JP2019088455A - Monitoring device - Google Patents

Abstract

To provide a monitoring device that allows an activity state of a subject to be grasped by monitoring information on a body motion of the subject.SOLUTION: A monitoring device for monitoring a subject includes a reception unit for receiving a reflection wave of a micro-wave irradiated onto the subject, a monitoring unit for monitoring a behavior of the subject based on a body motion signal on a body motion of the subject extracted from a signal of the reflection wave, and an output control unit for outputting activity information based on the behavior of the subject monitored by the monitoring unit. The activity information includes an amplitude of the body motion signal, and at least one of the number of body motions in a predetermined period in a low frequency area and the number of body motions in the predetermined period in a high frequency area.SELECTED DRAWING: Figure 7

Description

  The present disclosure relates to a monitoring device for monitoring a subject.

  In recent years, with the progress of the aging society, the number of households with only elderly people living alone or elderly couples is increasing. In addition, due to depopulation and so on, it can not be expected to be watched by nearby people, and there is a limit to the support by carers who support their lives, so it is often difficult to confirm the safety of elderly people and single living people. . Therefore, delays in dealing with unforeseen situations frequently occur. Therefore, there is known a system for monitoring a subject using a microwave Doppler sensor in order to prevent such occurrence of a situation.

  For example, Japanese Patent Application Laid-Open No. 2012-75861 (Patent Document 1) discloses a safety monitoring device that collects biological information of a subject and monitors the safety of the subject. The safety monitoring device irradiates the subject with microwaves and detects body motion and respiration of the subject from the Doppler-shifted reflected wave, and the subject motion and respiration rate within a predetermined time are tested. Monitor the safety of persons

JP, 2012-75861, A

  In the technology according to Patent Document 1, the body movement number and the respiration rate are calculated using the microwave Doppler shift signal output by the microwave Doppler sensor, and the safety of the subject is monitored using the safety pattern that is a combination of these. Do. For example, the safety points are set according to the safety pattern, the safety level is determined according to the total of the daily safety points, and the notification corresponding to the safety level is performed. However, for example, in the daily life, it is not possible to grasp the activity state, such as whether the subject frequently moved and was active.

  An object of the present disclosure is, in one aspect, to provide a monitoring device capable of grasping an activity state of a subject by monitoring information on body motion of the subject.

  According to an embodiment, a monitoring device is provided for monitoring a subject. The monitoring device receives the reflected wave of the microwave irradiated to the subject, and the body movement signal related to the body movement of the subject extracted from the signal of the reflected wave. A monitoring unit that monitors the operation, and an output control unit that outputs activity information based on the operation of the subject monitored by the monitoring unit. The activity information includes at least one of an amplitude of a body movement signal, a body movement number within a predetermined period in a low frequency region, and a body movement number within the predetermined period in a high frequency region.

  According to the present disclosure, it is possible to grasp the activity state of the subject by monitoring information on the motion of the subject.

FIG. 1 shows an overall configuration of a monitoring system according to a first embodiment. 5 is a plan view showing a configuration of a planar antenna in the monitoring device according to Embodiment 1. FIG. FIG. 7 is a diagram showing the directivity characteristic of the planar antenna according to the first embodiment. FIG. 5 is a diagram for illustrating an installation method of the monitoring device according to the first embodiment. FIG. 5 is a diagram for illustrating an installation method of the monitoring device according to the first embodiment. FIG. 13 is a diagram for describing a modification of the installation method of the monitoring device according to the first embodiment. FIG. 5 is a block diagram for illustrating a detailed configuration of a control circuit according to the first embodiment. FIG. 5 is a block diagram for illustrating a detailed configuration of an analog signal processing circuit according to the first embodiment. FIG. 7 is a diagram showing an example of an IQ plane of a reflected wave according to the first embodiment. It is a figure which shows the time change of approach operation | movement, separation operation | movement, and body movement amplitude according to Embodiment 1. FIG. It is a figure which shows the relationship between the distance of a monitoring apparatus and a test subject, and a body movement amplitude. FIG. 7 is a diagram showing an example of a breathing area calculation process of the monitoring device according to the first embodiment. FIG. 7 is a diagram showing an example of a heart rate area calculation process of the monitoring device according to the first embodiment. FIG. 7 is a diagram showing an example of body movement calculation processing by the monitoring device according to the first embodiment. It is a figure for demonstrating the installation system of the monitoring apparatus according to an Example. It is a figure which shows the measurement result of activity information. It is a figure which shows the measurement result of activity information. FIG. 7 is a diagram showing an output example of activity information according to the first embodiment. FIG. 17 is a diagram for illustrating an installation method of a monitoring device according to a second embodiment. FIG. 16 is a diagram for illustrating an installation method of a monitoring device according to a third embodiment.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. In the following description, the same components are denoted by the same reference numerals. Their names and functions are also the same. Therefore, detailed description about them will not be repeated.

First Embodiment
<Whole system configuration>
FIG. 1 is a diagram showing an entire configuration of a monitoring system 1000 according to the first embodiment. Referring to FIG. 1, monitoring system 1000 includes a monitoring device 100 for monitoring a subject, and a terminal device 200. The terminal device 200 is a terminal on the side of watching a subject who is a monitoring (watching) target person, and is, for example, a smartphone. However, the terminal device 200 may be another device such as a foldable mobile phone, a tablet terminal device, a personal computer (PC) or the like.

  A network 55 for connecting the monitoring apparatus 100 and the terminal device 200 to each other includes various networks such as the Internet and a mobile terminal communication network. The network 55 is not limited to this, and a wired communication method may be adopted, or another wireless communication method such as a wireless LAN (local area network) may be adopted.

  The monitoring device 100 includes, as main components, a control circuit 152, a memory 154, a speaker 156, a communication interface 158, and a microwave Doppler sensor 160. The monitoring apparatus 100 may include a display for displaying various information, and an input device such as a button for receiving various inputs from the user.

  The control circuit 152 typically includes a microprocessor including a CPU and the like, an analog signal processing circuit that processes an analog signal from the microwave Doppler sensor 160, and an AD converter. The detailed configuration of the control circuit 152 will be described later. The microprocessor functions as a control unit that controls the operation of each unit of the monitoring apparatus 100 by reading and executing the program stored in the memory 154. For example, the microprocessor implements the processing of the control circuit 152 described later by executing the program.

  The memory 154 is realized by a random access memory (RAM), a read-only memory (ROM), or the like. The memory 154 stores programs executed by the microprocessor or data used by the microprocessor.

  The speaker 156 converts an audio signal supplied from the microprocessor into audio and outputs the audio to the outside of the monitoring apparatus 100. The communication interface 158 encodes communication data from the microprocessor and converts it into a communication signal, and transmits the communication signal to the terminal device 200. Also, it decodes the signal received from the terminal device 200, converts it into communication data, and outputs it to the microprocessor. The communication method may be a wireless communication method using a wireless LAN or the like, or may be a wired communication method using USB (Universal Serial Bus) or the like.

  The microwave Doppler sensor 160 emits microwaves to the subject, and outputs a signal reflecting the movement of the body of the subject to the control circuit 152 from the reflected microwaves. Further, the microwave Doppler sensor 160 generates I channel signal and Q channel signal orthogonal to each other from the input reflected wave (reflection signal).

  Specifically, the microwave Doppler sensor 160 includes an oscillating circuit 21, amplifiers 22A and 22B, a transmitting antenna 25, a receiving antenna 30, mixers 32I and 32Q, and low pass filters (LPFs) 33I and 33Q and 90. And a phase shifter 38. The transmitting antenna 25 and the receiving antenna 30 are configured by planar antennas. The transmitting antenna 25 and the receiving antenna 30 may be configured by a waveguide antenna or a dielectric antenna.

  The microwave sine wave signal output from the oscillation circuit 21 is amplified by the amplifier 22A and emitted from the transmission antenna 25. The microwave Mt radiated into the space is reflected by the body surface (for example, the chest) of the subject who is the object. A Doppler shift corresponding to the movement (body movement) of the subject's body (respiratory movement) and the breathing movement and the heart movement is generated in the reflected microwave Mr of the radiated microwave. Therefore, the signal (reflected signal) of the reflected wave Mr input to the receiving antenna 30 is a signal corresponding to the body movement, the breathing operation and the heartbeat operation of the subject.

  The reflected signal received by the receiving antenna 30 is amplified by the amplifier 22B. The amplified signal Dr is input to the mixer 32I on the I channel side and the mixer 32Q on the Q channel side. Here, the signal Dr input to the I channel side is referred to as “Dri” for convenience, and the signal Dr input to the Q channel side is referred to as “Drq” for convenience.

  The signal Dt amplified by the amplifier 22A is input to the mixer 32I on the I channel side and the mixer 32Q via the 90-degree phase shifter 38. Here, the signal Dt input to the I channel side is referred to as “Dti” for convenience, and the signal Dt input to the Q channel side is referred to as “Dtq” for convenience. Although the present embodiment describes a configuration in which the phase of the signal Dtq with respect to the signal Dti is shifted by 90 degrees by using the 90-degree phase shifter 38, the present invention is not limited to this configuration. For example, by using a 90-degree phase shifter 38 on the input side of the mixer 32Q, the phase of the signal Drq relative to the signal Dri may be shifted by 90 degrees.

  The signal frequency-converted (down-converted) by the mixer 32I is input to the LPF 33I. The LPF 33I outputs a signal obtained by removing a relatively high frequency component from the signal to the control circuit 152 as a baseband signal Dbi on the I channel side. The signal frequency-converted by the mixer 32Q is input to the LPF 33Q. The LPF 33Q outputs a signal obtained by removing a relatively high frequency component from the signal as a baseband signal Dbq on the Q channel side to the control circuit 152. The baseband signals Dbi and Dbq are respectively output as microwave Doppler shift signals that have been Doppler-shifted by body movement of the subject.

