JP2010178933A - Physical information measuring device and physical information measuring system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To highly accurately measure physical information of a subject. <P>SOLUTION: This physical information measuring device (U) includes: frequency component intensity computing means (CA3) which computes the intensities of frequency components included in the waveform of the history of a first output signal and the waveform of the history of a second output signal stored in output signal history storage means (CA1); synthesized intensity computing means (CA5) which computes the synthesized intensity of the respective frequency components of the waveform of the history of the first output signal and the waveform of the history of the second output signal; frequency component extraction means (CA6) which extracts a heart rate component based on the synthesized intensity for every frequency component; heart rate computing means (CA7a) which computes the heart rate (h) based on the extracted heart rate component; and physical information image display means (CA11) which displays a physical information image (101) notifying of the heart rate (h). <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a physical information measuring apparatus and a physical information measuring system for measuring a heart rate and a respiratory rate per unit time which are physical information of a subject.

  2. Description of the Related Art Conventionally, a body information measuring apparatus that measures body information such as a heart rate and a respiration rate of a subject such as a human or an animal is known. As a technique related to the physical information measuring device, for example, a technique described in Patent Document 1 below is known.

  Japanese Patent Application Laid-Open No. 2000-102515 as Patent Document 1 discloses a bed (1) as a bedding and a microwave as electromagnetic waves on the chest of a subject lying in the bed (1) and lying on the bed (1). A microwave transmission / reception sensor (11) that receives the reflected electromagnetic wave upon irradiation, that is, the microwave reflected from the subject, and based on the received reflected electromagnetic wave, a body such as a heart rate and a respiratory rate of the subject The technique about the body condition detection tool (10) which detects a state is described. In Patent Document 1, a frequency component of respiration rate is extracted from the reflected electromagnetic wave that is an output waveform using a 0.3 Hz low-pass filter, and a heart rate frequency component is extracted using a 1 Hz high-pass filter. Describes a technique for calculating heart rate and respiratory rate.

That is, in Patent Document 1, the movement of the body of a subject lying down by the bed (1), that is, so-called body movement is reduced and the body state is measured with high accuracy, and the microwave transmission / reception sensor (11) is used. In addition, there is described a technique for easily measuring the physical state of a subject without contact / contact with a contact-type measuring device such as a silver plate electrode, thermistor electrode, piezo element, pressure sensor, or the like.
Patent Document 1 discloses a heart rate / respiration rate monitoring device (15) that constantly monitors a subject's heart rate and respiration rate, with a heart rate of 40 [pieces / minute] or less (bradycardia) or 160 [pieces / piece]. Min] Warning device that emits a warning sound when it is determined that it is above (tachycardia), or when it is determined that the respiratory rate is about 30 seconds to 2 minutes (apnea syndrome). 17) describes a technique for waking up a sleeping subject. In addition, although the specific structure is not shown by patent document 1, it is suggested that it is also possible to detect the body posture of the said test subject.

JP 2000-102515 A (Abstract, “0010” to “0034”, FIGS. 1 to 4)

"Technos Japan Co., Ltd. | Bed Call", "online", September 9, 2003, Technos Japan Co., Ltd., "Search January 16, 2009", Internet <URL: http: // www.technosj.co.jp/alarm/bc.html>

(Problems of conventional technology)
In the measurement by a so-called Doppler type microwave radar such as the microwave transmission / reception sensor (11) for detecting the minute movement of the subject by the reflected wave of the microwave as in the above-mentioned Patent Document 1, The effect of the subject's body movement is increased. Therefore, as in the microwave transmission / reception sensor (11), it is a case where body information can be detected with high accuracy and a wide range, and even when the subject is stationary, a large noise is generated. The output waveform as shown in FIG. 3 is not obtained as expected, noise processing is difficult, and heart rate and respiratory rate are difficult to detect.
Moreover, in the said patent document 1, the said microwave transmission / reception sensor (11) is arrange | positioned only in the position corresponding to the test subject's chest which lies on his back in the center of the said bed (1). Therefore, for example, when a sleeping subject turns over and moves to both left and right ends of the bed (1) and sleeps sideways, the output waveform cannot be received, and the heart rate There was a problem that the respiratory rate could not be detected.

  In view of the above-described circumstances, an object of the present invention is to accurately measure body information of a subject.

In order to solve the technical problem, the physical information measuring device according to claim 1 is provided.
A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a heartbeat component that is the frequency component corresponding to the heartbeat of the subject based on the combined intensity for each frequency component;
Heart rate calculating means for calculating a heart rate per unit time of the subject based on the extracted heart rate component;
A physical information image display means for displaying a physical information image for notifying the calculated heart rate per unit time of the subject;
It is provided with.

The invention according to claim 2 is the physical information measuring device according to claim 1,
The frequency component extraction means for extracting a respiratory component that is the frequency component corresponding to the breathing of the subject based on the combined intensity for each frequency component;
Respiration rate calculating means for calculating the respiration rate per unit time of the subject based on the extracted respiration component;
The physical information image display means for displaying the physical information image for notifying the calculated heart rate and respiratory rate per unit time of the subject;
It is provided with.

In order to solve the technical problem, the physical information measuring device according to claim 3 is provided.
A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a respiratory component that is the frequency component corresponding to the breathing of the subject based on the combined intensity for each frequency component;
Respiration rate calculating means for calculating the respiration rate per unit time of the subject based on the extracted respiration component;
A physical information image display means for displaying a physical information image for notifying the computed respiratory rate per unit time of the subject;
It is provided with.

The invention according to claim 4 is the physical information measuring device according to any one of claims 1 to 3,
The combined intensity calculating means for calculating the combined intensity by calculating a product of intensity of each frequency component of the waveform of the history of the first output signal and the waveform of the history of the second output signal;
It is provided with.

The invention according to claim 5 is the physical information measuring device according to any one of claims 1 to 4,
Of the history waveform of each output signal, frequency component removing means for removing frequency components outside the passband from a preset minimum frequency to a maximum frequency;
The frequency component intensity calculating means for calculating the intensity of each frequency component in the passband;
It is provided with.

The invention according to claim 6 is the physical information measuring device according to claim 5,
A heartbeat frequency component removing means for removing a frequency component outside the heartbeat passband from a preset heartbeat minimum frequency to a heartbeat maximum frequency in the history waveform of each output signal;
Breathing frequency component removing means for removing a frequency component outside a breathing passband from a preset breathing minimum frequency to a breathing maximum frequency in a history waveform of each output signal;
The frequency component intensity calculating means for calculating the intensity of each frequency component in the heartbeat passband and calculating the intensity of each frequency component in the breathing passband;
Of the frequency components of the history waveform of the first output signal and the history waveform of the second output signal, the combined intensity for heartbeats obtained by combining the intensities of the frequency components in the passband for heartbeats is the frequency. The combined intensity calculating means for calculating for each frequency component, calculating for each frequency component, calculating for each component, and calculating for each frequency component a combined intensity for respiration in which the intensity of each frequency component in the respiration passband is combined.
The frequency component extracting means for extracting the heartbeat component based on the heartbeat synthetic intensity and extracting the respiratory component based on the respiratory synthetic intensity;
It is provided with.

The invention described in claim 7 is the physical information measuring device according to any one of claims 1 to 6,
An object detection member for detecting the object on the bed;
When the subject detection member detects the subject and the heart rate or respiratory rate per unit time of the subject is calculated, it is determined that the subject is lying on the bed. Floor discrimination means;
When the subject detection member does not detect the subject and the heart rate and respiration rate per unit time of the subject are not calculated, it is determined that the subject is separated from the bed. Leaving bed discrimination means;
When it is determined that the subject is separated from the bed, a bed leaving notification means for notifying that the subject is separated from the bed;
It is provided with.

