B, the receiving unit 20 includes an antenna 21, a demodulation unit 200, and the like. The demodulation unit 200 includes an amplification unit 22, an orthogonal demodulation unit 23, an analog / digital conversion unit (ADC 24), a detection unit 25, and the like. The orthogonal demodulation unit 23 includes a local oscillator 231, a 90-degree phase shifter 232, a mixer 233, 234, a low-pass filter (LPF235, 236), and the like.

The antenna 21 has a length, a shape, and the like that match the frequency f0 transmitted by the transmitting unit 10, and the transmitting unit 10 transmits and receives radio waves reflected by a living body.

The amplification unit 22 has an LNA (Low Noise Amplifier) that amplifies a signal (received signal) related to a radio wave received by the antenna 21 with low noise. The amplified signal is output to the orthogonal demodulation unit 23.

In the orthogonal demodulation unit 23, the local oscillator 231 generates a signal having the same frequency f0 as the microwave transmitted by the transmission unit 10. The 90 degree phase shifter 232 rotates (delays) the phase of the signal generated by the local oscillator 231 by 90 degrees. The mixer 233 synthesizes the received signal input from the amplification unit 22 and the signal of the local oscillator 231 and outputs a signal having two orthogonal components.

The LPF 235 and 236 extract the I-phase signal and the Q-phase signal by removing high-frequency components (at least about twice the frequency f0) from the signals of the two orthogonal components output from the mixer 233, respectively. The signal output from LPF235, 236 is output to ADC24.

It should be noted that a slight deviation amount df may actually occur between the oscillation frequency of the local oscillator 231 and the frequency f0 of the signal transmitted by the transmission unit 10. The main causes of the deviation are individual differences and temperature changes. When this deviation amount df is not zero, the I-phase signal and Q-phase signal extracted from LPF235 and 236 include not only the modulation component according to the movement of the living body but also the deviation amount df between the frequency f0 and the oscillation frequency. Contains ingredients according to. The individual difference that causes this deviation amount df does not fluctuate with time, and the temperature change is short because the time scale is sufficiently long compared to the cycle of the modulation component (respiratory or pulse cycle) in many cases. It can be regarded as almost constant within the time range.

The ADC 24 has a first ADC 241 and a second ADC 242. The I-phase signal output from the LPF235 is input to the first ADC 241 and digitized at a predetermined sampling frequency (sufficiently higher than the frequency corresponding to the respiratory cycle). The Q-phase signal output from the LPF236 is input to the second ADC 242 and digitized at the same sampling frequency as the first ADC 241.

The digital data (IQ signal data) of the I-phase signal and the Q-phase signal output from the ADC 24 is output to the signal processing unit 30.

The detection unit 25 detects whether the reception signal amplified by the amplification unit 22 contains the radio wave transmitted by the transmission unit 10 with an intensity equal to or higher than the reference value, and whether or not the orthogonal demodulation unit 23 and the ADC 24 operate according to the detection result. To switch and control. The detection unit 25 may be, for example, an integrator, etc., and when a radio wave having a reference intensity or higher is received within a predetermined time, the orthogonal demodulation unit 23 and the ADC 24 are started to operate, and the radio wave reception with the reference intensity is received for a predetermined time or longer. If the state in which the above is not performed continues, the operations of the orthogonal demodulation unit 23 and the ADC 24 are stopped. That is, when the radio wave to be demodulated is not received, the receiving unit 20 goes into a standby state without performing the operation after the demodulation, and reduces unnecessary power consumption.

In addition, instead of partially stopping the operation of the receiving unit 20 based on the strength of the amplified received signal, or in addition, the strength is specified based on the output data of the ADC 24, and a signal having a predetermined strength or higher is not acquired. In this case, the operation of the signal processing unit 30 may be stopped.

The receiving unit 20 also has an operation receiving unit (switch) that accepts a switching operation of whether or not to receive microwaves, a control unit that controls the operation according to the operation content and the input voltage from the battery, and an operating status. It may have a display unit such as an LED lamp indicating. Further, the receiving unit 20 may include a communication unit that communicates with the external device in order to output signal data to the signal processing unit 30 and acquire a command or the like from the external device. Further, a memory for temporarily storing the data output from the ADC 24 until it is transmitted to the signal processing unit 30 may be provided.

The signal processing unit 30 acquires the output signal from the ADC 24 of each receiving unit 20 and performs analysis processing. Here, the respiratory state analysis process such as the respiratory rate and the interval thereof is performed as described above.

FIG. 3 is a diagram illustrating a processing configuration of the signal processing unit 30.
The signal processing unit 30 includes a communication unit 39, a signal combining unit 31, an amplitude calculation unit 32, a phase calculation unit 33, an unwrap processing unit 34, a difference value calculation unit 35, a breathing information acquisition unit 36, and the like. Be prepared.