  The velocity and amplitude of the reflected signal input to the receiving antenna 30 change with time. Therefore, although the signal on the I channel side and the signal on the Q channel side are instantaneously 90 degrees out of phase, depending on the speed and direction of the signal, the phase lead of the baseband signal Dbq relative to the baseband signal Dbi One is not constant but always changes with time.

  FIG. 2 is a plan view showing a configuration of a planar antenna in monitoring apparatus 100 according to the first embodiment. FIG. 3 is a diagram showing directivity characteristics of the planar antenna according to the first embodiment. Specifically, FIG. 3 (a) is a diagram showing directivity characteristics (pattern) in azimuth (horizontal) direction, and FIG. 3 (b) is a diagram showing directivity patterns in elevation (vertical) direction. is there.

  Referring to FIG. 2, the planar antenna in monitoring apparatus 100 includes a transmitting antenna 25 and a receiving antenna 30. Each of the transmitting antenna 25 and the receiving antenna 30 has eight antenna elements.

  Referring to FIG. 3, the directivity pattern of the planar antenna has a main lobe and two side lobes in each of azimuth and elevation directions. For example, the 3 dB beam width (half width) of the main lobe in the azimuth direction is ± 20 degrees, and the half width of the main lobe in the elevation direction is ± 15 degrees.

<Installation method of monitoring device>
The installation method of the monitoring apparatus 100 which monitors a subject is demonstrated. Although the following describes the configuration in which the bedding is a bed, the present invention is not limited to this, and the bedding may be a futon or the like.

  FIG. 4 is a diagram for illustrating an installation method of monitoring apparatus 100 according to the first embodiment. Specifically, FIG. 4A is a schematic view (plan view) when the subject on the bed is viewed from the ceiling side of the room. FIG.4 (b) is the schematic (side view) at the time of seeing the test subject on a bed from the side of a room.

  Referring to FIG. 4, monitoring device 100 is installed around entrance portion 203 of room 201. The inlet 203 is, for example, a door or a sliding door. The area of the room 201 is, for example, up to 16 tatami (for example, 3.8 m × 7.6 m) in size. In the room 201, a light 206, a storage stand 205, and a television 210 are provided.

  The peak direction of the main lobe of the planar antenna (the transmitting antenna 25 and the receiving antenna 30) of the monitoring apparatus 100 is horizontal. The direction of the monitoring apparatus 100 is set such that the peak direction line 121 (virtual line) of the main lobe is along the main flow line of the subject. The monitoring apparatus 100 is installed on the peak direction line 121 at such a height that the torso portion exists when the subject is in the standing posture. For example, the monitoring device 100 is horizontally installed near the height H (for example, 60 cm to 150 cm) from the floor. As a result, radio waves are hit and reflected perpendicularly to the subject in the standing posture, so that the reflection cross-sectional area for the reflected signal becomes constant, and the detection accuracy becomes high. In the case where the subject is lying (bed) in the bed 300, the subject is not present on the peak direction line 121 (see FIG. 4B).

  Further, the monitoring device 100 is installed so that two area lines 123A indicating the spread of the half width of the main lobe in the azimuth direction become the range shown in FIG. 4A. Thereby, the monitoring apparatus 100 can set the inside of the horizontal plane of the room 201 as a detection target. Further, the monitoring device 100 is installed such that two area lines 123B indicating the spread of the half width of the main lobe in the elevation direction are in the range shown in FIG. 4 (b). Thus, the vertical plane of the room 201 can be detected.

  Referring to FIG. 4, the vicinity of the monitoring device 100 is out of the range of the area defined by the area lines 123A and 123B. However, since the directivity pattern of the planar antenna has two side lobes in each of the azimuth and elevation directions, human detection is possible.

  FIG. 5 is a diagram for illustrating an installation method of monitoring apparatus 100 according to the first embodiment. Specifically, FIG. 5A is a schematic view (plan view) when the subject in the standing posture is viewed from the ceiling side of the room. FIG. 5 (b) is a schematic view (side view) when the subject in the standing posture is viewed from the side of the room.

  Although details will be described later, the monitoring apparatus 100 uses the I channel signal and the Q channel signal of the reflected wave Mr to determine whether the subject is approaching or away from the monitoring apparatus 100 at predetermined intervals. It is configured to be detectable.

  In the example of FIG. 5, a case where the subject leaves the bed 300 and tries to go out of the room 201 from the entrance 203 is shown. The subject proceeds in the direction of the arrow 209 along the peak direction line 121 of the main lobe irradiated from the monitoring device 100 and approaches the monitoring device 100. In this case, the operation is such as traversing the area lines 123A and 123B, and the monitoring apparatus 100 detects an operation (hereinafter, also referred to as “approaching operation”) in which the subject approaches the apparatus itself. On the other hand, when the subject moves in the direction opposite to the arrow 209 (in the direction from the entrance portion 203 to the bed 300), the monitoring apparatus 100 detects an operation (i.e., separation operation) in which the subject moves away from the own apparatus. Do.

  In the examples of FIGS. 4 and 5, although the monitoring device 100 has been described as to be provided so that the peak direction line 121 is horizontal to the floor portion, the present invention is not limited to this configuration, and is provided as shown in FIG. May be

  FIG. 6 is a diagram for describing a modification of the installation method of monitoring apparatus 100 according to the first embodiment. With reference to FIG. 6, the monitoring apparatus 100 is installed on the bed 300 side (that is, the floor side) at an angle θa in the elevation direction (see FIG. 6A), and the bed 300 in the azimuth direction. It is installed on the side (i.e., the side of the subject) at an angle θb (see FIG. 6B). In this case, even if the subject is lying on the bed 300, the subject is present on the peak direction line 121. As a result, the subject lying around the bed 300 and the bed 300 can be detected by the area lines 123A and 123B. As described above, the installation method of the monitoring apparatus 100 may be changed as appropriate according to the arrangement of the inlet 203, the position of the bed 300, the height, and the like.

<Configuration of control circuit>
FIG. 7 is a block diagram for illustrating the detailed configuration of the control circuit according to the first embodiment. Referring to FIG. 7, control circuit 152 includes an analog signal processing circuit 41, an AD converter 43, and a microprocessor 45. The microprocessor 45 is typically a digital signal processor (DSP) specialized for digital signal processing, or a microcontroller unit (MCU). The AD converter 43 may use an AD conversion function in the microprocessor 45.

  The analog signal processing circuit 41 removes unnecessary frequency band components of the signal input from the microwave Doppler sensor 160, and outputs the component to the AD converter 43. Specifically, the analog signal processing circuit 41 outputs the analog signal Shi of the I channel and the analog signal Shq of the Q channel in the frequency band including the band of the heartbeat component (for example, 0.7 Hz to 20 Hz), and the body movement component The analog signal Sti of the I channel and the analog signal Stq of the Q channel are output. The bands of body motion components also include bands of respiratory components.

  FIG. 8 is a block diagram for describing a detailed configuration of analog signal processing circuit 41 according to the first embodiment. Referring to FIG. 8, analog signal processing circuit 41 receives baseband signal Dbi on the I channel side output from microwave Doppler sensor 160 and baseband signal Dbq on the Q channel side output from microwave Doppler sensor 160. Accept the input with. The baseband signal Dbi is distributed to the analog signals Dbia and Dbib. The baseband signal Dbq is distributed to the analog signals Dbqa and Dbqb.

  The analog signal processing circuit 41 includes signal processing circuits 149A to 149D. The analog signal Dbia is output to the signal processing circuit 149A for heart rate measurement. The signal processing circuit 149A includes an HPF 143A which is a high pass filter, an LPF 144A which is a low pass filter, and an amplifier 145A.

  The HPF 143A removes low frequency components of the analog signal Dbia. As an example, the HPF 143A removes signal components of 0.7 Hz or less. The signal after removal is output to the LPF 144A. The LPF 144A removes high frequency components of the analog signal Dbia output from the HPF 143A. As one example, the LPF 144A removes signal components of 200 Hz or more. The signal after removal is output to the amplifier 145A. The amplifier 145A amplifies the analog signal Dbia output from the LPF 144A by a predetermined factor (for example, 400) to generate an analog signal Shi. The analog signal Shi is output to the AD converter 43 (see FIG. 7).

  The analog signal Dbib is output to the signal processing circuit 149B for measuring respiration. The signal processing circuit 149B includes an HPF 143B, an LPF 144B, and an amplifier 145B.

  The HPF 143B removes low frequency components of the analog signal Dbib. As an example, the HPF 143B removes signal components of 0.1 Hz or less. The signal after removal is output to the LPF 144B. The LPF 144B removes high frequency components of the analog signal Dbib output from the HPF 143B. As an example, the LPF 144B removes signal components of 200 Hz or more. The signal after removal is output to the amplifier 145B. The amplifier 145B amplifies the analog signal Dbib output from the LPF 144B by a predetermined factor (for example, 100 times) to generate an analog signal Sti. The analog signal Sti is output to the AD converter 43 (see FIG. 7).

  Since the amplitude of the heartbeat signal is about 1/10 or less of the amplitude of the respiration signal, the amplification factor of the amplifier 145A for heartbeat measurement is larger than the amplification factor of the amplifier 145B for respiration measurement. 145A, 145B are designed. As an example, the amplification factor of the amplifier 145A is 400 times, and the amplification factor of the amplifier 145B is 100 times.

  The analog signal Dbqa is output to the signal processing circuit 149C for heart rate measurement. The signal processing circuit 149C includes an HPF 143C, an LPF 144C, and an amplifier 145C.