The invention according to claim 8 is the physical information measuring device according to claim 7,
A bed leaving time measuring means for measuring a bed leaving time which is an elapsed time since it was determined that the subject has left the bed;
A long-term bed leaving judging means for judging that the subject is separated from the bed for a long time when the bed leaving time during timing exceeds a preset bed leaving threshold;
When it is determined that the subject is away from the bed for a long time, long-term bed notification means for notifying that the subject is away from the bed for a long time;
It is provided with.

The invention described in claim 9 is the physical information measuring device according to claim 7 or 8,
When the subject detection member detects the subject and the heart rate per unit time of the subject is outside the normal heart rate range from a preset minimum heart rate to a maximum heart rate, A heartbeat abnormality determining means for determining that the heartbeat of the subject is in an abnormal state;
A heartbeat abnormality notification means for notifying that the heartbeat of the subject is in an abnormal state when it is determined that the heartbeat of the subject is in an abnormal state;
It is provided with.

The invention according to claim 10 is the physical information measuring device according to any one of claims 7 to 9,
When the subject detection member detects the subject, and the respiratory rate per unit time of the subject is outside a normal breathing range from a preset minimum respiratory rate to a maximum respiratory rate, Breathing abnormality determining means for determining that the subject's breathing is in an abnormal state;
A breathing abnormality notification means for notifying that the subject's breathing is in an abnormal state when it is determined that the subject's breathing is in an abnormal state;
It is provided with.

The invention according to claim 11 is the physical information measuring device according to any one of claims 7 to 10,
An apnea discrimination means for discriminating that the subject is in an apnea state when the subject detection member detects the subject and the respiration rate per unit time of the subject is not calculated; ,
An apnea time measuring means for measuring an apnea time which is an elapsed time since it is determined that the subject is in an apnea state;
Long-term apnea discrimination means for discriminating that the subject is in an apnea state for a long time when the apnea time during timing exceeds a preset threshold for apnea discrimination;
Long-term apnea notification means for notifying that the subject is in a long-term apnea state when it is determined that the subject is in a long-term apnea state;
It is provided with.

The invention according to claim 12 is the physical information measuring device according to any one of claims 7 to 11,
Of the frequency components of the history waveform of the first output signal and the history waveform of the second output signal, the frequency components other than the heartbeat component and the respiratory component, and the body motion of the subject. The frequency component extracting means for extracting the body motion component which is the corresponding frequency component;
The strength of the body motion component included in the history waveform of the first output signal or the strength of the body motion component included in the history waveform of the second output signal is set to a preset threshold for turning determination. When it exceeds, the turning determination means for determining that the subject has turned over,
When it is determined that the subject has turned over, the bed notifying means for notifying that the subject has turned over; and
It is provided with.

The invention according to claim 13 is the physical information measuring device according to claim 12,
A non-sleep time measuring means for measuring a non-sleep time which is an elapsed time since it was determined that the subject has turned over;
Long-term non-sleep determination means for determining that the subject has not turned over for a long period of time when the non-sleep time exceeds a preset non-sleep determination threshold,
When it is determined that the subject has not turned over for a long time, a long-term non-sleeping notification means for notifying that the subject has not turned over for a long time;
It is provided with.

In order to solve the technical problem, the body information measuring system according to claim 14 is provided.
A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a heartbeat component that is the frequency component corresponding to the heartbeat of the subject based on the combined intensity for each frequency component;
Heart rate calculating means for calculating a heart rate per unit time of the subject based on the extracted heart rate component;
A physical information image display means for displaying a physical information image for notifying the calculated heart rate per unit time of the subject;
It is provided with.

In order to solve the technical problem, the body information measuring system according to claim 15 is characterized in that:
A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a respiratory component that is the frequency component corresponding to the breathing of the subject based on the combined intensity for each frequency component;
Respiration rate calculating means for calculating the respiration rate per unit time of the subject based on the extracted respiration component;
A physical information image display means for displaying a physical information image for notifying the computed respiratory rate per unit time of the subject;
It is provided with.

According to invention of Claim 1 and 15, by calculating the said synthetic | combination intensity | strength for every said frequency component, compared with the synthetic | combination intensity | strength of the said heart rate component and the said respiratory component, frequencies other than the said heart rate component and the said respiratory component Compared to the case without the configuration of the present invention, the heart rate, which is the physical information of the subject, can be measured with high accuracy since the combined intensity of the components becomes relatively small and the accurate heart rate component is easily extracted. Can do.
According to invention of Claim 2, 3, and 16, by calculating the said synthetic | combination intensity | strength for every said frequency component, compared with the synthetic | combination intensity | strength of the said heart rate component and the said respiratory component, except the said heart rate component and the said respiratory component Compared to the case without the configuration of the present invention, the respiration rate, which is the physical information of the subject, can be measured with high accuracy, since the combined intensity of the frequency components of the relative frequency becomes relatively small and the accurate respiration component is easily extracted. can do.

According to the fourth aspect of the present invention, the combined intensity for each frequency component can be calculated by calculating the product of the intensities of the frequency components. According to the second aspect of the present invention, compared to the combined intensity of the heartbeat component and the respiratory component, the combined intensity of frequency components other than the heartbeat component and the respiratory component tends to be relatively small and accurate. Since the heart rate component and the respiratory component are easily extracted, the heart rate and the respiratory rate, which are the body information of the subject, can be measured with higher accuracy than when the configuration of the present invention is not provided.
According to the fifth aspect of the present invention, noise outside the passband is removed based on the combined intensity by removing frequency components outside the passband, and the heartbeat component and the respiratory component are accurate. Therefore, the heart rate and the respiration rate, which are the body information of the subject, can be measured with higher accuracy than when the configuration of the present invention is not provided.

According to the sixth aspect of the present invention, noise outside the passband for heartbeats is removed based on the combined intensity for heartbeat by removing frequency components outside the passband for heartbeats. It is easy to extract a heartbeat component, and by removing a frequency component outside the passband for respiration, noise outside the passband for respiration is removed based on the combined intensity for respiration, and the accurate respiration component Therefore, the heart rate and the respiration rate, which are the body information of the subject, can be measured with higher accuracy than when the configuration of the present invention is not provided.
According to the seventh aspect of the present invention, the intensity of each frequency component included in the waveform of the history of each output signal is normalized so that the heart rate component is more accurate than when the configuration of the present invention is not provided. Further, the respiratory component can be easily extracted, and the heart rate and the respiratory rate, which are body information of the subject, can be measured with high accuracy.

According to the invention described in claim 8, based on the detection result of the subject detection member and the calculation results of the heart rate and the respiratory rate, the subject lies on the bed or the subject is You can check if you are away from the bed, and if necessary, you can go to find the subject.
According to the ninth aspect of the present invention, it can be confirmed that the subject is away from the bed for a long period of time based on the detection result of the subject detection member and the calculation results of the heart rate and the respiratory rate. It is possible to go to find out whether the subject who needs monitoring, nursing care, care or the like is going out or trapped, or to check the safety of the subject.
According to the invention described in claim 10, it is possible to confirm that the life support of the subject is in a dangerous state based on the detection result of the subject detection member and the calculation result of the heart rate, and the subject It is possible to rush to confirm the safety of the specimen or to promptly perform medical practice.
According to the eleventh aspect of the present invention, it is possible to confirm that the life support of the subject is in a dangerous state based on the detection result of the subject detection member and the calculation result of the respiration rate, and the subject It is possible to rush to confirm the safety of the specimen or to promptly perform medical practice.