As described above, the microwave transmitted from the transmitting unit 10 is received by the plurality of receiving units 20, and is output as an IQ-separated digital discrete signal (IQ signal data). Since a plurality of IQ signal data (I1 to I3, Q1 to Q3) have a difference in the absolute value of the phase and amplitude depending on the difference in the reception path length and the reception strength of the signal, the plurality of IQ signal data received by the communication unit 39. The IQ signal data (I1 to I3, Q1 to Q3) of the above are input to the signal combine unit 31, and after adjusting the difference in phase and amplitude, they are added and combined. The adjustment amount is dynamically determined, for example, so that the amplitude intensity of the combined waveform is maximized. Alternatively, the adjustment amount may be determined in consideration of other factors such as the S / N ratio. Further, the signal combining unit 31 may acquire the calculation result of the difference value calculation unit 35 and the acquisition result of the respiratory information acquisition unit 36, and determine the adjustment amount in consideration of these.

For example, after excluding the received signal by the receiving unit 20 in which the received signal having a strength higher than the reference value is not obtained in the frequency band corresponding to the microwave to be received (that is, at least a part of the received signal based on the receiving strength). (If the intensity above the standard is obtained from all of them, all may be selected), and the remaining received signals are mutually correlated, and the amount of deviation that the correlation meets the predetermined standard ( The S / N ratio can be improved by combining (combining) a combination of (phase differences), for example, a deviation amount at which the largest correlation can be obtained as an adjustment amount (phase difference). Since the amount of change due to respiration differs depending on the path of the received signal of each receiving unit 20, that is, the reflection position on the body, the amount of phase shift may also differ. Therefore, the composite waveform is not simply the sum of the same amount of change, but qualitative improvement is expected.

The signal combine unit 31 has, for example, a CPU or the like, and may obtain the optimum timing by processing by executing a program, or has a hardware circuit having a specific logic circuit or the like, and the hardware circuit has the same. Processing data may be obtained by inputting.

The amplitude calculation unit 32 calculates the amplitude intensity A of the received signal from the IQ signal data that has been subjected to the combined wave processing. The amplitude intensity is obtained by the sum of squares of the I signal and the Q signal at each timing. The phase calculation unit 33 calculates the phase φ (t) of the modulation component (including the influence of the deviation amount df). Since the I-phase signal and the Q-phase signal are orthogonal to each other, the phase φ (t) is specified by the component ratio of the I-phase signal and the Q-phase signal. The phase φ (t) is for one cycle, for example, in the range of −π ≦ φ (t) <π.

The unwrap processing unit 34 connects the portions whose phases are apparently discontinuous due to the circuit of the above phase range. This process is for the difference value calculation unit 35 to appropriately obtain the difference value.

The difference value calculation unit 35 calculates the difference value of the phase φ (t) between the sampling data, that is, the phase change amount dφ at the sampling interval. Since the difference value is calculated based on the phase data unwrapped as described above, it is not affected by the discontinuity in the period spanning each period.

The respiration information acquisition unit 36 acquires the fluctuation of the phase change amount dφ obtained by the difference value calculation unit 35 as a fluctuation component according to respiration. The phase φ (t) is the sum of the phase difference component φm (t) and the component (2π · df) remaining in the mixer 233 and 234 due to the deviation amount df as described above, and corresponds to the latter deviation amount df. The ingredients can be considered constant in the short term. Therefore, the fluctuation of the phase change amount dφ can be regarded as the fluctuation dφm of the phase difference component φm (t). Since the phase difference component φm (t), that is, the movement of the living body occurs in the same cycle as the respiratory cycle (the movement of the living body here means a qualitative movement pattern, the completely same movement is repeated. Does not mean that), the period of fluctuation dφm and the respiratory cycle are equal. The respiration information acquisition unit 36 includes a processor such as a CPU 361 (Central Processing Unit) and a memory 362 such as a RAM (Random Access Memory). The CPU uses this fluctuation dφm to specify the respiratory rate per unit time (for example, per minute), the length of the respiratory cycle, the fluctuation range (maximum amplitude) for each respiratory cycle, and the like. Since the measured fluctuation range may change when the posture or position of the measurement target person R changes, it may be associated with the information on the posture or position, and if possible, depending on the posture or position. It may be corrected.

Further, the memory 362 may include a non-volatile memory such as a flash memory for storing a program 3621 related to acquisition control of breathing information and setting data.

Although it has been described here that the processing of the breathing information acquisition unit 36 is performed by the CPU and the other processing is performed by a dedicated hardware circuit, a separate CPU, or the like, each configuration other than the breathing information acquisition unit 36 has been described. A part or all of the processing operations of the above, particularly the entire operation of the signal processing unit 30, may be controlled and processed by a common CPU.

Information such as the specified respiratory rate and respiratory interval is output together with waveform data such as IQ signal data as needed. The output is performed, for example, by transmission to a terminal device that performs information processing (may be merely data transfer to a server device) via a communication unit or the like. The transmission may be performed in accordance with various wireless communication standards such as wireless LAN (Local Area Network) and Bluetooth (registered trademark).

Next, the identification of the respiratory rate will be described in more detail.

The respiratory rate may be obtained by simply specifying and counting the extreme value (maximum value or minimum value) of the fluctuation dφm within a unit time, or the time difference between the extreme values may be calculated and counted. The respiratory rate per unit time may be determined based on a representative value (for example, an average value). In addition, when using the representative value, an abnormal value that seems to be noise due to body movement, for example, fluctuates according to the respiratory cycle from the respiratory cycle within the latest predetermined period to the predetermined reference width (ratio to the respiratory cycle, etc.). You may exclude the measurement result when there is a deviation of more than or equal to, or when there is a decrease in reception intensity by more than the reference intensity and the reference time (reception omission, acquisition loss). In addition, if an abnormal value exists or there is an acquisition loss near the timing when the next extreme value is expected to be detected, judging from the respiratory cycle within the latest predetermined period, the extreme value is at that timing. Respiratory rate may be counted as if it had a value.