  The HPF 143C removes low frequency components of the analog signal Dbqa. As an example, the HPF 143C removes signal components of 0.7 Hz or less. The signal after removal is output to the LPF 144C. The LPF 144C removes high frequency components of the analog signal Dbqa output from the HPF 143C. As an example, the LPF 144C removes signal components of 200 Hz or more. The signal after removal is output to the amplifier 145C. The amplifier 145C amplifies the analog signal Dbqa output from the LPF 144C by a predetermined multiple (for example, 400) to generate an analog signal Shq. The analog signal Shq is output to the AD converter 43 (see FIG. 7).

  The analog signal Dbqb is output to the signal processing circuit 149D for measuring respiration. The signal processing circuit 149D includes an HPF 143D, an LPF 144D, and an amplifier 145D.

  The HPF 143D removes low frequency components of the analog signal Dbqb. As an example, HPF143D removes the signal component below 0.1 Hz. The signal after removal is output to the LPF 144D. The LPF 144D removes high frequency components of the analog signal Dbqb output from the HPF 143D. As an example, the LPF 144D removes signal components of 200 Hz or more. The signal after removal is output to the amplifier 145D. The amplifier 145D amplifies the analog signal Dbqb output from the LPF 144D by a predetermined multiple (for example, 100) to generate an analog signal Stq. The analog signal Stq is output to the AD converter 43 (see FIG. 7).

  In the above, the LPF 144A, the LPF 144B, the LPF 144C, and the LPF 144D use a low pass filter that passes less than 200 Hz, but may be a low pass filter that passes a frequency less than 1⁄2 of the sampling frequency. For example, in the present embodiment, although 400 Hz is used as the sampling frequency according to the performance of the microprocessor 45, for example, high-speed sampling of about 1 kHz may be used. In this case, movement of the body or fast movement when walking can be detected as movement of body movement.

  Since the amplitude of the heartbeat signal is about 1/10 or less compared to the amplitude of the respiration signal, the amplification factor of the amplifier 145C for heartbeat measurement is larger than the amplification factor of the amplifier 145D for respiration measurement. The amplifiers 145C and 145D are designed. As an example, the amplification factor of the amplifier 145C is 400 times, and the amplification factor of the amplifier 145D is 100 times.

  The HPFs 143A to 143D and the LPFs 144A to 144D are, for example, active filters using operational amplifiers. Alternatively, the HPFs 143A to 143D may be passive elements using coils, capacitors, and resistors.

  As described above, by performing band limitation and amplification independently for heart rate measurement and for body movement measurement (including respiration measurement), the SN (Signal Noise) ratio is high between the heart rate area and the respiration area. Good quality analog signals are extracted. The LPFs 144A to 144D also function as anti-aliasing filters for the AD converter 43.

  Again, referring to FIG. 7, the AD converter 43 AD converts the input signal into 16 bits (or 12 bits). Specifically, the AD converter 43 receives the input of the analog signals Shi, Shq, Sti, and Stq, and converts the analog signals Shi, Shq, Sti, and Stq into digital signals at a predetermined sampling rate (for example, 10 msec). To the microprocessor 45. The digital signals Shi, Shq, Sti, and Stq are appropriately offset-adjusted as ± signals according to the voltage amplitude.

  The microprocessor 45 executes various processes using the digital signals Shi, Shq, Sti and Stq. Specifically, the microprocessor 45 includes, as main functional components, an output control unit 54, a heartbeat calculation unit 60, a respiration calculation unit 70, and an operation monitoring unit 80. The HPFs 64I and 64Q and the LPFs 65I and 65Q are digital filters realized by digital signal processing.

  The heart rate calculator 60 receives the input of the digital signals Shi and Shq, and executes various processes. Specifically, the heart rate calculation unit 60 includes an HPF 64I on the I channel side, an HPF 64Q on the Q channel side, an LPF 65I on the I channel side, an LPF 65Q on the Q channel side, and a fundamental wave detection unit 66I on the I channel side. It includes a fundamental wave detection unit 66Q on the Q channel side and a heart rate average processing unit 67.

  The HPFs 64I and 64Q respectively generate the digital signals Hai and Haq by removing low frequency components (particularly, the band of the respiratory component) of the digital signals Shi and Shq. The HPF 64I outputs the digital signal Hai to the LPF 65I, and the HPF 64Q outputs the digital signal Haq to the LPF 65Q. Typically, the HPFs 64I and 64Q remove frequency components lower than 0.7 Hz (that is, equivalent to 42 bpm).

  The LPFs 65I and 65Q generate digital signals Hbi and Hbq by removing high frequency components of the digital signals Hai and Haq, respectively. The LPF 65I outputs the digital signal Hbi to the fundamental wave detection unit 66I, and the LPF 65Q outputs the digital signal Hbq to the fundamental wave detection unit 66Q. Typically, the LPFs 65I and 65Q remove frequency components of 20 Hz or more. The LPFs 65I and 65Q may be configured to remove frequency components of 4 Hz (that is, corresponding to 240 bpm) or more.

  The fundamental wave detectors 66I and 66Q calculate the heart rate using the digital signals Hbi and Hbq, respectively. Specifically, the fundamental wave detection unit 66I performs fast Fourier transform (FFT) on the digital signal Hbi stored for a predetermined time (for example, 5 seconds), and decomposes it into individual signal components, and then the respective components are separated. Is processed on the frequency spectrum to create frequency distribution data. The fundamental wave detection unit 66I selects a frequency distribution (for example, 0.7 Hz to 20 Hz) in a predetermined range related to the heartbeat from the frequency distribution data, and the frequency component with the highest intensity (peak) is selected from among the fundamental frequency waves. Detect as data (ie, fundamental frequency). The fundamental wave detection units 66I and 66Q may detect fundamental wave data using an autocorrelation function, wavelet transform, or the like.

  The fundamental wave detection unit 66I calculates the heart rate Hi, which is the number of heartbeats per unit time (for example, one minute), by multiplying the fundamental frequency by a predetermined factor (for example, 60). Similarly, the fundamental wave detection unit 66Q calculates the heart rate Hq using the digital signal Hbq.

  The heart rate average processing unit 67 calculates the heart rate Hn by averaging the heart rate Hi and the heart rate Hq. The heart rate average processing unit 67 may remove signals with small noise level intensity or signals with poor periodicity by integrating the digital signals Hbi and Hbq and appropriately setting the threshold.

  The respiration operation unit 70 receives the input of the digital signals Sti and Stq, and executes various processes. Specifically, the respiration operation unit 70 includes an LPF 71I on the I channel side, an LPF 71Q on the Q channel side, a fundamental wave detection unit 72I on the I channel side, a fundamental wave detection unit 72Q on the Q channel side, and respiration average processing. And part 73.

  The LPFs 71I and 71Q generate digital signals Bai and Baq by removing high frequency components of the digital signals Sti and Stq, respectively. The LPF 71I outputs the digital signal Bai to the fundamental wave detection unit 72I, and the LPF 71Q outputs the digital signal Baq to the fundamental wave detection unit 72Q. Typically, the LPFs 71I and 71Q remove frequency components of 0.75 Hz or higher (that is, equivalent to 45 bpm).

  The fundamental wave detectors 72I and 72Q calculate the respiration rate using the digital signals Bai and Baq, respectively. The fundamental wave detection unit 72I calculates the respiration rate by the same calculation method as the calculation method by the fundamental wave detection unit 66I. Specifically, the fundamental wave detection unit 72I creates frequency distribution data by subjecting the digital signal Bai accumulated for a predetermined time (for example, 10 seconds) to fast Fourier transform. Among the frequency distribution data, the fundamental wave detection unit 72I is the fundamental wave data (that is, the fundamental frequency) of the frequency component with the highest intensity among the frequency distribution (for example, 0 Hz to 0.75 Hz) in a predetermined range related to respiration. As detected. The fundamental wave detection unit 72I calculates the respiration rate Bi, which is the number of respirations per unit time (for example, one minute), by multiplying the frequency of the fundamental wave data by a predetermined factor (for example, 60). Similarly, the fundamental wave detection unit 72Q calculates the respiration rate Bq using the digital signal Baq.

  The respiration average processing unit 73 calculates the respiration rate Bn by averaging the respiration rate Bi and the respiration rate Bq. The respiration average processing unit 73 may remove the signal with a small noise level or the signal with a poor periodicity by integrating the digital signals Bai and Baq and appropriately setting a threshold.

  The operation monitoring unit 80 monitors the operation of the subject based on the body movement signal (specifically, each digital signal Sti, Stq) extracted from the signal of the reflected wave Mr. Operation monitoring unit 80 includes a detection unit 81, an amplitude calculation unit 82, a distance estimation unit 83, a ratio calculation unit 84, and a determination unit 85. In the following description, the digital signal corresponding to the I channel is simply referred to as "I signal", and the digital signal corresponding to the Q channel is simply referred to as "Q signal".

  The detection unit 81 detects the approaching operation and the separating operation of the subject at predetermined intervals based on the I signal Sti and the Q signal Stq. Specifically, the detection unit 81 detects the approaching operation and the separating operation based on the loci of the I signal Sti and the Q signal Stq on the IQ plane.

  FIG. 9 is a diagram showing an example of an IQ plane of a reflected wave according to the first embodiment. An IQ plane which is a complex plane is composed of an I axis (in-phase axis) which is a horizontal axis, and a Q-axis (quadrature phase axis) which is a vertical axis. FIG. 9A shows the case where the subject approaches the monitoring device 100, and FIG. 9B shows the case where the subject separates from the monitoring device 100. Each point in FIG. 9A and each point in FIG. 9B are plots of the I signal Sti and the Q signal Stq at each sampling time.

  Referring to FIG. 9A, a counterclockwise arrow 601 indicates the direction of the locus of coordinates on the IQ plane of the I signal Sti and the Q signal Stq when the subject approaches the monitoring device 100. ing. Referring to FIG. 9B, a clockwise arrow 602 indicates the direction of the locus of coordinates on the IQ plane when the subject separates from the monitoring apparatus 100.