According to the invention of claim 12, it can be confirmed that the subject is in a dangerous state such as sleep apnea syndrome. For example, the subject can rush to confirm the safety of the subject, It is also possible to wake up and encourage direct breathing, or to adjust the posture of the subject to make it easy to breathe and indirectly encourage breathing. In addition, for example, for the treatment of sleep apnea syndrome, the history of the respiratory rate of the subject can be recorded and used for a severe examination of symptoms, or the examination result can be used for treatment. .
According to the invention described in claim 13, it is possible to confirm that the subject has turned over based on the intensity of the body movement component, for example, a survey record of the subject ecology being monitored or observed, etc. It can be performed.
According to the invention of claim 14, based on the strength of the body motion component, it can be confirmed that the subject has not been turned over for a long period of time, for example, to encourage the subject to turn over, You can help to turn over.

FIG. 1 is an overall explanatory view of a body information measuring system according to a first embodiment of the present invention. FIG. 2 is an explanatory diagram of the first microwave radar, the second microwave radar, and the bed sensor according to the first embodiment of the present invention, FIG. 2A is an enlarged explanatory diagram when the mattress is viewed from below, and FIG. FIG. 2B is an enlarged explanatory diagram when FIG. 2A is viewed from an arrow IIB. FIG. 3 is an explanatory diagram showing the function of each device constituting the body information measuring system according to the first embodiment of the present invention in a block diagram (functional block diagram). FIG. 4 is a block diagram continued from FIG. FIG. 5 is an explanatory diagram of a physical information image according to the first embodiment of the present invention. 6 is an explanatory diagram of each notification image according to the first embodiment of the present invention, FIG. 6A is an explanatory diagram of a bed leaving notification image, FIG. 6B is an explanatory diagram of a long-term bed leaving notification image, and FIG. 6C is a heartbeat abnormality notification. 6D is an explanatory diagram of a respiratory abnormality notification image, FIG. 6E is an explanatory diagram of a long-term apnea notification image, FIG. 6F is an explanatory diagram of a sleep notification image, and FIG. It is explanatory drawing of a non-sleeping notification image. FIG. 7 is a flowchart of physical information measurement of the physical information measurement program AP1 according to the first embodiment. FIG. 8 is a flowchart of the abnormal heart rate notification process of the physical information measurement program AP1 of the first embodiment, and is an explanatory diagram of the subroutine of ST16 of FIG. FIG. 9 is a flowchart of the respiratory abnormality notification process of the physical information measurement program AP1 of Example 1, and is an explanatory diagram of the subroutine of ST17 of FIG. FIG. 10 is a flowchart of the sleep notification process of the physical information measurement program AP1 according to the first embodiment, and is an explanatory diagram of the subroutine of ST18 of FIG. FIG. 11 is an explanatory diagram of measurement results obtained by the sensors of Experimental Example 1 and Comparative Example 1, and is an explanatory diagram of a waveform graph in which the vertical axis indicates amplitude [V] and the horizontal axis indicates time [sec]. FIG. 11A shows an output waveform relating to the heartbeat of the subject when the waveform of each output signal of each microwave radar in Experimental Example 1 and the output waveform of the electrocardiogram in Comparative Example 1 are passed through a high-pass filter of 0.5 Hz. FIG. 11B is a diagram illustrating a history waveform of each output signal of each microwave radar of Experimental Example 1 and an output waveform of the respiratory sensor of Comparative Example 1 when passing through a 0.05 Hz high-pass filter. It is explanatory drawing of the output waveform regarding the respiration of a test substance. FIG. 12 is an explanatory diagram of the removal result by band-pass filtering for the measurement results of Experimental Example 1 and Comparative Example 1. FIG. 12A shows the output waveform of FIG. 11A in the passband for heartbeat (0.5 to 3.0 [Hz]. ]) Is an explanatory diagram of each heartbeat passband waveform from which the external frequency components have been removed, and FIG. 12B shows each output waveform in FIG. 11B outside the breathing passband (0.05 to 0.5 [Hz]). It is explanatory drawing of each pass band waveform for respiration from which the frequency component was removed. FIG. 13 is an explanatory diagram of the removal result by band-pass filtering for the measurement results of Experimental Example 1 and Comparative Example 1. FIG. 13A shows the passband waveforms for heartbeats of FIG. 12A displayed at intervals of 30 seconds at intervals of 5 seconds. FIG. 13B is an enlarged explanatory diagram in which each respiratory passband waveform of FIG. 12B displayed at intervals of 30 seconds is displayed at intervals of 5 seconds. FIG. 14 is an explanatory diagram of calculation results by fast Fourier transform on the removal results of Experimental Example 1 and Comparative Example 1, and an explanatory diagram of a graph of a spectrum waveform in which the vertical axis indicates intensity and the horizontal axis indicates frequency [Hz]. 14A is an explanatory view of a spectrum waveform obtained by fast Fourier transforming each heartbeat passband waveform of FIGS. 12A and 13A, and FIG. 14B is a diagram of each respiratory passband waveform of FIGS. 12B and 13B being fast Fourier transformed. It is explanatory drawing of the converted spectrum waveform. FIG. 15 is an explanatory diagram of the calculation result of the combined intensity (the product of each normalized intensity) with respect to the calculation result of Experimental Example 1. The vertical axis indicates the ratio [%] to the total combined intensity, and the horizontal axis indicates the body information. It is explanatory drawing of the graph of the spectrum waveform which took (heart rate h [bpm], respiration rate r [bpm]), and FIG. 15A is the synthetic | combination intensity | strength for every frequency component contained in each passband waveform for heartbeats of FIG. 14A. FIG. 15B is an explanatory view of the spectrum waveform of the combined intensity for each frequency component included in each respiratory passband waveform of FIG. 14B.

Next, specific examples of embodiments of the present invention (hereinafter referred to as examples) will be described with reference to the drawings, but the present invention is not limited to the following examples.
In the following description using the drawings, illustrations other than members necessary for the description are omitted as appropriate for easy understanding.

FIG. 1 is an overall explanatory view of a body information measuring system according to Embodiment 1 of the present invention.
FIG. 2 is an explanatory diagram of the first microwave radar, the second microwave radar, and the bed sensor according to the first embodiment of the present invention, FIG. 2A is an enlarged explanatory diagram when the mattress is viewed from below, and FIG. FIG. 2B is an enlarged explanatory diagram when FIG. 2A is viewed from an arrow IIB.
1 and 2, the body information measuring system S according to the first embodiment of the present invention includes a bed (bed) 1 on which a human (subject, subject) lies as an example of a subject. The bed 1 includes a mattress support 1a as a bed body and a mattress 1b supported by the mattress support 1a. The mattress 1b according to the first embodiment is configured by a so-called air mattress (air mat, air bed) in which air is enclosed. The mattress 1b of the first embodiment is designed in a so-called single size, and the width L1 is 980 [mm], the length L2 is 1950 [mm], and the height L3 is 275 [mm]. It is set in advance.

  Further, on the lower surface of the mattress 1b, a first microwave radar (first electromagnetic wave transmission / reception member, first radar antenna) SN1 that transmits and receives microwaves (electromagnetic waves) and a second microwave radar (second electromagnetic wave transmission / reception member, The second radar antenna SN2 is supported. The first microwave radar SN1 according to the first embodiment is a first microwave irradiation unit (first electromagnetic wave irradiation unit) that irradiates a first microwave (first electromagnetic wave) upward as shown in FIG. SN1a and a first microwave receiving unit (first electromagnetic wave receiving unit) SN1b that receives the first microwave reflected from the subject on the mattress 1b, that is, the reflected wave. Similarly, for the second microwave radar SN2 of the first embodiment, as shown in FIG. 3 to be described later, a second microwave irradiation unit (second microwave irradiation unit) that irradiates the second microwave (second electromagnetic wave) upward. 2 electromagnetic wave irradiation part) SN2a and 2nd microwave receiving part (2nd electromagnetic wave receiving part) SN2b which receives the reflected wave from the said test object.