Further, when a temporary fluctuation far larger than the fluctuation due to respiration occurs in the plurality of receiving units 20a to 20c as noise, not only the phase but also the receiving intensity (amplitude) is generated between the receiving units 20a to 20c. The change of is also large. By also considering this pattern of amplitude change, body movements and turning over can be identified. By memorizing and setting these patterns in advance, the timing and frequency of body movements (movement of the living body) and turning over (rotation of the living body) and their frequency (collectively generated information) can be stored in parallel with the measurement of the respiratory rate. It may be measured and acquired.

Alternatively, the respiratory rate may be calculated again based on the representative value. For example, the average respiratory cycle may be calculated based on the time difference between the minimum timings, that is, the average value of the individual respiratory cycles, and the respiratory rate per unit time corresponding to the average respiratory cycle may be calculated. In addition, in order to exclude the influence of temporary noise due to body movement, etc., a predetermined number of the obtained individual respiratory cycles are deleted from the larger side and / or a predetermined number are deleted from the smaller side, and the rest. The average respiratory cycle may be determined based on.

Further, the periodicity of the change of the fluctuation component (that is, the fluctuation dφm) of the phase change amount dφ can be specified by the autocorrelation of the data of the phase change amount dφ obtained in time series. Based on the time difference τ that maximizes the autocorrelation coefficient, the average respiratory cycle in the most recent or autocorrelation coefficient calculation interval is specified. Further, as something similar to autocorrelation, for example, a measured value S (t) of timing t (the above-mentioned phase change amount dφ) and a measured value S (t + τ) of a timing (t + τ) deviated from this timing t by a time difference τ. The difference (norm) between them may be obtained as the direct deviation amount D (t, τ). The amount of deviation D (t, τ) may be the L1 norm (absolute value; D (t, τ) = | S (t) -S (t + τ) |, or the L2 norm, that is, the square of the difference. It may be of higher order such as D (t, τ) = (S (t) −S (t + τ)) ² .

The total deviation amount Z (τ) = Σ _{(0 ≦ t} ) obtained by adding this deviation amount D (t, τ) for each measurement timing t within a predetermined time k, which is about several times the general respiratory cycle. _{≦ k)} D (t, τ) becomes the minimum at the timing when the time difference τ is closest to the typical respiratory cycle.

Since the total deviation amount Z (τ) has a minimum value of “0” at τ = 0, it may be positive or negative inverted (may be multiplied by -1). Further, in order to make this a positive value, an appropriate offset value may be added. The function F = (1-z (τ)), which obtains a value obtained by inverting z (τ) obtained by normalizing the total deviation amount Z (τ) and further adding an offset value “1”, has a value of 0 or more and 1 It becomes the following, and the degree of agreement becomes the maximum at the maximum value. This function F is referred to as a Position Autocorrelation Function (hereinafter abbreviated as PACF) as an autocorrelation function related to the time change of the one-dimensional coordinates indicated by the measured value S (t).

Since the PACF value reflects the tendency of the entire measurement period, the influence of both the noise included as a whole and the noise superimposed on a part (burst noise, etc.) is reduced. On the other hand, if the periodicity of the measurement target such as respiratory rate is not uniform, the value of the function F may not increase and the result may be inaccurate if data for a measurement period that is too long compared to the period is input. be. Therefore, it suffices to determine the measurement period to be input by dividing the respiratory rate into cycles of the same to several cycles. The measurement period may be variable according to the latest measurement situation. In addition, the measurement time may be slid while overlapping part by part. If the unit time for calculating the respiratory rate is longer than the measurement period, the respiratory rates in multiple measurement times obtained within the latest unit time are added (if there is overlap, weighting is performed according to the degree of overlap). May).

By extending the PACF to a plurality of dimensions, it is possible to detect the periodicity while maintaining the relationship of the phase shift between the received signals of each receiving unit 20. Since the signals received by the plurality of receiving units 20a to 20c include fluctuations of the same cycle according to the breathing motion of a single living body, even if the signal amplitude and the amplitude of the phase shift amount are different, the signals have the same cycle. The waveform has a common variation. Therefore, N signal values for each time are treated as N-dimensional measured values S (each component is Si (1 ≦ i ≦ N)), and the time change (trajectory) of the measured values S in the N-dimensional coordinate space. ) Is specified by PACF, the respiratory cycle (the cycle of generation of biological information to be measured) can be obtained.

FIG. 4 is a diagram schematically showing the time change of the measured value of the phase change amount obtained based on the received data of each of the receiving units 20a to 20c.
The intensity and timing of the microwaves received by the receiving units 20a to 20c from the reflection position of the measurement target person R differ from each other depending on the positional relationship between the receiving units 20a to 20c and the transmitting unit 10 and the measurement target person R. The measured value S2 has a larger amplitude (reception intensity) than the measured value S1, and the timing is advanced by φL1. The measured value S3 has a smaller amplitude than the measured value S1, and the timing is delayed by φL2. Regardless of the amplitude or phase shift between these measured values S1 to S3, in PACF, the autocorrelation in which each received data is shifted by the time difference τ can be collectively obtained.