  The detection unit 81 calculates the trajectory direction for each point. Specifically, the detection unit 81 calculates the phase θ of the reflected wave on the IQ plane every sampling time. The phase θ is calculated by arctan (Q signal Stq / I signal Sti). The detection unit 81 determines whether the phase θ at each point is increasing (that is, in the increasing direction) or whether the phase θ is decreasing (that is, is the decreasing direction) (that is, the phase θ is Judge how to move), calculate the track direction.

  For example, the detection unit 81 calculates the increase direction and the decrease direction of the phase θ 40 times (that is, corresponds to the number of times of sampling for 0.1 seconds), and when the phase θ is 10 directions or more continuously increase direction The movement of the subject during the unit period (ie, 0.1 seconds) is detected as the approaching movement. For example, when it is determined that the phase θ is in the decreasing direction continuously ten times or more, the detection unit 81 detects the operation of the subject in the unit period as the separation operation. In the case where the phase θ does not increase or decrease continuously ten times or more and does not decrease, the detecting unit 81 determines that the approaching operation and the separating operation are not detected (that is, not determined). .

  Here, the configuration has been described in which the approach (or separation) operation is detected when the increase (or decrease) direction of the phase θ continues 10 times or more in 40 times, but it is continuous 20 times or more in 40 times In this case, the operation may be detected. In addition, when the difference between the number of approaches and the number of departures is 10 or more in 40 (or 20 or more), an operation corresponding to a larger number of times is detected as the operation of the subject. It is also good. These configurations may be selected as appropriate according to the performance of the microwave Doppler sensor 160 of the monitoring apparatus 100, the installation position, and the installation environment.

  Furthermore, in the monitoring apparatus 100, although the structure which determines approach and separation in the direction of turning of the said IQ plane was demonstrated, it is not restricted to this. For example, the phase inversion of the phase of the I channel signal and the phase of the Q channel signal (here, the phase inversion of the phase of the I channel and the phase of the Q channel is reversed and the phase of the Q channel is faster The approach and departure may be determined using approach and separation at the time of inversion when the phase of the Q channel is delayed). In addition, the configuration may be a combination of both the rotation of the phase on the IQ plane and the progressive inversion of the IQ phase.

  Again referring to FIG. 7, the amplitude computing unit 82 computes the amplitude (hereinafter also referred to as "body movement amplitude") of the body movement signal (I signal Sti, Q signal Stq). Typically, a combined amplitude of the amplitude of the I signal Sti and the amplitude of the Q signal Stq (that is, the distance from the “0” point on the IQ plane in FIG. 9) is used as the body movement amplitude. The combined amplitude is represented by SQRT {(amplitude of I signal Sti) ^ 2 + (amplitude of Q signal Stq) ^ 2}.

  In one aspect, the amplitude computing unit 82 performs averaging processing of body movement amplitude every predetermined time Ts (for example, one second). For example, when the sampling rate is 400 Hz (that is, sampling every 2.5 ms), the amplitude computing unit 82 executes a process of averaging 400 (that is, the number of samplings per second) of body movement amplitudes. .

  In another aspect, the amplitude computing unit 82 calculates the integrated value of the body movement amplitude during the continuation period of the operation including at least one of the approaching operation and the separating operation of the subject. The integrated value is a value obtained by integrating (accumulating) an average value of body movement amplitudes at predetermined time intervals (for example, one second) over a continuous period. For example, in the case where the duration is 4 seconds, the integrated value is a value obtained by adding the average value of the body motion amplitudes for four times. The start time point of the duration period is a time point at which the subject's action (at least one of the approaching action and the leaving action) is detected. However, it is assumed that the motion of the subject is not detected within a predetermined past time Tx (for example, several seconds) from the time point. The end time point of the continuation period is a time point at which the latest operation is detected in the case where the next operation is not detected even when a predetermined time Tx has elapsed since the latest operation was detected.

  Further, the microprocessor 45 can calculate the approaching movement and the separating movement of the subject and the body movement amplitude in time series by the functions of the detecting unit 81 and the amplitude calculating unit 82.

  FIG. 10 is a diagram showing a time change of the approaching operation, the separating operation, and the body movement amplitude according to the first embodiment. Here, it is assumed that the subject moves away from the monitoring device 100 after the subject approaches the monitoring device 100.

  Specifically, FIG. 10A is a view showing temporal change of the approaching operation and the separating operation detected by the detecting unit 81. As shown in FIG. In FIG. 10A, the horizontal axis represents time, and the vertical axis represents the number of detections of the approaching operation or the separating operation. FIG. 10 (b) is a view showing temporal change of the body movement amplitude calculated by the amplitude calculator 82. The horizontal axis of FIG. 10 (b) is time, and the vertical axis shows the magnitude of body movement amplitude. The unit of the magnitude of the amplitude is an arbitrary unit (au) and indicates the intensity amplitude (corresponding to a voltage component) of the reflected signal from the subject. The body movement amplitude is averaged every predetermined time Ts (for example, one second).

  As described above, when the phase θ is in the increase direction continuously ten times or more, the detection unit 81 detects the motion of the subject in the unit period (for example, 0.1 seconds) as the approaching motion, When the phase θ is in the decreasing direction continuously ten times or more, the movement of the subject in the unit period is detected as the separation movement.

  Referring to FIG. 10A, during the period from time t1 to time t2 (that is, duration T1n = 3 × Ts), the detection unit 81 detects the approaching operation. The number of approach operations detected at this time is N1 times. The detecting unit 81 detects the separating operation from time t3 to time t4. The number of separation operations detected at this time is A1. The period from time t2 to time t3 is an undetermined section in which the approaching operation and the separating operation are not detected by the detecting unit 81. In this undetermined section, the phase θ is not detected as the approaching operation and the separating operation because the phase θ does not continuously increase or decrease ten times or more.

  Since the detection unit 81 detects the approach operation of the subject at time t1, the detection unit 81 recognizes time t1 as the start time of the continuation period of the operation. Further, since the approaching operation and the separating operation are not detected even after the predetermined time Tx has passed from the time t2, the time t2 is recognized as the end time of the continuation period. Thus, the continuation period T1 n is a period from time t1 to time t2. In addition, since the detection unit 81 detects the approach operation of the subject at time t3, the detection unit 81 recognizes time t3 as the start time of the operation continuation period. Further, since the approaching operation and the separating operation are not detected even when the predetermined time Tx has elapsed from the time t4, the time t4 is recognized as the end time of the continuation period. Thus, the continuation period T1a is a period from time t3 to time t4.

  The amplitude computing unit 82 calculates an integrated value Q1 of the body movement amplitude in the continuation period T1 n. Specifically, the integrated value Q1 is a value obtained by integrating an average value of body movement amplitudes at predetermined time intervals Ts over a continuation period T1n. The amplitude calculator 82 calculates an integrated value Q2 of body movement amplitudes in the continuation period T1a. The integrated value Q2 is a value obtained by integrating an average value of body movement amplitudes at predetermined time intervals Ts over a continuation period T1a.

  Similarly, the detection unit 81 detects the approaching operation N2 times in the continuation period T2n, and detects the separating operation A2 times in the continuation period T2a (see FIG. 10A). The amplitude computing unit 82 calculates an integrated value Q3 of the body movement amplitude in the continuation period T2n, and calculates an integrated value Q4 of the body movement amplitude in the continuation period T2a (see FIG. 10B).

  Referring again to FIG. 7, distance estimating unit 83 determines the relationship between the result of the motion analysis detected by detector 81, the average value of the body movement amplitudes calculated by amplitude calculator 82, and the memory 154. Based on the information J, the distance between the subject and the monitoring apparatus 100 is estimated. As described above, the detection unit 81 detects an operation (approaching operation or separating operation) of the subject every unit period (for example, 0.1 seconds). Further, the amplitude computing unit 82 calculates an average value of body movement amplitude every predetermined time Ts (for example, one second).

  The distance estimation unit 83 compares the number of approaching operations and the number of separating operations at a predetermined time Ts. If the number of the approaching motions is larger than the number of the separating motions, the distance estimating unit 83 determines that the average value of the body motion amplitudes calculated by the amplitude computing unit 82 is the body motion amplitude value associated with the approaching motions. If the number of detachment operations is greater than the number of approaching operations, the average value of the body movement amplitudes is determined to be the body movement amplitude associated with the detachment operations.

  Here, how the body movement amplitude changes according to the distance from the monitoring device 100 to the subject will be described. FIG. 11 is a diagram showing the relationship between the distance between the monitoring apparatus 100 and the subject and the body movement amplitude. The vertical axis represents the average value of the body movement amplitude at the predetermined time Ts. The values on the vertical axis are digital values when AD converting the amplitude (voltage 0 V to 3.3 V) of the analog signals Sti and Stq, which are analog values of body movement amplitude. The horizontal axis indicates the distance between the monitoring device 100 and the subject. Here, it is assumed that the subject is approaching the monitoring device 100 in a section where the distance is 0 m to 8 m. The subject is an old man, and walking in the subject's room is at a speed of about 0.5 m / s (that is, 1.8 km / h).

  Referring to FIG. 11, the threshold value Th1 (for example, 12000) of the body movement amplitude is a value when the subject approaches the monitoring device 100 about 1 m from the front. The threshold value Th2 (for example, 370) of the body movement amplitude is a value when there is no subject in the room 201 and there is no movement of a person.