  In the first embodiment, the microwave radars SN1 and SN2 are installed in advance at positions where the left and right sides of the chest can be measured with the subject on the mattress 1b facing up. That is, in the first microwave radar SN1 of the first embodiment, the length L4 to the upper end of the mattress 1b is 650 [mm], and the width L5 to the left end (right end in FIG. 2) is about 330 [mm]. It is installed in advance at a first measurement position that is only a distance. The second microwave radar SN2 has a length L4 (L4 = 650 [mm]) to the upper end of the mattress 1b and a width L6 to the right end (left end in FIG. 2) separated by about 330 [mm]. The second measurement position is set in advance. That is, the microwave radars SN1 and SN2 of the first embodiment are spaced L7 between the microwave radars SN1 and SN2 in the width direction of the mattress 1b (L7 = 980−330 × 2≈320 [mm]). And the widths L5 and L6 (L5 = L6≈330 [mm]) to the left and right ends of the mattress 1b are set in advance so as to be substantially equidistant (L5 = L6≈L7).

In Example 1, the irradiation angle α in the width direction of the subject irradiated with the microwaves from the microwave irradiation units SN1a and SN2a is preset to about 40 °. Therefore, in the first embodiment, the radius r1 (r1 = L3 × tan (α / 2) ≈275 × tan20 ° ≈100 [mm]) from the position corresponding to each measurement position on the upper surface of the mattress 1b. In addition, the measurement areas A1 and A2 of the microwave radars SN1 and SN2 are set in advance.
In addition, the frequency of each microwave according to the first embodiment is open to the public and does not require a specific license, and passes through the outer surface of the mattress 1b, the clothes of the subject, and the like. It is desirable to employ a frequency that can be transmitted to the body surface of the specimen and can receive a reflected wave from the subject. Specifically, the frequency of the first microwave is preset as 24.15 [GHz], and the frequency of the second microwave is preset as 24.19 [GHz]. The mattress 1b is also free from coil springs or the like that may adversely affect microwave transmission / reception, and is preferably, for example, a low-resilience mattress made of urethane or the air mattress. For this reason, the mattress 1b according to the first embodiment is configured by the air mattress having a hollow inside.

  Further, an object detection member SN3 for detecting the object lying on the mattress 1b is supported on the upper surface of the mattress 1b. The subject detection member SN3 of Example 1 is a sheet-like sensor that detects whether or not the subject is separated from the bed 1 based on the weight (weight) of the subject, a so-called bed sensor ( It is comprised by the heel sensor. In addition, about the said bed leaving sensor, it is possible to use the well-known product described in the nonpatent literature 1, etc., for example.

In FIG. 1, the body information measurement system S of the first embodiment is a measurement client personal computer (body) as a terminal operable by a user to which the microwave radars SN1 and SN2 and the subject detection member SN3 are connected. (Information measuring device main body, personal computer) PCa. The physical information measuring system S is a receiving client personal computer capable of receiving information from the measuring client personal computer PCa via a wired LAN (Local Area Network) 2 as an example of an information communication line. PCb (receiving terminal, personal computer). Each of the client personal computers PCa and PCb of the first embodiment is configured by a so-called computer device, and includes a computer main body H1, a display H2, input devices such as a keyboard H3 and a mouse H4, and an HD drive (hard disk drive) not shown. Etc.
The bed 1, the sensors SN <b> 1 to SN <b> 3, and the measurement client personal computer PCa constitute a body information measuring device U of Example 1.

(Description of the control part of Example 1)
FIG. 3 is an explanatory diagram showing the function of each device constituting the body information measuring system according to the first embodiment of the present invention in a block diagram (functional block diagram).
FIG. 4 is a block diagram continued from FIG.
In FIG. 3, the computer main body H1 of each of the client personal computers PCa and PCb performs I / O (input / output interface) for performing input / output of signals to / from the outside, adjustment of input / output signal levels, and the like and necessary startup processing. ROM (read-only memory, recording medium) in which programs and data are stored, RAM (random access memory, recording medium) for temporarily storing necessary data and programs, and startup programs stored in ROM, etc. CPU (Central Processing Unit) that performs processing according to the above, a clock oscillator, and the like, and various functions can be realized by executing programs stored in ROM, RAM, and the like.
Each client personal computer PCa, PCb having the above configuration can realize various functions by executing a program stored in the hard disk, ROM, or the like.

(Signal input element connected to the control unit of the computer main body H1 of the measurement client personal computer PCa)
Output signals from the following signal output elements SN1 to SN3 are input to the control unit of the computer main body H1 of the measurement client personal computer PCa.
SN1: First microwave radar The first microwave radar SN1 irradiates the first measurement region A1 with the first microwave from the first microwave irradiation unit SN1a and from the subject in the first measurement region A1. Is received by the first microwave receiving unit SN1b, and a first output signal is input to the control unit in accordance with the received reflected wave.
SN2: Second microwave radar The second microwave radar SN2 irradiates the second measurement region A2 with the second microwave from the second microwave irradiation unit SN2a and from the subject in the second measurement region A2. Is received by the second microwave receiving unit SN2b, and the second output signal is input to the control unit in accordance with the received reflected wave.
SN3: Subject Detection Member The subject detection member SN3 detects whether or not the subject is lying on the mattress 1b based on the weight (weight) of the subject, and inputs the detection signal to the control unit.
(Description of the control unit of the computer main body H1 of the measurement client personal computer PCa)
The hard disk drive of the measurement client personal computer PCa has a basic software (operating system) OS for controlling the basic operation of the measurement client personal computer PCa, a physical information measurement program AP1 as an application program, a physical information notification program AP2, and the like. Software (not shown) is stored.

(Physical information measurement program AP1)
The physical information measurement program AP1 has the following functional means (program module).
CA1: Output signal history storage means The output signal history storage means CA1 includes a history of the first output signal output from the first microwave radar SN1, and a history of the second output signal output from the second microwave radar SN2. Remember. In the first embodiment, the history of each output signal is a waveform of a measurement result by a so-called Doppler type microwave radar, similar to the above-mentioned Patent Document 1, and a microwave is transmitted along with heartbeat and respiration. When the subject to be reflected moves finely, a waveform is obtained by plotting output values corresponding to the difference value of the frequency based on the Doppler effect in which the frequency of the reflected wave changes with respect to the frequency of the transmitted wave. .

CA2: Frequency component removal means The frequency component removal means CA2 has a heartbeat frequency component removal means CA2a and a breathing frequency component removal means CA2b, and the history of each output signal stored in the output signal history storage means CA1. In this waveform, so-called filtering (band-pass filtering) is performed to remove frequency components outside the passband from the preset minimum frequency to the maximum frequency.
CA2a: Heartbeat frequency component removing means The heartbeat frequency component removing means CA2a is located outside the passband for heartbeats from the preset minimum heartbeat frequency to the maximum heartbeat frequency in the waveform of the history of each output signal. Remove frequency components. In Example 1, 0.5 [Hz] is preset as the minimum heartbeat frequency and 3.0 [Hz] is preset as the maximum heartbeat frequency as the heartbeat passband.

CA2b: Respiratory frequency component removing means Respiratory frequency component removing means CA2b is located outside the respiratory passband from the preset minimum respiratory frequency to the maximum respiratory frequency in the waveform of the history of each output signal. Remove frequency components. In the first embodiment, 0.05 [Hz] is set in advance as the minimum frequency for respiration and 0.5 [Hz] is set as the maximum frequency for respiration as the passband for respiration.
That is, the frequency component removing unit CA2 according to the first embodiment uses the heartbeat frequency component removing unit CA2a to set the heartbeat passband (0.5 to 3.0 [Hz]) for the history waveform of the first output signal. The first passband waveform for heartbeat that has passed and the first passband waveform for respiration that has passed through the respiration passband (0.05 to 0.5 [Hz]) are generated by the respiration frequency component removing means CA2b. In addition, the frequency component removing unit CA2 of the first embodiment similarly applies to the history waveform of the second output signal, the second heartbeat passband waveform that has passed through the breathing passband by the heartbeat frequency component removing unit CA2a. And a second respiratory passband waveform that has passed through the respiratory passband is generated by the respiratory frequency component removing means CA2b.