In this case, the calculation of the amplitude by the amplitude calculation unit 32 and the calculation of the difference value by the difference value calculation unit 35 may be executed for the received data by the plurality of reception units 20a to 20c, respectively.

The amount of deviation D (t, τ) between timings that differ by the time difference τ in the N-dimensional measured value S is D (t, τ) = Σ _{(1 ≦ i ≦ N)} in the L2 norm (square of the Euclidean distance) (1 ≦ i ≦ N). Si (t) -Si (t + τ)) ² ). Further, in the L1 norm (absolute value), D (t, τ) = Σ _{(1 ≦ i ≦ N)} | Si (t) −Si (t + τ) |). If the total deviation amount Z (τ) is obtained from the deviation amount D (t, τ) and the time difference τ at which this is the minimum is specified, a typical respiratory cycle can be obtained as in the one-dimensional case.

As a result, even if the S / N ratio of some of the measured values is low and sufficient accuracy cannot be obtained by themselves, noise is comprehensively reduced and the accuracy is improved by combining them. Here, the weighting coefficient may be multiplied by each measured value Si so as to weaken or appropriately adjust the magnitude relationship of the N components of the N-dimensional data. In addition, when the physical quantity related to the respiratory rate is measured by a method other than the respiratory rate measurement by receiving microwaves, the measured value obtained is different from the radio field intensity and the reference (measurement unit), so it is appropriate to optimize the weight. It may be multiplied by a factor. Alternatively, the weights may be set according to the validity of each signal, for example, the mixing rate of the abnormal waveform (noise) described above, the amplitude thereof, and the like.

An index indicating the reliability of the respiratory rate obtained by using PACF or the like may also be determined. For example, the index may be set so that the reliability is lowered according to the variation in the timing interval of the maximum value obtained in a plurality of predetermined time k (measurement period). Further, the index may be set so that the reliability decreases as the PACF value at the other time difference τ having the maximum value becomes smaller than the PACF value at τ = 0 (that is, 1). Also, the respiratory rate obtained (which may include those obtained during some of the measurement periods) deviates from the respiratory rate that humans should be able to obtain (eg, 4-50 breaths per minute). If there is such a case, or if the interval between the timings of each maximum value deviates from the interval corresponding to the respiratory rate (for example, 1.2 to 15.0 seconds), the reliability becomes the lowest level. The index may be set as such. The index is represented by a numerical value, for example, but may be graded by other things such as a symbol.

FIG. 5 is a flowchart showing a control procedure by the CPU (processor) of the respiratory information acquisition control process (acquisition means of the present embodiment) executed by the respiratory information acquisition unit 36. This process is repeatedly executed every time the measurement data (variation dφm) of the set measurement time is input from the difference value calculation unit 35.

When the respiratory information acquisition control process is started, the CPU 361 specifies the position and value of the extreme value (maximum or minimum) in the change of the variation dφm of the measurement time (step S101). For specific purposes, any of the above methods may be used. The CPU 361 sets the reliability according to the ratio of the magnitudes of the extreme values (when PACF is used, the ratio of the value of the function F at τ = 0 to the value of the function F at τ ≠ 0) (step). S102).

The CPU 361 specifies the number of occurrences of extreme values per measurement time and calculates the respiratory rate per unit time (step S103). When the unit time is longer than the measurement time, the CPU 361 may calculate the respiratory rate based on the number of extreme values in a plurality of measurement times within the latest unit time, or the unit time and the measurement time may be calculated. The respiratory rate may be obtained by multiplying the respiratory rate according to the ratio by the respiratory rate within the measurement time.

The CPU 361 calculates the interval between the extreme values as the breathing interval (step S104).

The CPU 361 determines whether or not the respiratory rate per unit time is an abnormal value (step S105). As described above, for example, 3 times or less or 51 times or more may be regarded as an outlier. If it is determined to be an abnormal value (“YES” in step S105), the CPU 361 sets the total reliability to the lowest level (step S110). Then, the process of the CPU 361 shifts to step S111.

If it is determined that the respiratory rate is not an abnormal value (“NO” in step S105), the CPU 361 determines whether or not there is an abnormal value in each calculated respiratory interval (step S106). The outlier is, for example, less than 1.2 seconds or longer than 15.0 seconds as described above. If it is determined that there is something abnormal (“YES” in step S106), the processing of the CPU 361 shifts to step S110. In addition, it is possible to determine that a factor that temporarily disturbs breathing, such as body movement or cough, is apparently occurring, and if this causes an abnormality in the breathing interval, that part is an exception (noise). It is not necessary to move to step S110. Alternatively, the number of times and the interval may be calculated by excluding that part. The CPU 361 may perform this exclusion process before step S101. Exclusion factors are not limited to coughing and body movements, but may include various temporary movements such as sneezing and yawning, and also include getting out of bed of the measurement subject R, and appropriately with the occurrence of these. Discrimination conditions such as situations where measurement is not possible may be set in advance. Further, the CPU 361 may identify and record these occurrences according to the agreement with the discrimination condition.