  According to the graph 800 of FIG. 11, it can be seen that the body movement amplitude increases as the distance decreases. Specifically, when the subject is at a relatively distant position from the monitoring device 100 (for example, a distance of 8 m to 4 m), the body movement amplitude gradually increases as the distance decreases. On the other hand, when the subject is present at a position relatively close to the monitoring device 100 (for example, a distance of 4 m to 0 m), the body movement amplitude rapidly increases as the distance decreases. This depends on the characteristics of the microwave Doppler sensor including the performance of the planar antenna of the monitoring device 100.

  The distance estimation unit 83 estimates the distance between the monitoring device 100 and the subject using the motion amplitude associated with the approaching operation and the graph 800 stored in the memory 154 as the relationship information J. For example, when the body movement amplitude is about 8000, the distance estimation unit 83 estimates that the distance is approaching at 2 m.

  Note that, even if the relationship between the distance between the monitoring apparatus 100 and the subject and the motion amplitude is stored in the memory 154 as the relationship information J, the subject is separated from the monitoring apparatus 100. Good. Thereby, the distance estimation unit 83 can estimate the distance between the monitoring apparatus 100 and the subject and the movement direction (separation) using the body motion amplitude accompanying the separation operation and the graph GR.

  In addition, when the characteristics of the graph 800 and the graph GR substantially match, the distance estimation unit 83 does not determine whether it is the body movement amplitude value associated with the approaching operation or the body movement amplitude associated with the separating operation. Good. In this case, the distance estimation unit 83 determines the distance between the monitoring apparatus 100 and the subject, the direction of approach and departure, and the direction of movement based on the body movement amplitude calculated by the amplitude calculation unit 82 and the graph 800 or the graph GR. Estimate As described above, when the subject walks at a constant speed in the standing posture, the distance between the subject and the monitoring apparatus 100 and the movement direction of the approach and departure are made using the body movement amplitude. It can be estimated.

  In the above description, when estimating the distance, the configuration using the synthetic amplitude as the body movement amplitude has been described, but the absolute value of the amplitude of the I signal Sti or the absolute value of the amplitude of the Q signal Stq may be used. Alternatively, the sum of the absolute value of the amplitude of the I signal Sti and the absolute value of the amplitude of the Q signal Stq may be used as the body movement amplitude.

  Referring again to FIG. 7, the ratio calculator 84 determines the amplitude of the body movement signal (I signal Sti, Q signal Stq) and the respiration signal (I signal) calculated by the respiration calculator 70 at predetermined time intervals Ts. An amplitude ratio BBRATIO with the amplitude of Bai, Q signal Baq) (hereinafter also referred to as "respiration amplitude") is calculated. The amplitude of the heartbeat signal (I signal Hbi, Q signal Hbq) is also referred to as “heartbeat amplitude”.

  Typically, ratio operation unit 84 calculates composite amplitude A1 of the average value of the amplitude (absolute value) of I signal Sti and the average value of the amplitude (absolute value) of Q signal Stq at predetermined time Ts. . The ratio calculator 84 calculates a combined amplitude A2 of the average value of the amplitudes (absolute values) of the I signal Bai and the average value of the amplitudes (absolute values) of the Q signal Baq. Then, the ratio calculation unit 84 calculates, as an amplitude ratio BBRATIO, a ratio of the combined amplitude A1 of the body movement signal to the combined amplitude A2 of the respiration signal.

  The amplitude ratio BBRATIO may be a ratio of the amplitude (absolute value) of the I signal Sti to the average value of the amplitude (absolute value) of the I signal Bai, or the average of the amplitude (absolute value) of the Q signal Baq. It may be a ratio of the amplitude (absolute value) of the Q signal Stq to a value. Alternatively, the ratio calculation unit 84 calculates an integrated value of the amplitude of a predetermined period for each of the body motion signal and the respiration signal, and calculates the integrated value of the amplitude of the body motion signal with respect to the integration value of the respiration signal amplitude. It may be calculated as the amplitude ratio BBRATIO. For ease of explanation, in the following description, the ratio calculation unit 84 calculates the synthetic amplitude A1 as the body movement amplitude and calculates the synthetic amplitude A2 as the respiration amplitude.

  When the sampling frequency is 400 Hz, the predetermined time Ts may be set in the range of 0.1 seconds to 1 second. The predetermined time Ts may be appropriately determined in accordance with the sampling speed and the movement speed of the subject to be monitored. Generally, in consideration of the movement of a person, it is preferable that the predetermined time Ts be 1 second or less.

  The determination unit 85 determines various operations of the subject based on the body movement signal of the subject. In one aspect, the determination unit 85 uses the threshold value Th1 (for example, 12000) of the body movement amplitude (see FIG. 10 (b) and FIG. 11), and the monitoring apparatus 100 and the subject approach each other for every predetermined time Ts. It is determined whether the Specifically, when the body movement amplitude (average value) of the predetermined time Ts is equal to or greater than the threshold Th1, the determination unit 85 determines that the monitoring apparatus 100 and the subject are approaching, and the body If the motion amplitude is less than the threshold Th1, it is determined that the monitoring apparatus 100 and the subject are not approaching. In addition, the determination unit 85 calculates the number of times the body movement amplitude has become equal to or greater than the threshold Th1 within a predetermined period (for example, one day, in the morning, in the afternoon, etc.).

  In another aspect, the determination unit 85 uses the amplitude ratio BBRATIO to determine whether the respiration rate Bn indicates the respiration rate of the subject's person (for example, in a calm state) or the frequency range Fb in the low frequency range. It is determined whether the number of body movements of the subject in is indicated. The frequency range Fb includes a frequency range corresponding to the respiration of the human body, and is a frequency range that has passed through the LPFs 71I and 71I in the respiration calculation unit 70. The amplitude ratio BBRATIO is a normalized value of one or more. However, when used as a determination index in the determination unit 85, for example, it may be multiplied by 1000 and normalized to a value of 1000 or more.

  Here, when the subject is in a resting state, a body movement signal (I signal Sti, Q signal Stq) reflecting the breathing movement is input to the operation monitoring unit 80. Therefore, the body movement amplitude calculated by the amplitude calculator 82 is an amplitude corresponding to the breathing operation. On the other hand, the respiration amplitude calculated by the respiration calculation unit 70 is an amplitude corresponding to the respiration operation. Therefore, when the subject is at rest, the body movement amplitude and the respiration amplitude become almost the same, and the amplitude ratio BBRATIO takes a value of around 1.0 (around 1000 when multiplied by 1000). .

  Therefore, when the amplitude ratio BBRATIO is less than the threshold Thx1 (for example, 1100) (that is, when the subject is in a stationary state), the determination unit 85 determines the respiration rate Bn calculated based on the fundamental frequency. It is determined that the respiratory rate of the subject at rest is indicated. On the other hand, when the amplitude ratio BBRATIO is equal to or greater than the threshold Thx1 (that is, when the subject is not at rest), the determination unit 85 determines that the respiration rate Bn calculated based on the fundamental frequency includes the respiration region. It is determined that the number of body movements of the subject in the frequency domain Fb is indicated.

  Similarly, using the amplitude ratio BBRATIO, the determination unit 85 determines whether the heart rate Hn indicates the heart rate of the subject at rest, or the body movement frequency of the subject in the frequency range Fh, which is a high frequency range. To determine if The frequency range Fh includes a frequency range corresponding to the heartbeat of the human body, and is a frequency range that has passed through the HPFs 64I and 64Q and the LPFs 65I and 65Q in the heartbeat calculation unit 60. Specifically, when the amplitude ratio BBRATIO is less than the threshold Thx1 (that is, when the subject is in the resting state), the determination unit 85 determines that the heart rate Hn is the heart rate at the time of the subject's inactivity. It is determined that the On the other hand, when the amplitude ratio BBRATIO is equal to or greater than the threshold Thx1 (that is, when the subject is not in the resting state), the determination unit 85 determines that the heart rate Hn is the subject in the frequency range Fh including the heart rate range. It is determined that the number of body movements is indicated.

  The output control unit 54 outputs activity information based on the operation of the subject monitored by the operation monitoring unit 80. Specifically, the output control unit 54 determines the body movement amplitude, the estimated distance estimated by the distance estimation unit 83, the amplitude ratio BBRATIO, the determination result of the determination unit 85, the number of times the body movement amplitude has become the threshold Th1 or more, etc. It is received from the operation monitoring unit 80. In one aspect, the output control unit 54 outputs the respiration rate Bn as the respiration rate of the subject at rest or the body movement rate of the subject in the frequency range Fb according to the determination result of the determination unit 85. . The output control unit 54 outputs the respiration rate Bn as the respiration rate of the subject or the body movement number of the subject in the frequency range Fh according to the determination result of the determination unit 85.

  The activity information includes: body movement amplitude, estimated distance, amplitude ratio BBRATIO, determination result, number of times body movement amplitude exceeds threshold Th1, respiratory rate, heart rate, body movement rate of subject in frequency domain Fb, and frequency It includes the motion number of the subject in the area Fh. Note that the output control unit 54 does not have to output all of the above as the activity information, and may output arbitrarily selected information.

  The output control unit 54 may output the activity information by voice via the speaker 156 or may display the activity information on the display. Also, the output control unit 54 may transmit the activity information to the terminal device 200 via the communication interface 158.

  Further, the output control unit 54 may output warning information when the activity information satisfies a predetermined condition. For example, when the body movement amplitude becomes equal to or higher than the threshold Th1, and the amplitude ratio BBRATIO becomes equal to or higher than the threshold Thx2 (for example, 2500), the subject is about to leave the room 201 Is assumed. In this case, the output control unit 54 outputs a voice message such as “Don't leave the room” or “Wait for a carer to come” as warning information, and urges attention. The output control unit 54 may transmit, to the terminal device 200, information indicating that the subject is about to leave the room as the warning information.