CA3: Frequency component intensity calculation means The frequency component intensity calculation means CA3 calculates the intensity of the frequency component included in the waveform of the history of each output signal stored in the output signal history storage means CA1 for each frequency component. The frequency component intensity calculating means CA3 according to the first embodiment can perform fast Fourier transform (FFT) capable of calculating at high speed which frequency component is included in the history waveform of each output signal. Accordingly, the first heartbeat passband waveform, the first breathing passband waveform, and the second heartbeat passband waveform from which frequency components outside the respective passbands have been removed by the frequency component removing means CA2; The intensity of each frequency component is calculated for each of the second respiratory passband waveforms. The technique relating to frequency analysis using the fast Fourier transform is described in, for example, Japanese Patent Application Laid-Open No. 2001-257611, Japanese Patent Application Laid-Open No. 2006-258786, and the like, and is not described in detail. To do.

CA4: Intensity normalizing means The intensity normalizing means CA4 normalizes the intensity of each frequency component included in each passband waveform calculated by the frequency component intensity calculating means CA3. The intensity normalizing means CA4 according to the first embodiment can compare the intensity of each frequency component included in the first heartbeat passband waveform with the intensity of each frequency component included in the second heartbeat passband waveform. And normalizing the intensity of each frequency component included in the first respiratory passband waveform to a value that can be compared with the intensity of each frequency component included in the second respiratory passband waveform. Execute. Specifically, the intensity ratio (rate, ratio, composition ratio, composition ratio) of each frequency component when the total value (total intensity) of all the frequency components included in each passband waveform is 1. The intensity of each frequency component included in each passband waveform is normalized by calculating and setting each ratio as the intensity value of each frequency component.

CA5: Combined intensity calculating means The combined intensity calculating means CA5 has a combined intensity calculating means CA5a for heart rate and a combined intensity calculating means CA5b for respiration, and the output signal calculated by the frequency component intensity calculating means CA3. A combined intensity obtained by combining the intensity of each frequency component of the history waveform is calculated for each frequency component.
CA5a: Heart rate composite intensity calculating means CA5a is an intensity of each frequency component included in the first heartbeat passband waveform normalized by the intensity normalizing means CA4, and each frequency. By calculating the product of the intensity of each frequency component included in the second heartbeat passband waveform corresponding to the component, the combined intensity for heartbeats, which is the combined intensity for each frequency component of each heartbeat passband waveform, is obtained. Calculate.
CA5b: Respiratory synthetic intensity calculating means Respiratory synthetic intensity calculating means CA5b includes the intensity of each frequency component included in the first respiratory passband waveform and the second respiratory passband waveform corresponding to each frequency component. By calculating the product of the intensities of the respective frequency components included in the above, the combined intensity for respiration, which is the combined intensity for each frequency component of each of the respiratory passband waveforms, is calculated.

CA6: Frequency component extraction means The frequency component extraction means CA6 has a heartbeat component extraction means CA6a, a respiratory component extraction means CA6b, and a body motion component extraction means CA6c, and the frequency calculated by the combined intensity calculation means CA5. Based on the combined intensity for each component, the heart rate component that is the frequency component corresponding to the heartbeat of the subject, the respiratory component that is the frequency component corresponding to the breathing of the subject, the heartbeat component and the respiratory component And the body motion component that is the frequency component corresponding to the body motion of the subject.

CA6a: Heartbeat component extracting means Heartbeat component extracting means CA6a extracts the heartbeat component based on the combined intensity for heartbeat. The heartbeat component extracting means CA6a according to the first embodiment extracts a frequency component having the maximum heartbeat synthetic intensity, that is, a so-called peak frequency component as the heartbeat component.
CA6b: Respiratory component extracting means Respiratory component extracting means CA6b extracts the respiratory component based on the combined intensity for respiration. The respiratory component extraction means CA6b of Embodiment 1 extracts a frequency component having a peak frequency that maximizes the combined intensity for respiration as the respiratory component.
CA6c: Body motion component extracting means The body motion component extracting means CA6c extracts the body motion components other than the heart rate component and the respiratory component based on the combined heart rate intensity and the combined respiratory intensity. The respiratory component extraction means CA6b of Embodiment 1 extracts each frequency component having the second highest combined intensity for heartbeat or the combined intensity for breathing as the body movement component.

CA7: Physical information calculation means The physical information calculation means C7 is based on the heart rate component extracted by the heart rate component extraction means CA6a, and the heart rate per unit time of the subject [bpm: beats per minute, times / minute. ] Heart rate calculating means CA7a for calculating the respiratory rate [bpm] per unit time of the subject based on the respiratory component extracted by the respiratory component extracting means CA6b, The heart rate [bpm] and the respiration rate [bpm], which are the body information of the subject, are calculated. In the body information calculation unit C7 of the first embodiment, the frequency of the heartbeat component is f _h [Hz], the frequency of the respiratory component is f _r [Hz], and the heart rate is h [bpm], When the respiration rate is r [bpm], the heart rate h [bpm] and the respiration rate r [bpm] are calculated by the following equations (1-1) and (1-2).

h = f _h × 60 (1-1)
r = f _r × 60 (1-2)
That is, in Example 1, the heart rate h [bpm] within the heartbeat passband (0.5 to 3.0 [Hz]) is 30 to 180 [bpm] according to the equation (1-1). I understand that. Moreover, it turns out that the respiration rate r [bpm] in the passband for respiration (0.05-0.5 [Hz]) is 3-30 [bpm] by said Formula (1-1).

CA8: Physical information storage means The physical information storage means CA8 stores the heart rate h [bpm] and the respiratory rate r [bpm], which are physical information of the subject calculated by the physical information calculation means C7.
CA9: Physical information measurement discriminating means The physical information measurement discriminating means CA9 has a measuring timer (measurement time measuring means) TM for measuring the measurement interval (measurement time), and stores the history waveform of each output signal. It is determined whether or not each measurement interval for measuring the body information of the subject has been timed.

(Physical information notification program AP2)
The physical information notification program AP2 has the following functional means (program module).
CA10: Physical information transmitting means Physical information transmitting means CA10 is the heart information which is the physical information of the subject stored in the physical information storage means CA8 with respect to the physical information receiving means CB10 of the receiving client personal computer PCb described later. The number h [bpm] and the respiration rate r [bpm] are transmitted.

FIG. 5 is an explanatory diagram of a physical information image according to the first embodiment of the present invention.
CA11: physical information image display means The physical information image display means CA11 is the physical rate information of the subject calculated by the physical information calculation means C7 shown in FIG. The physical information image 101 that announces [bpm] is displayed on the display H2.
CA12: Bed determination means The bed determination means CA12 determines whether or not the subject is lying on the mattress 1b. The bed determination unit CA12 according to the first embodiment is configured when the subject detection member SN3 detects the subject and the heart rate h [bpm] or the respiration rate r [bpm] is calculated. It is determined that the subject is lying on the mattress 1b.

CA13: Bed leaving determination means The bed leaving determination means CA13 determines whether the subject has left the bed 1 or not. In the bed leaving determination unit CA13 according to the first embodiment, the subject detection member SN3 does not detect the subject, and the heart rate h [bpm] and the respiration rate r [bpm] are both calculated. If not, it is determined that the subject has left the bed 1.
CA14: Get-off notification means The get-off notice means CA14 has a get-off notice information transmission means CA14a and a get-off notice image display means CA14b. In addition, the fact that the subject has left the bed 1 is notified.
CA14a: Get-off notice information sending means The get-off notice information sending means CA 14a gives the get-off notice information for notifying the get-off notice information receiving means CB 14a of the receiving client personal computer PCb described later that the subject has left the bed 1. Send.