If it is determined that there is no abnormality (“NO” in step S106), the CPU 361 calculates the degree of variation in the breathing interval (step S107). The degree of variability may be simply dispersion or standard deviation, or the number (ratio) of breathing intervals that do not fall within the reference range from the average value may be counted. The CPU 361 sets the reliability according to the degree of variation (step S108).

The CPU 361 sets the total reliability based on the reliability set in step S102 and the reliability set in step S108 (step S109). The total reliability may be the lower of the two or the average value. Alternatively, the weighting may be set so as to give more importance to either one. Then, the process of the CPU 361 shifts to step S111.

When the process of step S109 or step S110 shifts to the process of step S111, the CPU 361 outputs the obtained data related to the respiration (step S111). Here, the output data may include at least the respiratory rate per unit time and the overall reliability. In addition, information related to the cause of the decrease in reliability may be included. Further, the original measurement data and the detection position (timing) of the specified extreme value may be associated and output. Then, the CPU 361 ends the respiratory information acquisition control process.

[Modification example]
FIG. 6 is a diagram showing a functional configuration of the receiving unit 20 of the modified example.
The receiving unit 20d includes a plurality of demodulation units 200a to 200d (three are shown here) and a directivity control unit 201. Each demodulation unit 200a to 200d is provided with antenna elements 21a to 21d. The antenna elements 21a to 21d form an array antenna, and are fixedly arranged side by side in a direction that changes the directivity direction of the radio wave received by the antenna 21. When the directivity direction is changed two-dimensionally, a plurality of antenna elements may be arranged in a matrix or concentric circles in the two-dimensional plane. That is, the receiving unit 20d can adjust the directivity direction related to microwave reception.

The demodulation units 200a to 200d have the same configuration as the demodulation unit 200 shown in the above embodiment. That is, the radio waves tuned to the antenna elements 21a to 21d are demodulated by the demodulation units 200a to 200d and input to the directivity control unit 201.

The directivity control unit 201 shifts and superimposes the IQ signals demodulated by the demodulation units 200a to 200d according to the time difference of the radio waves input to the antenna elements 21a to 21d from the set incident direction. By appropriately adjusting this time difference in a phased array or the like, the directivity direction of the array antenna can be set variably.

The directivity change operation may be performed sequentially or periodically. Alternatively, the directivity direction may be changed when the reception intensity changes by a predetermined reference fluctuation range or more. At the time of change, the direction in which the gain is most increased by receiving in all the directivity directions may be selected, or may be changed to the one having the larger gain and narrowed down.

The directivity control is not only dynamically performed by the directivity control unit 201 based on the reception strength or the like, but also the ideal direction is set and held in advance based on the positional relationship between the transmission unit 10 and the reception unit 20d. May be. It is possible to suppress the directivity to strongly receive the reflected wave at a position that is apparently strong and has nothing to do with fluctuations due to breathing or the like.

As described above, the biological signal processing system 1 of the present embodiment can be arranged independently of the transmitting unit 10 that transmits radio waves to the living body and the transmitting unit 10, and the radio waves transmitted by the transmitting unit 10 can be arranged independently. A receiving unit 20 for receiving a reflected wave from a living body is provided. In this way, since the receiving unit 20 can be arranged separately and independently with respect to the transmitting unit 10 at a position where the reflected wave can be easily received, the biological signal processing system 1 can more reliably and continuously arrange the living body. Information can be measured and acquired.

Further, the sharpness of the directivity of the radio wave transmitted by the transmitting unit 10 and the sharpness of the directivity related to the radio wave reception of the receiving unit 20 are different from each other. As a result, it is possible to reduce the reception intensity of noise and perform efficient reception while reducing the reception omission of the transmitted microwave.

Further, in particular, the directivity related to the radio wave reception of the receiving unit 20 may be sharper than the directivity of the radio wave transmitted from the transmitting unit 10. As a result, the receiving unit 20 suppresses reception from outside the required range, so that reception of noise and the like can be reduced.

Further, the biological signal processing system 1 includes a signal processing unit 30 that acquires a biological signal related to the state of the living body based on the radio wave signal received by the receiving unit 20. This makes it possible to appropriately obtain biometric information based on the signal demodulated from the received microwave.

In addition, the state of the living body includes vital information (life sign information) including at least one of respiration and pulse rate. With the biological signal processing system 1 of the present embodiment, it is possible to more appropriately and surely and stably acquire such contents essential for continuous monitoring of patients in hospitals and the like.

In addition, the state of the living body includes information on the occurrence of rotation such as movement and turning over of the living body. Physical movement is also important for patients who are lying down for a long period of time and care recipients, and it is easier to judge whether or not it is necessary to take measures by performing continuous measurement for a long period of time. Can be done.

Further, the biological signal processing system 1 may include a plurality of receiving units 20. When the measurement target person R moves due to turning over or the like, there may be a time zone in which an appropriate signal cannot be obtained only by fixing one receiving unit 20. By using the plurality of receiving units 20 side by side at different positions, it is possible to facilitate more continuous and stable acquisition of information related to the living body regardless of the movement of the measurement target person R.