  In addition, the threshold value Th2 (for example, Th2 <370) or less indicating whether or not there is a body movement signal in a predetermined period, and the amplitude ratio BBRATIO is 1 (1000 when multiplied by 1000), If the body movement number in the frequency domain Fh and the body movement number in the frequency domain Fb are both 0 bpm, the subject may fall down in the room 201. In this case, the output control unit 54 may transmit, to the terminal device 200, information indicating that the subject may have fallen into the room as the warning information.

  The threshold Th2 is calculated by operating the monitoring apparatus 100 in the state where no one is present in advance. Furthermore, the microprocessor 45 outputs a signal indicating "with body movement" when the body movement amplitude value is greater than or equal to the threshold value Th2, and indicates "without body movement" when the body movement amplitude value is less than the threshold value Th2. A signal may be output.

<Processing procedure>
The procedure of various processes executed by the monitoring apparatus 100 will be described. The following process steps are mainly implemented by the microprocessor 45 of the control circuit 152 executing a program stored in the memory 154. In addition, before performing each process of the following FIGS. 12-14, the microprocessor 45 performs environmental calibration about a respiration component, a heart rate component, and a body motion component.

  Specifically, the monitoring device 100 performs sensing for a fixed time (for example, one minute) in a state where a mobile body such as a human body is not present in a space (for example, the room 201) where the monitoring device 100 is installed. Calculate the average value of heart rate amplitude and body movement amplitude. Then, with regard to the respiration amplitude, a threshold value K1 which is a value (for example, 1.2 times) slightly larger than the average value of the respiration amplitude is set as a threshold for distinguishing the noise component and the signal component. Similarly, with regard to the heartbeat amplitude, a threshold K2 which is a value slightly larger than the average value of the heartbeat amplitude is set as a threshold for distinguishing the noise component from the signal component. A threshold value K3 which is a value slightly larger than the average value of body movement amplitude is set as the body movement amplitude, as a threshold value for distinguishing the noise component from the signal component.

  Typically, synthetic amplitudes are used as respiration amplitudes, heart rate amplitudes and body movement amplitudes, but absolute values of I and Q signal amplitudes may be averaged, or absolute values of I signal amplitudes may be averaged. Or the absolute value of the amplitude of the Q signal may be averaged.

  When the measurement by the monitoring apparatus 100 is started, it branches into three of a breathing area calculation process shown in FIG. 12, a heart rate area calculation process shown in FIG. 13, and a body movement calculation process shown in FIG.

(Respiration area arithmetic processing)
FIG. 12 is a diagram showing an example of a breathing area calculation process of monitoring apparatus 100 according to the first embodiment.

  12, microprocessor 45 receives input of I signal Sti and Q signal Stq from AD converter 43, generates I signal Bai and Q signal Baq, and generates a combined amplitude of I signal Bai and Q signal Baq. Is calculated, and it is determined whether the combined amplitude is larger than the threshold K1 (step S12).

  If the synthetic amplitude is less than or equal to the threshold value K1 (NO in step S12), the microprocessor 45 determines that the respiration signal does not exist and that the amplitude is the noise level (that is, the respiration of the subject is not detected; It is judged 0 bpm) (step S18), and the processing is ended.

  On the other hand, when the combined amplitude is larger than threshold value K1 (YES in step S12), microprocessor 45 generates frequency distribution data for each of I signal Bai and Q signal Baq, and based on the frequency distribution data, signal strength (peak) The high frequency component of is detected as the fundamental frequency (step S14). Specifically, the processing by the above-described fundamental wave detectors 72I and 72Q is performed. Subsequently, the microprocessor 45 calculates a respiration rate Bn obtained by averaging the respiration rate Bi and the respiration rate Bq for which the respiration rate for 1 minute is obtained from the fundamental frequency (step S16). The microprocessor 45 stores m past (for example, m = 2) respiratory rates, and calculates a median value from (m + 1) respiratory rates including the respiratory rate calculated by averaging this time. By doing this, the respiration rate Bn may be calculated.

  Next, the microprocessor 45 determines whether the amplitude ratio BBRATIO calculated in step S74 of FIG. 14 described later is less than the threshold Thx1 (for example, 1100) (step S20). If the amplitude ratio BBRATIO is less than the threshold Thx1 (YES in step S20), the microprocessor 45 outputs the respiration rate Bn as the respiration rate of the subject at rest (step S22), and ends the process. .

  On the other hand, when the amplitude ratio BBRATIO is equal to or higher than the threshold Thx1 (NO in step S22), the microprocessor 45 outputs the respiration rate Bn as a body movement number in the frequency range Fb including the breathing range (step S24) , End the process.

  After the processing is completed, the microprocessor 45 returns to step S10 again, and continuously and repeatedly executes the breathing region calculation processing.

  In addition, when the movement of the body is added (for example, when the amplitude ratio BBRATIO is 1200 or more), the movement of the body is usually dominated by one movement per second, that is, a movement of 1 Hz or more. Therefore, the slow movement of the breathing area becomes inferior, and the body movement frequency of the frequency area Fb tends to decrease.

(Heart region arithmetic processing)
FIG. 13 is a diagram showing an example of heart rate region calculation processing of monitoring device 100 according to the first embodiment.

  Referring to FIG. 13, microprocessor 45 receives inputs of I signal Shi and Q signal Shq from AD converter 43, and executes high-pass filter processing with HPFs 64I and 64Q (step S40). Specifically, the microprocessor 45 removes the low frequency component (for example, 0.7 Hz or less) of the I signal Sti by the HPF 64I to generate the I signal Hai, and removes the low frequency component of the Q signal Shq by the HPF 64Q. To generate a Q signal Haq.

  The microprocessor 45 executes low-pass filter processing by the LPFs 65I and 65Q (step S42). Specifically, the microprocessor 45 removes high frequency components (for example, 20 Hz or more) of the I signal Hai by the LPF 65I to generate the I signal Hbi, and removes high frequency components of the Q signal Haq by the LPF 65Q to generate the Q signal Hbq. Generate The cutoff frequencies of the LPF 65I and the LPF 65Q may be low frequencies of about 7 Hz and 10 Hz, or may be relatively high frequencies of about 200 Hz.

  The microprocessor 45 calculates the combined amplitude of the I signal Hbi and the Q signal Hbq, and determines whether the combined amplitude is larger than the threshold value K2 (step S44).

  If the synthetic amplitude is equal to or smaller than the threshold K2 (NO in step S44), the microprocessor 45 determines that the heartbeat signal is absent and the amplitude is the noise level (that is, the heartbeat of the subject is not detected; It judges that it is 0 bpm (step S50), and ends the processing.

  On the other hand, when the composite amplitude is larger than threshold value K2 (YES in step S44), microprocessor 45 generates frequency distribution data for each of I signal Hbi and Q signal Hbq, and based on the frequency distribution data, signal strength (peak) The high frequency component of is detected as the fundamental frequency (step S46). Specifically, the processing by the above-described fundamental wave detectors 66I and 66Q is performed. Subsequently, the microprocessor 45 calculates the heart rate Hn by averaging the heart rate Hi and the heart rate Hq for which the heart rate for one minute is obtained from the fundamental frequency (step S48). The microprocessor 45 stores the past m heart rates (for example, m = 2), and calculates a median value from (m + 1) heart rates including the heart rate calculated by averaging this time By doing this, the heart rate Hn may be calculated.

  Next, the microprocessor 45 determines whether the amplitude ratio BBRATIO calculated in step S74 of FIG. 14 described later is less than the threshold Thx1 (for example, 1100) (step S52). If the amplitude ratio BBRATIO is less than the threshold Thx1 (YES in step S52), the microprocessor 45 outputs the heart rate Hn as the respiratory rate of the subject at rest (step S54), and ends the process. .

  On the other hand, if the amplitude ratio BBRATIO is equal to or greater than the threshold Thx1 (NO in step S52), the microprocessor 45 outputs the heart rate Hn as a body movement number in the frequency range Fh including the heart rate range (step S56) , End the process.

  After the processing is completed, the microprocessor 45 returns to step S40 again and continuously and repeatedly executes the heartbeat region calculation processing.

  In addition, when the movement of the body is added (for example, when the amplitude ratio BBRATIO is 1200 or more), the movement of the body is usually dominated by one movement per second, that is, a movement of 1 Hz or more. In this case, since the fast movement of the heart rate area is dominant, not the heart rate of the weak movement but the body movement frequency indicating the movement of the body is output.

(Body movement operation processing)
FIG. 14 is a diagram showing an example of body movement calculation processing by monitoring device 100 according to the first embodiment.

  Referring to FIG. 14, microprocessor 45 receives inputs of I signal Sti and Q signal Stq from AD converter 43, and calculates body movement amplitude (step S70). Specifically, the microprocessor 45 calculates the combined amplitude of the I signal Sti and the Q signal Stq. Subsequently, the microprocessor 45 determines the presence or absence of body movement based on the calculated combined amplitude and the threshold value K3 (step S72). Specifically, when the body movement amplitude is equal to or less than the threshold value K3, the microprocessor 45 determines that there is no body movement signal and that the amplitude is at the noise level (that is, the body movement of the subject is absent). Do. On the other hand, when the body movement amplitude is larger than the threshold value K3, the microprocessor 45 determines that the body movement of the subject is present.

  The microprocessor 45 calculates an amplitude ratio BBRATIO indicating the ratio of the body movement amplitude to the respiration amplitude obtained in the breathing area calculation process (step S74). Subsequently, the microprocessor 45 detects the approaching operation and the separating operation of the subject (step S76).