6 is an explanatory diagram of each notification image according to the first embodiment of the present invention, FIG. 6A is an explanatory diagram of a bed leaving notification image, FIG. 6B is an explanatory diagram of a long-term bed leaving notification image, and FIG. 6C is a heartbeat abnormality notification. FIG. 6D is an explanatory diagram of a respiratory abnormality notification image, FIG. 6E is an explanatory diagram of a long-term apnea notification image, FIG. 6F is an explanatory diagram of a sleep notification image, and FIG. It is explanatory drawing of a non-sleeping notification image.
CA14b: Get-off notification image display means The get-off notice image display means CA14b displays a get-off notice image 102 showing the get-off notice information shown in FIG. 6A on the display H2.
CA15: bed leaving time measuring means The bed leaving time measuring means CA15 has a bed leaving timer TM ′ for measuring a bed leaving time which is an elapsed time since it is determined that the subject has left the bed 1, and a bed leaving timer TM ′. To measure the bed leaving time.

CA16: Long-term bed leaving distinguishing means The long-term bed leaving judging means CA16 determines whether or not the subject is away from the bed 1 for a long time. The long-term bed leaving determination unit CA16 according to the first embodiment is configured such that when the bed leaving time during timing exceeds a preset bed detection threshold value by the bed leaving time measuring unit CA15, the subject moves from the bed 1 for a long time. Determine that you are away.
CA17: Long-term bed leaving notice means Long-term bed leaving notice means CA17 has long-term bed leaving notice information sending means CA17a and long-term bed leaving notice image display means CA17b. When it is determined that the subject is away from the period, the subject is informed that the subject has been away from the bed 1 for a long period of time.
CA17a: Long-term bed announcement information transmitting means Long-term bed announcement information transmitting means CA17a indicates that the subject has been separated from the bed 1 for a long time with respect to long-term bed announcement information receiving means CB17a of the receiving client personal computer PCb described later. Send long-term bed announcement information to be notified.

CA17b: Long-term bed announcement image display means The long-term bed announcement image display means CA17b displays the long-term bed announcement image 103 showing the long-term bed announcement information shown in FIG. 6B on the display H2.
CA18: Heartbeat abnormality determining means The heartbeat abnormality determining means CA18 determines whether or not the subject's heartbeat is in an abnormal state. In the heartbeat abnormality determining means CA18 according to the first embodiment, the subject detection member SN3 detects the subject and the heart rate h [bpm] is a preset heart rate from a minimum heart rate to a maximum heart rate. When it is outside the normal range for use, it is determined that the heartbeat of the subject is in an abnormal state. In Example 1, the minimum heart rate of the normal heart rate range is preset to 40 [bpm], the maximum heart rate is set to 100 [bpm], and the normal heart rate range is 40 to 100 [bpm]. bpm]. Therefore, when the heart rate h [bpm] is less than 40 [bpm], it is determined as bradycardia, and when it is greater than 100 [bpm], it is determined as tachycardia.

CA19: Heartbeat abnormality notification means The heartbeat abnormality notification means CA19 has a heartbeat abnormality notification information transmission means CA19a and a heartbeat abnormality notification image display means CA19b, and the heartbeat abnormality determination means CA18 makes the heartbeat of the subject abnormal. If it is determined that the subject is in a state, the subject is informed that the heartbeat of the subject is abnormal.
CA19a: Heartbeat abnormality notification information transmission means The heartbeat abnormality notification information transmission means CA19a notifies the heartbeat abnormality notification information reception means CB19a of the receiving client personal computer PCb described later that the heartbeat of the subject is abnormal. Send heart rate abnormality notification information.

CA19b: Heartbeat abnormality notification image display means The heartbeat abnormality notification image display means CA19b displays the heartbeat abnormality notification image 104 indicating the heartbeat abnormality notification information shown in FIG. 6C on the display H2.
CA20: Respiratory abnormality determining means Respiratory abnormality determining means CA20 determines whether or not the subject's respiration is in an abnormal state. In the respiratory abnormality determining means CA20 according to the first embodiment, the subject detection member SN3 detects the subject, and the respiratory rate r [bpm] is preset from the minimum respiratory rate to the maximum respiratory rate. If the subject is out of the normal range, it is determined that the subject's breathing is in an abnormal state. In Example 1, the minimum respiratory rate of the normal breathing range is preset to 10 [bpm], the maximum respiratory rate is set to 25 [bpm], and the normal breathing range is 10 to 25 [bpm]. bpm]. Therefore, when the respiration rate r [bpm] is smaller than 10 [bpm], it is determined as slow breathing, and when it is larger than 25 [bpm], it is determined as tachyrespiration.

CA21: Respiratory abnormality notification means Respiratory abnormality notification means CA21 has a respiratory abnormality notification information transmission means CA21a and a respiratory abnormality notification image display means CA21b, and the respiratory abnormality determination means CA20 causes abnormal breathing of the subject. When it is determined that the subject is in a state, the fact that the subject's breathing is in an abnormal state is notified.
CA21a: Respiratory abnormality notification information transmitting means Respiratory abnormality notification information transmitting means CA21a notifies the respiratory abnormality notification information receiving means CB21a of the receiving client personal computer PCb, which will be described later, that the subject's respiration is abnormal. To send respiratory abnormality notification information.

CA21b: Respiratory abnormality notification image display means Respiration abnormality notification image display means CA21b displays a respiratory abnormality notification image 106 indicating the respiratory abnormality notification information shown in FIG. 6D on the display H2.
CA22: Apnea determining means The apnea determining means CA22 determines whether or not the subject is in an apnea state. The apnea discrimination means CA22 of Example 1 is configured so that the subject is in an apnea state when the subject detection member SN3 detects the subject and the respiration rate r [bpm] is not calculated. It is determined that it has become.

CA23: Apnea time measuring means The apnea time measuring means CA23 has an apnea counter (measurement count counting means) i, and is an elapsed time since it is determined that the subject is in an apnea state. Timing breathing time. The apnea time measuring means CA23 of the first embodiment counts the apnea time by counting the number of times the measurement timer TM measures the measurement interval by the apnea counter i. That is, when the measurement interval is TM1 and the apnea time is TM2, the apnea time TM2 is calculated by calculating the following equation (2-1).
TM2 = i × TM1 (2-1)

CA24: Long-term apnea determination means The long-term apnea determination means CA24 determines whether or not the subject is in an apnea state for a long time. The long-term apnea discriminating means CA24 of Embodiment 1 discriminates that the subject is in an apnea state for a long time when the apnea counter i exceeds a preset apnea discrimination threshold. Specifically, when the apnea determination threshold is Si, it is determined whether i> Si is satisfied, thereby determining whether the subject is in an apnea state for a long time. To do.
CA25: Long-term apnea notification means The long-term apnea notification means CA25 has long-term apnea notification information transmission means CA25a and long-term apnea notification image display means CA25b. When it is determined that the subject is in an apnea state for a long time, the subject is informed that the subject is in an apnea state for a long time.
CA25a: Long-term apnea notification information transmitting means Long-term apnea notification information transmitting means CA25a is the long-term apnea notification information receiving means CB25a of the receiving client personal computer PCb described later. Send long-term apnea notification information to notify you.