Further, the signal processing unit 30 may select at least a part of the biological signals obtained by the plurality of receiving units 20 based on the reception intensity in the frequency band to be acquired and perform analysis processing. That is, when a plurality of receiving units 20 are arranged side by side and received in parallel, it is easy to receive microwaves in some parts and difficult to receive microwaves in other parts depending on the positional relationship between the transmitting unit 10 and the living body. Can occur. Therefore, by selecting and using the biological signal of the receiving unit 20 in which a part of the microwave is received with the required intensity, the S / N ratio can be improved and more accurate biological information can be acquired. can.

Further, the signal processing unit 30 obtains a cross-correlation between each combination of the biological signals obtained by the plurality of receiving units 20, and combines the plurality of biological signals with a combination of phase differences in which the cross-correlation satisfies the standard. Analysis processing may be performed on the collected data.
Since the distance from the reflection of the microwave transmitted from the transmitting unit 10 by the living body to the arrival at each receiving unit 20 is different from each other, the microwave modulated by the change according to the movement of the living body is generated by each receiving unit 20. The timing of reception is also different. Therefore, the modulated signal can be acquired more reliably by superimposing the signals on each other so as to reduce the timing deviation. The amount of this superposition shift is obtained by cross-correlation, and in the biometric signal processing system 1, the characteristic modulation pattern (phase change pattern) and the increase / decrease in reception intensity due to the change in the posture and position of the measurement target person R are obtained. It is possible to comprehensively evaluate the combination of the above and obtain a stable modulated signal.

Further, in the biological signal processing system 1 of the first modification, at least one of the directivity direction of the transmitted radio wave of the transmitting unit 10 and the directivity direction of the received radio wave of the receiving unit 20 can be adjusted. By receiving with sharp directivity as described above, it is possible to reduce the mixing of noise and the like. On the other hand, it is difficult to physically and finely adjust the direction of the antenna according to the mounting position of the receiving unit 20, and the directivity is deviated from the line connecting the transmitting unit 10, the reflecting position, and the receiving unit 20. It may not be possible to send and receive radio waves in / from the appropriate direction. Therefore, the biological signal processing system 1 can be adjusted and controlled in the directivity direction by an array antenna or the like, so that it can receive more stably and with an appropriate intensity. Further, since it is not necessary for the transmission unit 10 to transmit microwaves with an intensity higher than necessary, it is possible to suppress an increase in power consumption.

Further, the signal processing unit 30 may adjust the directivity direction of the transmitting unit 10 and / or the receiving unit 20 so as to increase the gain of the obtained biological signal. By dynamically adjusting the directivity direction by the signal processing unit 30, it is possible to search for an appropriate directivity direction and receive radio waves with good sensitivity without the user instructing the adjustment.

Further, in actual mounting / installation, the receiving unit 20 may be located on the opposite side of the transmitting unit 10 with the measurement surface of the living body sandwiched in a plan view. As mentioned above, especially in bed B, the incident angle of the microwave transmitted to the living body becomes large, and the reflected wave does not return to the transmitting side. The reflected wave of the microwave can be received more efficiently than the transmission intensity of the wave.

Further, the receiving unit 20 is located in the assumed reflection direction of the radio wave transmitted from the transmitting unit 10 by the living body. As a result, microwaves reflected by the living body can be efficiently received.

Further, the biological information processing method using the transmitting unit 10 of the present embodiment and the receiving unit 20 that can be arranged independently of the transmitting unit 10 relates to the state of the living body based on the radio signal received by the receiving unit 20. Includes an acquisition step to acquire a biological signal. As a result, the transmitting unit 10 and the receiving unit 20 can be arranged in a more preferable positional relationship in consideration of the reflection direction of the transmitting unit 10, so that the living body is more appropriately based on the signal demodulated from the received microwave. It becomes possible to obtain information.

Further, in particular, in this biometric information processing method, the receiving unit 20 is located on the opposite side of the measuring surface of the living body in a plan view from the transmitting unit 10, or the assumed reflection direction of the radio wave transmitted from the transmitting unit 10 by the living body. By being located at, it becomes possible to efficiently receive microwaves reflected by the living body.

Further, in the program 3621 of the present embodiment, the signal processing unit 30 (computer) can be arranged independently of the transmission unit 10 that transmits radio waves to the living body, and the signal processing unit 30 is based on the living body of the radio waves transmitted by the transmission unit 10. Based on the radio wave signal received by the receiving unit 20 that receives the reflected wave, it functions as an acquisition means for acquiring the biological signal related to the state of the living body. As described above, by including the software processing by the CPU 361 in the signal processing of the received microwave, it becomes possible to easily acquire the biological information by installing and executing the program 3621 in the general-purpose configuration. Further, since various control processes such as adjustment by the number and arrangement of the receiving units 20 and directivity control can be performed in an integrated manner, it is easy to extend to optional operations and control thereof.