  The microprocessor 45 outputs various activity information based on the information calculated in steps S70 to S76 (step S78). Specifically, the microprocessor 45 determines the motion amplitude (for example, the maximum value, the minimum value, the average value) calculated in step S70 and the presence or absence of the motion calculated in step S72 every predetermined time Ts, The amplitude ratio BBRATIO calculated in step S74 and the detection result (for example, the number of times of approach, the number of times of separation) of the approaching operation and the separating operation of the subject in step S76 are output. Further, the microprocessor 45 compares the motion amplitude with the threshold value Th1 within a predetermined time Ts to determine whether the subject is approaching the monitoring apparatus 100, and the approach based on the determination result is performed. You may output the frequency. Furthermore, the microprocessor 45 may output the distance between the subject and the monitoring device 100 estimated based on the average value of the body movement amplitude and the relationship information J.

<Example>
The measurement result of the activity information measured by installing the monitoring apparatus 100 in a room of 3 m × 3.6 m will be described.

  FIG. 15 is a diagram for explaining an installation method of the monitoring apparatus 100 according to the embodiment. Referring to FIG. 15, similarly to FIG. 4 (or FIG. 5), the monitoring apparatus 100 is horizontally installed near the entrance (the door in FIG. 15) of the room 201b. In this embodiment, the subject sits in a chair placed in front of a desk (in a sitting posture) to watch the television 210, work at a desk, or bed in the bed 300. Do. The monitoring device 100 monitors the operation of the subject and outputs activity information.

  FIG. 16 and FIG. 17 show the measurement results of the activity information. Specifically, in FIG. 16, the body motion number in the frequency range Fh including the heart rate region (hereinafter, also simply referred to as “body motion number in the heart rate region”) and the frequency range Fb including the breathing region (hereinafter simply “ Also referred to as “moving speed of breathing area”), moving speed of moving area (synthesized amplitude) is shown. FIG. 17 shows a body movement amplitude and an amplitude ratio BBRATIO (normalized value) in a predetermined range (0 to 1500). The horizontal axis of FIG. 16 and FIG. 17 is time (minute), and the measurement result of about 30 minutes is shown. Each activity information in FIG. 16 and FIG. 17 indicates an average value at one second intervals.

  Referring to FIGS. 16 and 17, the subject watches television 210 or the like in sitting position in period Tk1, operates in a standing position in period Tk2, and leaves room 201 in period Tk3. The operation in the standing posture / sitting posture / standing posture is repeated in the period Tk4, and a crawling operation is performed in the period Tk5, and a rising operation is performed in the period Tk6.

  The body movement amplitude during operation in the standing posture in the period Tk2 or in the period Tk4 is very large compared to the body movement amplitude during the operation in the sitting posture in the period Tk1. When the user approaches the monitoring apparatus 100 in a standing position (here, the distance between the monitoring apparatus 100 and the subject is several centimeters) in order to exit the door (the distance between the monitoring apparatus 100 and the subject is several cm), the body motion amplitude is the threshold Th1 ( For example, it greatly exceeds 12000) (see the region Rm1 in FIG. 16). In a period Tk3 in which the subject is leaving the room 201, the body movement amplitude is in the vicinity of the threshold value Th2 (for example, 370) and is a noise floor (see the area Rm3 in FIG. 17). Subsequently, when the subject enters the room 201 and departs from the monitoring apparatus 100 (see the region Rm2 in FIG. 16), the body movement amplitude gradually falls below the threshold Th1.

  Although the body movement frequency in the breathing area is close to a reference value (for example, 17 bpm) which is the respiratory rate of the subject at rest in the sitting posture (for example, the period Tk1), see (Rb1 in FIG. 16) And in the standing posture (for example, in the periods Tk2 and Tk4), they are below the reference values (see the regions Rb2 and Rb3 in FIG. 16). This is because in the case of the sitting posture, the slow movement of the breathing area is easily detected, and in the standing posture, the slow movement of the breathing area is difficult to detect.

  Although the body movement frequency in the heart rate region is close to the reference value (for example, 55 bpm) which is the heart rate of the subject in the case of sitting posture (for example, period Tk1), (refer to region Rh2 in FIG. 16) And in the standing posture (for example, period Tk2), the reference value is exceeded (see region Rh3 in FIG. 16).

  In the sitting posture (for example, the period Tk1), the region Rh1 in which the body motion speed is partially high is a region in which the second harmonic component of the heart rate is detected. This is because the amplitude of the heartbeat signal decreases and the fundamental wave component of the heartbeat signal can not be detected and the second harmonic component is detected. It is preferable to remove such second harmonic components. For example, by limiting the 48 bpm to 250 bpm of the body motion range of the heart rate region to the second harmonic component or less (for example, 50 bpm to 99 bpm), the harmonic component of the second harmonic (or third harmonic etc.) can be removed. Just do it. It is considered that the heart rate of the subject at rest is generally reflected by removing the second harmonic shown in the region Rh1 in FIG. 16 in the period Tk1.

  In addition, when the subject is out of the room 201, the respiratory rate is zero, and the movement of a person is not detected, the normalized amplitude ratio is defined as about 1000. Therefore, the amplitude ratio is approximately 1000 in the period Tk3. In period Tk1 at the sitting posture, the amplitude ratio is small at 1500 or less (region Ra1 in FIG. 17), and the body movement number in the heart rate region when the second harmonic wave is removed is approximately the reference value (for example, 55 bpm) It's getting close. In particular, when the amplitude ratio is 1100 or less (see area Ra2 in FIG. 17), the body movement frequency in the heart rate area is 55 bpm (see Rh2 in FIG. 16), and the heart rate of the subject at rest (Ie, substantially match the reference value).

  In addition, in the periods Tk2 and Tk3 operating in the standing posture, the amplitude ratio is often 1500 or more (see area Ra3 in FIG. 17). In particular, when approaching the monitoring device 100, the amplitude ratio is rapidly increasing.

  In addition, the amplitude ratio is about 1500 in the period in which the movement of the subject can be detected during the period Tk5 in which the patient is performing bed rest operation, but when the respiration of the subject can not be detected, the amplitude ratio is 1000 (Refer to area Ra4 in FIG. 17). However, the body movement amplitude in the period Tk5 (see the area Rm4 in FIG. 17) has a variation as compared to the body movement amplitude in the period Tk3 in which the subject is leaving (see the area Rm3 in FIG. 17). Therefore, by calculating and comparing the average value and the standard deviation of the body movement amplitude in each period, it can be determined whether the subject is out of the room or whether the subject is performing the bed rest operation. In the period Tk5, in the period in which the movement of the subject can be detected, the body movement number in the breathing area and the body movement number in the heart rate area are near the reference value, but when the movement of the subject becomes minute The body movement speed in the breathing area and the movement speed in the heart rate area are 0 bpm (see the areas Rb4 and Rh4 in FIG. 16).

  Next, an output example of the activity information will be described. FIG. 18 is a diagram showing an output example of activity information according to the first embodiment. In addition, it is assumed that the monitoring apparatus 100 is installed as shown in FIG. Referring to FIG. 18, activity information for two days (for 48 hours) is shown. Specifically, the time zone Tu1 from 7 am to 10 pm on September 10, the time zone Tu2 from 10 pm on September 10 to 7 am on September 11th, September 11 The activity information is shown for each of the four time zones Tu3 from 7 am to 10 pm and the time zone Tu4 from 10 pm on September 11 to 7 am on September 12 ing.

  In addition, as activity information, maximum value and average value of amplitude ratio, average value of body movement amplitude, number of approaches approaching within 1 m from monitoring device 100, average value of heart rate area movement number, average value of heart rate, respiration The average value of the region motion frequency and the average value of the respiration rate are shown.

  For example, compared with the time zone Tu1 which is the active time zone of September 10, in the time zone Tu3 which is the active time zone of September 11, since the amplitude ratio is high and the body movement amplitude is large, the subject Is estimated to be more active than the previous day. This can also be estimated from the fact that in the time zone Tu3 the motion frequency in the heart rate region is high and the motion frequency in the breathing region is low in the time zone Tu1 (that is, detection of slow motion in the breathing region is low). .

  Also, by comparing the body motion rate of the heart rate region with the heart rate, and the comparison with the body motion rate of the breathing region with the respiration rate, the heart rate and respiration rate of the subject at rest will be compared with that of the body of the heart rate region. It is possible to grasp the relationship between movement (relatively fast movement) and physical movement (relatively slow movement) in the breathing area.

  Furthermore, in the time zone Tu3 with respect to the time zone Tu1, it is estimated that the number of access times to the room 201 is larger than in the previous day because the number of approaches is large. In such a case, the caregiver who has seen the output example shown in FIG. 18 can confirm the reason and the like for the subject.

  Also, for example, compared with the time zone Tu2 which is the sleep time zone of September 10 to September 11, the time period Tu4 which is the sleep time zone of September 11 to September 12 has an amplitude ratio of Both the mean and maximum values are low, and the motion amplitude is also low. It is estimated that the subject sleeps deeply in deep sleep in the time zone Tu4 with respect to the time zone Tu2. It can be assumed that this is because the subject is actively moving in the time zone Tu3.

  In this way, it is estimated whether the subject is actively working in his daily life, whether he is losing energy, the frequency of entering and leaving the room, the sleep state, etc., and the subject's activity state Can understand.

<Advantage>
According to the first embodiment, the activity state of the subject can be grasped by monitoring the information related to the body movement of the subject. For example, in a room, it can be grasped whether the subject is actively moving, resting, or leaving the room. In addition, if the subject is walking in a standing posture, the distance to the monitoring device 100 can be estimated. Furthermore, it is also possible to estimate whether the number of relatively slow motions or the number of relatively fast motions is large based on the motion frequency of the breathing area and the motion frequency of the heart rate region.

Second Embodiment
In the second embodiment, an installation method of the monitoring apparatus 100 different from the first embodiment will be described. In the first embodiment, the configuration in which the monitoring apparatus 100 is installed around the entrance portion 203 of the room 201 has been described, but in the second embodiment, the configuration is installed around the place where the subject usually spends in the room 201. Will be explained. For example, it is assumed that the subject is an old man who needs nursing care and generally spends on the bed 300 in the room 201.