CA25b: Long-term apnea notification image display means The long-term apnea notification image display means CA25b displays the long-term apnea notification image 107 indicating the long-term apnea notification information shown in FIG. 6E on the display H2.
CA26: Laying-down discriminating means The lying-down discriminating means CA26 discriminates whether or not the subject has turned over. The turn-over discriminating means CA26 according to the first embodiment is configured such that the body motion component having the second highest combined strength for heart rate extracted by the respiratory component extracting means CA6b or the body having the second highest combined strength for breathing. When any one of the intensities of the dynamic component exceeds a preset turning determination threshold, it is determined that the subject has turned over.

CA27: Sleeping notification means The sleeping notification means CA27 includes a sleeping notification information transmitting means CA27a and a sleeping notification image display means CA27b, and when it is determined by the sleep determination means CA26 that the subject has turned over. , Announce that the subject has turned over.
CA27a: sleeping notification information transmitting means The sleeping notification information transmitting means CA27a transmits the sleeping notification information for notifying that the subject has turned to the sleeping notification information receiving means CB27a of the receiving client personal computer PCb described later. To do.

CA27b: Sleep notification image display means The sleep notification image display means CA27b displays the sleep notification image 108 indicating the sleep notification information shown in FIG. 6F on the display H2.
CA28: Non-sleeping time counting means The non-sleeping time counting means CA28 has a non-sleeping counter (measurement number counting means) j, and is the non-sleeping time that is an elapsed time since it is determined that the subject has turned over. Time. The non-sleeping time counting means CA28 according to the first embodiment counts the number of times when the measurement timer TM times the measurement interval by the non-sleeping counter j, thereby counting the non-sleeping time. That is, when the measurement interval is TM1 and the non-sleeping time is TM3, the non-sleeping time TM3 is calculated by calculating the following equation (2-2).
TM3 = j × TM1 (2-2)
CA29: Long-term non-sleeping determination means The long-term non-sleeping determination means CA29 determines whether or not the subject has not laid down for a long time. The long-term non-sleep determination means CA29 according to the first embodiment determines that the subject has not laid down for a long time when the non-sleep counter j exceeds a preset non-sleep determination threshold. Specifically, it is determined whether or not the subject has not laid down for a long period of time by determining whether or not j> Sj is satisfied when the threshold for determining unturned is Sj. To do.

CA30: Long-term unsleeping notification means Long-term unsleeping notification means CA30 includes long-term unsleeping notification information transmitting means CA30a and long-term unsleeping notification image display means CA30b. When it is determined that the subject has not turned over for a long time, the subject is informed that the subject has not turned over for a long time.
CA30a: Long-term non-sleeping notification information transmitting means Long-term non-sleeping notification information transmitting means CA30a is not subject to long-term non-sleeping notification information receiving means CB30a of the receiving client personal computer PCb. Send long-term unannounced notice information to notify you.
CA30b: Long-term unsleeping notification image display means The long-term unsleeping notification image display means CA30b displays the long-term unsleeping notification image 109 indicating the long-term unsleeping notification information shown in FIG. 6G on the display H2.

(Description of the control unit of the computer main body H1 of the receiving client personal computer PCb)
The hard disk drive of the receiving client personal computer PCb also includes a basic software (operating system) OS for controlling basic operations of the receiving client personal computer PCb, a physical information notification program AP3 as an application program, and other software (not shown). It is remembered.

(Physical information notification program AP3)
The physical information notification program AP3 includes the following functional means (program modules).
CB10: Physical information receiving means The physical information receiving means CB10 receives the heart rate h [bpm] and the respiratory rate r [bpm], which are the physical information of the subject transmitted by the physical information transmitting means CA10.

CB11: Physical information image display means The physical information image display means CB11 uses the physical information image 101 shown in FIG. 5 as the heart rate h [bpm] and the respiratory rate r [bpm] received by the physical information reception means CB10. Is displayed on the display H2.
CB14: Get-off notification means The get-off notice means CB14 has a get-off notice information receiving means CB14a and a get-off notice image display means CB14b. Notice.
CB14a: Get-off notice information receiving means The get-off notice information receiving means CB14a receives the get-off notice information transmitted by the get-off notice information transmitting means CA 14a.
CB14b: Get-off notification image display means The get-off notice image display means CB14b displays the get-off notice information received by the get-off notice information receiving means CB14a on the display H2 as the get-off notice image 102 shown in FIG. 6A.

CB17: Long-term bed leaving notice means The long-term bed leaving notice means CB17 has a long-term bed leaving notice information receiving means CB17a and a long-term bed leaving notice image display means CA17b. Like the long-term bed leaving notice means CA17, the subject is the bed 1 Announce for a long time away from
CB17a: Long-term bed announcement information receiving means The long-term bed announcement information receiving means CB17a receives the long-term bed announcement information transmitting means CA17a.
CA17b: Long-term bed announcement image display means The long-term bed announcement image display means CA17b displays the long-term bed announcement information received by the long-term bed announcement information reception means CB17a on the display H2 as the long-term bed announcement image 103 shown in FIG. 6B. indicate.

CB19: Heartbeat abnormality notification means The heartbeat abnormality notification means CB19 has a heartbeat abnormality notification information receiving means CB19a and a heartbeat abnormality notification image display means CB19b. Like the heartbeat abnormality notification means CA19, the heartbeat of the subject is detected. Announce an abnormal condition.
CB19a: Heartbeat abnormality notification information receiving means Heartbeat abnormality notification information receiving means CB19a receives the heartbeat abnormality notification information transmitted by the heartbeat abnormality notification information transmitting means CA19a.
CB19b: Heartbeat abnormality notification image display means The heartbeat abnormality notification image display means CB19b displays the heartbeat abnormality notification information received by the heartbeat abnormality notification information reception means CB19a on the display H2 as the heartbeat abnormality notification image 104 shown in FIG. 6C. indicate.

CB21: Respiratory abnormality notification means Respiratory abnormality notification means CB21 has a respiratory abnormality notification information receiving means CB21a and a respiratory abnormality notification image display means CB21b. Like the respiratory abnormality notification means CA21, breathing of the subject is performed. Announce an abnormal condition.
CB21a: Respiratory abnormality notification information receiving means Respiratory abnormality notification information receiving means CB21a receives the respiratory abnormality notification information transmitted by the respiratory abnormality notification information transmitting means CA21a.
CB21b: Respiratory abnormality notification image display means Respiration abnormality notification image display means CB21b displays the respiratory abnormality notification information received by the respiratory abnormality notification information receiving means CB21a on the display H2 as the respiratory abnormality notification image 106 shown in FIG. 6D. indicate.

CB25: Long-term apnea notification means The long-term apnea notification means CB25 includes a long-term apnea notification information reception means CB25a and a long-term apnea notification image display means CB25b. Announce that the subject has been in apnea for a long time.
CB25a: Long-term apnea notification information receiving means The long-term apnea notification information receiving means CB25a receives the long-term apnea notification information transmitted by the respiratory abnormality notification information transmitting means CA21a.
CB25b: Long-term apnea notification image display means The long-term apnea notification image display means CB25b indicates the long-term apnea notification information 107 received by the long-term apnea notification information reception means CB25a as shown in FIG. 6E. Is displayed on the display H2.

CB27: Sleep notification means The sleep notification means CB27 has a sleep notification information receiving means CB27a and a sleep notification image display means CB27b, and, like the sleep notification means CA27, notifies that the subject has turned over. To do.
CB27a: Sleep notification information receiving means The sleep notification information receiving means CB27a receives the sleep notification information transmitted by the sleep notification information transmitting means CA27a.
CB27b: Sleep notification image display means The sleep notification image display means CB27b displays the sleep notification information received by the sleep notification information receiving means CB27a on the display H2 as the sleep notification image 108 shown in FIG. 6F.