The present invention is not limited to the above embodiment, and various modifications can be made.
For example, in the above embodiment, the transmitting unit 10 transmits low-directional microwave waves, and the plurality of (three) receiving units 20 receive each with high directivity, so that noise is mixed in on the receiving side. It is possible to receive in a wide range while suppressing it, but it is not limited to this. There may be one receiving unit 20. In this case, the transmitting unit 10 may transmit highly directional microwave waves according to the position of the receiving unit 20, and conversely, the receiving unit 20 lowers the directivity to transmit radio waves from the receiving unit 20 as much as possible. It may be possible to receive without omission. That is, by making the directivity different between the transmitting unit 10 and the receiving unit 20, it is possible to appropriately balance the suppression of the decrease in transmission / reception sensitivity and the suppression of noise reception. Further, at this time, the directivity direction of the transmission unit 10 may be adjustable. Alternatively, the directivity direction of the transmission unit 10 and the directivity direction of the reception unit 20 may be adjustable at the same time. On the other hand, the directivity of the transmitting unit 10 and the receiving unit 20 may be fixed to an appropriate degree of directivity, or the degree of directivity may be the same.

Further, in the above embodiment, the case of transmitting and receiving a microwave of 24 GHz has been described as an example, but the present invention is not limited to this. It may be a microwave or a millimeter wave in another wavelength band. In this case, it is preferable that the wavelength band is appropriately reflected by the human body and passes through a futon, clothing, or the like.

Further, in the above embodiment, the measurement of the respiratory rate has been described as an example, but the present invention is not limited to this. Examples of various biological information and vital information measured by changes in the living body include pulse rate (heart rate) and the like. That is, the measured periodic fluctuation may be pulsed. Since the frequency, time resolution, and amplitude intensity of the target change differ depending on the measurement target, the sampling interval, the strength of the transmitted radio wave, and the like may be determined according to these.

Further, in the above embodiment, the phase modulation according to the biological vibration at the time of reflection is measured, but other periodic fluctuations, for example, the frequency modulation accompanying the Doppler effect may be measured. ..

Further, when the data obtained by IQ separation into two components can be used independently for specifying the respiratory rate, they may be used separately. That is, the I-phase signal and the Q-phase signal may be input and used in parallel as each component of the two-dimensional measurement value in the PACF for one receiving unit 20. When the I-phase signal and the Q-phase signal can be used independently for each of the three receiving units 20a to 20c, the six-dimensional measured value S is obtained.

FIG. 7 is a schematic diagram showing the change patterns of the I-phase signal and the Q-phase signal when there is no deviation amount df in an orthogonal IQ coordinate system.
In this case, as shown in FIG. 7A, in the measurement of normal periodic fluctuation such as respiration, the angle p (phase φ) from the I-axis direction indicated by the IQ coordinate system has a large amplitude in a certain rotation angle range. It vibrates without change. The amplitude change depends not only on the magnitude of the fluctuation of the living body but also on the sharpness of the directivity of the receiver 20 and the like. Further, depending on the vibration range, either the I-phase signal or the Q-phase signal may vibrate twice in the respiratory cycle. Here, as shown in FIG. 7 (b), the Q-phase signal reaches a maximum at a position where the intensity of the I-phase signal becomes zero and decreases on both sides, so that a maximum occurs twice in the respiratory cycle. Therefore, if only the maximum number of times in the Q phase signal is simply counted, the respiratory cycle and the respiratory rate become inaccurate. However, by using both IQ signals, such inaccurate counting can be avoided.

Further, as the biosensor, in addition to the one by transmitting and receiving microwaves, another type of sensor may be used in combination. Data from a plurality of sensors may be collectively analyzed for identification of the respiratory rate and the like. For example, in the PACF, the dφ obtained from the received data by the receiving unit 20 (the number is not particularly limited) and the measurement data of the contact type sensor may be collectively treated as a four-dimensional value S.

Further, in the above embodiment, the transmission unit 10 is located on the head side and the reception unit 20 is located on the leg side, but the present invention is not limited to this.
FIG. 8 is a diagram showing another example of the arrangement of the transmitting unit 10 and the receiving unit 20.
As shown in FIG. 8A, the transmitting unit 10 and the receiving unit 20 may be attached to the left and right sides of the body of the measurement target person R. In this case as well, the receiving unit 20 may be located at a plurality of locations, such as near the head and near the legs, in addition to / instead of the positions symmetrical to the transmitting unit 10. Further, as shown in FIG. 8B, for a person who sleeps sideways, the transmitting unit 10 and the receiving unit 20 are attached to different height positions on the same side or separately on the head side and the leg side. It is also possible. Further, the receiving unit 20 may be located on both the side surface and the leg side with respect to the transmitting unit 10 on the head side. Further, when one receiving unit 20 is used, the receiving unit 20 may be easily movable along a rail or the like. Further, the movement is performed electrically, and the movement is automatically controlled by the signal processing unit 30 or another control unit that has received the received information from the signal processing unit 30 according to the microwave reception state or the like. May be good.

Further, in the above embodiment, the measurement of the measurement target person R lying on the bed has been described, but when the patient is in a state to some extent or when he / she is continuously sitting on a reclining seat or the like, etc. , It is also possible to measure in various other postures. In any case, it is particularly effective when the incident angle is large.

Further, the signal processing unit 30 does not have to be attached to the receiving unit 20, and may be independently located at a place where communication with the receiving unit 20 is possible. Further, the signal processing unit 30 may be integrated with a monitor device that displays a measurement result and detects and notifies an abnormal state. Alternatively, when there is only one receiving unit 20, the receiving unit 20 and the signal processing unit 30 may be integrated. Further, even if the number is not one, the receiving unit 20 and the signal processing unit 30 may be a combination of a constant master unit and a slave unit having only the receiving unit 20.