  FIG. 19 is a diagram for illustrating an installation method of monitoring apparatus 100 according to the second embodiment. Specifically, FIG. 19A is a schematic view (plan view) when the subject on the bed is viewed from the ceiling side of the room. FIG. 19B is a schematic view (side view) of the subject on the bed as viewed from the side of the room. Here, it is assumed that the subject is watching the television 210 placed on the storage stand 205 on the bed 300 in the sitting position or the sitting position.

  The monitoring apparatus 100 is installed on a storage stand 205 near the bed 300. The distance between the bed 300 and the monitoring device 100 is, for example, about several tens of centimeters to about 1.5 m, and the distance between the subject and the monitoring device 100 is also close. Even when the subject is lying on the bed 300, the subject is present on the peak direction line 121. As a result, the movement of the subject lying on the bed 300 in the periphery of the bed 300 can be accurately detected by the area lines 123A and 123B.

  Further, in the example of FIG. 19, when the subject gets up from the bed 300, the subject is present on the peak direction line 121 and the subject approaches from the monitoring device 100 (that is, Approach) is mainly performed. On the other hand, when the subject lies on the bed 300, the subject is present on the peak direction line 121, and the operation (that is, the detachment operation) in which the subject is detached from the monitoring apparatus 100 is mainly performed. I am doing.

  When the subject is a carer, both approaching motion and disengaging motion are detected because the patient lifts up with his hands or lifts with the bedside handrail. Therefore, if the monitoring apparatus 100 determines that the number of approaching movements of the subject is greater than the number of separating actions during the duration of the action, the monitoring apparatus 100 determines that the subject has risen up, and the separating action of the subject If it is determined that the number of times is greater than the number of approaching actions, it may be determined that the subject has been in bed.

  In addition, when the subject approaches the monitoring device 100 in a standing posture, the body motion amplitude and the amplitude ratio increase rapidly. Therefore, the monitoring apparatus 100 may determine that the subject has left the bed when the body movement amplitude (or the amplitude ratio) becomes equal to or greater than a predetermined threshold. If it is determined that the subject has risen, the monitoring apparatus 100 may output, for example, a message such as “Don't get out of bed yet” as warning information.

  In the installation example of the monitoring apparatus 100 shown in FIG. 19, when the body movement speed in the heart rate area is 0 bpm, the body movement speed in the breathing area is 0 bpm, the body movement amplitude is near the threshold Th2, and the amplitude ratio is 1000, It is considered that the subject has left the room.

  In the second embodiment, since the distance between the monitoring apparatus 100 and the subject is short, the amplitude of the heartbeat signal is large, and it is considered that the fundamental frequency can be detected with high accuracy. For example, when another monitoring device 100 is further installed in the vicinity of the entrance 203 as shown in FIG. 4, the two monitoring devices 100 acquire the body movement number in the heart rate region, but in consideration of the accuracy, The heart rate area acquired by the monitoring device 100 installed on the storage stand 205 may be employed.

  According to the second embodiment, it is possible to output warning information when the subject gets up from the bed 300 and performs an operation. The other advantages are the same as in the first embodiment.

Third Embodiment
In the third embodiment, an installation method of the monitoring apparatus 100 different from the first and second embodiments will be described. In the third embodiment, the monitoring device 100 is installed on a cashier in a store (for example, in a convenience store). In particular, at a convenience store in the middle of the night, the clerk is not always on the cash register, and often goes to the cash register when the customer finishes shopping. Therefore, a configuration in which the monitoring device 100 detects a customer heading for the cash register will be described.

  FIG. 20 is a diagram for describing an installation method of the monitoring apparatus 100 according to the third embodiment. Referring to FIG. 20, monitoring apparatus 100 is attached to cash register table 213 on which cash register 212 is placed in store 211. The subject who has finished shopping walks in a standing posture and approaches the cash register 213. The monitoring apparatus 100 detects the approaching motion of the subject, and when the distance to the subject is less than a predetermined distance (for example, when the body movement amplitude becomes equal to or more than a predetermined threshold), the warning information is displayed. It can be output by voice or the like.

  According to the third embodiment, it is possible to detect a subject approaching the cash register 213 in the store and output warning information. The other advantages are the same as in the first embodiment.

[Other Embodiments]
As another embodiment, a program can be provided that causes a computer to function to execute the control as described in the above embodiments. Such a program is recorded as a program product on a non-temporary computer readable recording medium such as a flexible disk attached to a computer, a CD-ROM (Compact Disk Read Only Memory), a ROM, a RAM and a memory card. It can also be provided. Alternatively, the program can be provided by being recorded in a recording medium such as a hard disk built in the computer. Also, the program can be provided by downloading via a network.

  The program may call a required module among program modules provided as a part of an operating system (OS) of a computer in a predetermined arrangement at a predetermined timing to execute processing. In that case, the program itself does not include the above module, and the processing is executed in cooperation with the OS. A program that does not include such a module may also be included in the program according to the present embodiment.

  Also, the program according to the present embodiment may be provided by being incorporated into a part of another program. Also in this case, the program itself does not include a module included in the other program, and the process is executed in cooperation with the other program. Programs incorporated into such other programs may also be included in the program according to the present embodiment.

  Further, the configuration exemplified as the above-described embodiment is an example of the configuration of the present invention, and can be combined with another known technique, and part of the configuration is omitted without departing from the scope of the present invention. For example, it is possible to change and configure.

  Furthermore, in the embodiment described above, the processes and configurations described in the other embodiments may be adopted appropriately and implemented.

  It should be understood that the embodiments disclosed herein are illustrative and non-restrictive in every respect. The scope of the present invention is indicated not by the above description but by the claims, and is intended to include all modifications within the meaning and scope equivalent to the claims.

  Reference Signs List 21 oscillator circuit 22A, 22B, 145A to 145D amplifier, 25 transmitting antenna, 30 receiving antenna, 32I, 32Q mixer, 3890 degree phase shifter, 41 analog signal processing circuit, 43 AD converter, 45 microprocessor, 54 output control Parts, 55 networks, 60 heart rate calculating parts, 66I, 66Q, 72I, 72Q fundamental wave detecting parts, 67 heart rate average processing parts, 70 respiration calculating parts, 73 respiration average processing parts, 80 motion monitoring parts, 81 detecting parts, 82 amplitudes Calculation unit, 83 distance estimation unit, 84 ratio calculation unit, 85 determination unit, 100 monitoring device, 149A to 149D signal processing circuit, 152 control circuit, 154 memory, 156 speaker, 158 communication interface, 160 microwave Doppler sensor, 200 terminal Device, 201, 201b Room, 203 entrance, 205 storage stand, 206 lighting, 210 TV, 212 cash register, 213 cash register, 300 beds, 1000 surveillance system.

Claims (8)

A monitoring apparatus for monitoring a subject, wherein
A receiving unit configured to receive a reflected wave of the microwave irradiated to the subject;
A monitoring unit that monitors an operation of the subject based on a body movement signal related to a body movement of the subject extracted from the signal of the reflected wave;
An output control unit that outputs activity information based on the operation of the subject monitored by the monitoring unit;
The monitoring apparatus includes at least one of an amplitude of the body movement signal, a body movement number within a predetermined period in a low frequency region, and a body movement number within the predetermined period in a high frequency region. The information processing apparatus further includes a storage unit that stores relationship information indicating a relationship between a distance from the monitoring device of the subject and the amplitude of the body movement signal.
The monitoring device according to claim 1, wherein the output control unit outputs the distance based on the relationship information. The body movement frequency within the predetermined period in the low frequency region is a body movement frequency within the predetermined period in a first frequency region including a frequency region corresponding to the respiration of a human body,
The monitoring according to claim 1 or 2, wherein the body movement frequency in the predetermined period in the high frequency region is a body movement number in the predetermined period in a second frequency region including a frequency region corresponding to a heartbeat of a human body. apparatus. And a first signal detection unit that detects a signal of a first fundamental frequency included in the first frequency region from the signal of the reflected wave.
The monitoring unit further calculates a ratio between the amplitude of the signal in the first frequency region and the amplitude of the body movement signal;
When the ratio is less than a predetermined threshold, the output control unit outputs the respiration rate of the subject calculated based on the first fundamental frequency, and the ratio is equal to or more than the predetermined threshold. The monitoring apparatus according to claim 3, wherein the body movement number of the subject in the first frequency region, which is calculated based on the first fundamental frequency, is output. And a second signal extraction unit that extracts a signal of a second fundamental frequency included in the second frequency region from the signal of the reflected wave.
The output control unit outputs the heart rate of the subject calculated based on the second fundamental frequency when the ratio is less than the predetermined threshold, and the ratio is equal to or more than the predetermined threshold. The monitoring device according to claim 4, wherein, in the case, the body movement number of the subject in the second frequency region, which is calculated based on the second fundamental frequency, is output.   The monitoring device according to claim 4 or 5, wherein the activity information further includes the number of times the amplitude of the body movement signal becomes equal to or higher than a reference value within the predetermined period, and the ratio. A signal generator for generating an I channel signal and a Q channel signal orthogonal to each other from the signal of the reflected wave;
And a detection unit that detects an operation of the subject at predetermined time intervals based on the I channel signal and the Q channel signal of the body movement signal.
The action of the subject includes at least one of an approaching action and an leaving action of the subject with respect to the monitoring device,
The detecting unit detects the approaching operation and the separating operation based on how the phases of the I channel signal and the Q channel signal for the body movement signal advance. The monitoring device described in.   The monitoring device according to any one of claims 1 to 7, wherein the output control unit transmits the activity information to an external device configured to be able to communicate with the monitoring device.