Further, in the above description, a memory 362 composed of a flash memory or the like is described as an example as a computer-readable medium for storing the program 3621 related to the biometric information (breathing information) acquisition control of the present invention, but the description is limited thereto. Not done. As other computer-readable media, (hard disks (HDD), other non-volatile memories such as MRAM, and portable recording media such as CD-ROMs and DVD discs can be applied to the present invention. A carrier wave (carrier) is also applied to the present invention as a medium for providing the data of the program via a communication line.
In addition, the specific configuration, the content and procedure of the processing operation shown in the above embodiment can be appropriately changed without departing from the spirit of the present invention. The scope of the present invention includes the scope of the invention described in the claims and the equivalent scope thereof.

1 Biometric signal processing system 10 Transmitter 11 Oscillator 12 Amplifier 13 Antenna 20, 20a to 20d Receiver 200, 200a to 200d Demodulation unit 201 Directional control unit 21 Antenna 21a to 21d Antenna element 22 Amplification unit 23 Orthogonal demodulation unit 231 Local oscillator 232 90 degree phase shifter 233, 234 mixer 235, 236 LPF
24 ADC
241 1st ADC
242 2nd ADC
25 Detection unit 30 Signal processing unit 31 Signal combining unit 32 Amplitude calculation unit 33 Phase calculation unit 34 Unwrap processing unit 35 Difference value calculation unit 36 Respiration information acquisition unit 361 CPU
362 Memory 3621 Program 39 Communication unit B Bed R Measurement target person dφ Phase change amount dφm Fluctuation f0 Frequency df Deviation amount τ Time difference φm Phase difference component

Claims (17)

A transmitter that emits radio waves to living organisms,
A receiving unit that can be arranged independently of the transmitting unit and receives the reflected wave of the radio wave transmitted by the transmitting unit by the living body.
A biological signal processing system characterized by being equipped with. The biometric signal processing system according to claim 1, wherein the sharpness of the directivity of the radio wave transmitted by the transmitting unit and the sharpness of the directivity related to the reception of the radio wave of the receiving unit are different from each other. The biometric signal processing system according to claim 2, wherein the directivity related to radio wave reception of the receiving unit is sharper than the directivity of the radio wave transmitted by the transmitting unit. The biomedical signal processing system according to any one of claims 1 to 3, further comprising a signal processing unit that acquires a biological signal related to the state of the living body based on the radio wave signal received by the receiving unit. The biological signal processing system according to claim 4, wherein the biological condition includes vital sign information including at least one of respiration and pulse rate. The biological signal processing system according to claim 4 or 5, wherein the state of the living body includes information on the movement and rotation of the living body. The biological signal processing system according to any one of claims 1 to 6, further comprising a plurality of receiving units. It is equipped with a plurality of the receiving units.
One of claims 4 to 6, wherein the signal processing unit selects at least a part of the obtained biological signals based on the reception intensity in the frequency band to be acquired and performs analysis processing. The biological signal processing system described in the section. It is equipped with a plurality of the receiving units.
The signal processing unit obtains a cross-correlation between each combination of the plurality of obtained biological signals, and analyzes the data obtained by combining the plurality of biological signals with a combination of phase differences in which the cross-correlation satisfies the standard. The biological signal processing system according to any one of claims 4 to 6 and 8. The biometric signal processing system according to any one of claims 1 to 9, wherein at least one of the directivity direction of the transmitted radio wave of the transmitting unit and the directivity direction of the received radio wave of the receiving unit can be adjusted. .. At least one of the directivity direction of the transmitted radio wave of the transmitting unit and the directivity direction of the received radio wave of the receiving unit can be adjusted.
The biological signal processing system according to any one of claims 4 to 6, 8, wherein the signal processing unit adjusts the pointing direction so as to increase the gain of the obtained biological signal. The biometric signal processing system according to any one of claims 1 to 11, wherein the receiving unit is located on the side opposite to the transmitting unit with the measurement surface of the living body interposed therebetween. The biometric signal processing system according to any one of claims 1 to 12, wherein the receiving unit is located in a direction of assumed reflection of radio waves transmitted from the transmitting unit by the living body. A biological signal processing system including a transmitting unit that transmits radio waves to a living body and a receiving unit that can be arranged independently of the transmitting unit and receives reflected waves of the radio waves transmitted by the transmitting unit by the living body. It is a biometric signal processing method of
A biological signal processing method comprising an acquisition step of acquiring a biological signal relating to a biological state. The biological signal processing method according to claim 14, wherein the receiving unit is located on the side opposite to the transmitting unit with the measurement surface of the living body interposed therebetween. The biological signal processing method according to claim 14, wherein the receiving unit is located in a direction of assumed reflection of radio waves transmitted from the transmitting unit by the living body. Computer,
It can be arranged independently of the transmitting unit that emits radio waves to the living body, and based on the radio signal received by the receiving unit that receives the reflected wave of the radio waves transmitted by the transmitting unit, it is in the state of the living body. A program characterized by functioning as an acquisition means for acquiring the biological signal.

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