CB30: Long-term unsleeping notification means The long-term unsleeping notification means CB30 includes a long-term unsleeping notification information receiving means CB30a and a long-term unsleeping notification image display means CB30b. Announce that the subject has not been turned over for a long time.
CB30a: Long-term unsleeping notification information receiving means Long-term unsleeping notification information receiving means CB30a receives the long-term unsleeping notification information transmitting means CA30a.
CB30b: Long-term unsleeping notification image display means The long-term unsleeping notification image display means CB30b indicates the long-term unsleeping notification information received by the long-term unsleeping notification information receiving means CB30a as the long-term unsleeping notification image 109 shown in FIG. 6G. Is displayed on the display H2.

(Description of Flowchart of Example 1)
Next, the processing flow of the programs AP1 and AP2 of the measurement client personal computer PCa according to the first embodiment will be described with reference to flowcharts. Note that each process of the physical information notification program AP3 of the receiving client personal computer PCb of the first embodiment is illustrated in FIG. Since the images are only displayed as the images 101 to 109 shown in FIG.
(Description of Flowchart of Physical Information Measurement Processing of Physical Information Measurement Program AP1 of Example 1)
FIG. 7 is a flowchart of physical information measurement of the physical information measurement program AP1 according to the first embodiment.
The processing of each ST (step) in the flowchart of FIG. 7 is performed according to a program stored in the ROM or the like of the control unit. This process is executed in a multitasking manner in parallel with other various processes of the control unit.

The flowchart shown in FIG. 7 is started when the measurement client personal computer PCa is activated.
In ST1 of FIG. 7, the following processes (1) to (4) are executed, and the process proceeds to ST2.
(1) The physical information image 101 shown in FIG. 5 is displayed.
(2) The storage of the history of the output signals output from the microwave radars SN1 and SN2 shown in FIGS. 1 and 2 is started.
(3) The measurement of the measurement interval TM1 by the measurement timer TM is started.
(4) Each counter i, j is set to 0 (i = j = 0).
In ST2, it is determined whether or not the subject detection member SN3 shown in FIGS. 1 and 2 has detected the subject. If no (N), the process moves to ST3, and if yes (Y), the process moves to ST9.
In ST3, it is determined whether or not the heart rate h and the respiratory rate r have been calculated. That is, it is determined whether or not the initial state is reached. If yes (Y), the process proceeds to ST4, and, if no (N), the process proceeds to ST5.

In ST4, it is determined whether or not the values of heart rate h and respiration rate r have been calculated. That is, it is determined whether or not h = r = 0 holds. If yes (Y), the process proceeds to ST4, and, if no (N), the process proceeds to ST5.
In ST5, the following processes (1) to (4) are executed, and the process proceeds to ST6.
(1) Transmitting bed leaving notification information to the receiving client personal computer PCb.
(2) The bed announcement image 102 shown in FIG. 6A is displayed.
(3) Start counting the bed leaving time by the bed leaving timer TM ′.
In ST6, it is determined whether or not the subject detection member SN3 has detected the subject. If yes (Y), the process proceeds to ST9, and, if no (N), the process proceeds to ST7.

In ST7, it is determined whether or not the subject has been away from the bed 1 for a long time by determining whether or not the bed leaving time during measurement exceeds the threshold for bed leaving determination. If yes (Y), the process proceeds to ST8, and, if no (N), the process returns to ST6.
In ST8, the following processes (1) and (2) are executed, and the process proceeds to ST2.
(1) The long-term bed leaving notification information is transmitted to the receiving client personal computer PCb.
(2) The long-term bed leaving notification image 103 shown in FIG. 6B is displayed.
In ST9, it is determined whether or not the waveform of the history of each output signal is stored by determining whether or not the measurement interval TM1 has elapsed by the measurement timer TM. If yes (Y), the process proceeds to ST10, and, if no (N), ST9 is repeated.

In ST10, the following processes (1) and (2) are executed, and the process proceeds to ST11.
(1) The frequency components outside the heartbeat passband (0.5 to 3.0 [Hz]) are removed from the history waveform of each output signal, and the first heartbeat passband waveform and the second heartbeat pass. Generate a band waveform.
(2) The frequency component outside the passband for respiration (0.05 to 0.5 [Hz]) is removed from the history waveform of each output signal, and the first respiration passband waveform and the first respiration pass Generate a band waveform.
In ST11, the following processes (1) and (2) are executed, and the process proceeds to ST12.
(1) The intensity of each frequency component included in each heartbeat passband waveform is calculated and normalized for each frequency component by fast Fourier transform (FFT).
(2) The intensity of each frequency component included in each respiratory passband waveform is calculated and normalized for each frequency component by fast Fourier transform (FFT).

In ST12, the following processes (1) and (2) are executed, and the process proceeds to ST13.
(1) The product of the intensity of each frequency component included in the first heartbeat passband waveform and the intensity of each frequency component included in the second heartbeat passband waveform corresponding to each frequency component is calculated for each frequency component. By calculating, the combined intensity for heartbeats, which is the combined intensity for each frequency component of the passband waveform for each heartbeat, is calculated.
(2) The product of the intensity of each frequency component included in the first respiratory passband waveform and the intensity of each frequency component included in the second respiratory passband waveform corresponding to each frequency component is calculated for each frequency component. By calculating, the combined intensity for respiration that is the combined intensity for each frequency component of each passband waveform for respiration is calculated.

In ST13, the following processes (1) to (3) are executed, and the process proceeds to ST14.
(1) A frequency component (peak frequency) having the maximum combined intensity for heartbeat is extracted as a heartbeat component.
(2) A frequency component (peak frequency) having a maximum combined intensity for respiration is extracted as a respiration component.
(3) Each frequency component with the second highest combined intensity for heartbeat and combined intensity for respiration is extracted as a body movement component.
In ST14, the following processes (1) and (2) are executed, and the process proceeds to ST15.
(1) Based on the extracted frequency f _h [Hz] of the heart rate component and Expression (1-1), the heart rate h [bpm] of the subject per unit time is calculated and temporarily stored.
(2) Based on the extracted frequency f _r [Hz] of the respiratory component and the expression (1-2), the respiratory rate r [bpm] per unit time of the subject is calculated and temporarily stored.

In ST15, the following processes (1) and (2) are executed, and the process proceeds to ST16.
(1) The heart rate h [bpm] and the respiration rate r [bpm] as the calculation results, which are the body information of the subject, are transmitted to the receiving client personal computer PCb.
(2) The heart rate h [bpm] and the respiratory rate r [bpm] are displayed (updated) on the physical information image 1.
In ST16, a heartbeat abnormality notification process shown in FIG. Then, the process proceeds to ST17.
In ST17, a respiratory abnormality notification process shown in FIG. 9 described later is executed. Then, the process proceeds to ST18.
In ST18, a sleep notification process shown in FIG. Then, the process returns to ST2.

(Explanation of Flowchart of Heart Rate Abnormality Notification Processing of Physical Information Measurement Program AP1 of Example 1)
FIG. 8 is a flowchart of the abnormal heart rate notification process of the physical information measurement program AP1 of the first embodiment, and is an explanatory diagram of the subroutine of ST16 of FIG.
In ST101 of FIG. 8, it is determined whether or not the heart rate h [bpm] is calculated, that is, whether h = 0 [bpm] is not satisfied. If yes (Y), the process proceeds to ST102, and, if no (N), the process proceeds to ST103.
In ST102, it is determined whether or not the heart rate h [bpm] is outside the normal heart rate range (40 to 100 [bpm]). If yes (Y), the process moves to ST103, and, if no (N), the heartbeat abnormality notification process is terminated, and the process returns to ST16 in FIG.
In ST103, the following processes (1) and (2) are executed, the heartbeat abnormality notification process is terminated, and the process returns to ST16 in FIG.
(1) The heartbeat abnormality notification information is transmitted to the receiving client personal computer PCb.
(2) The heartbeat abnormality notification image 104 shown in FIG. 6C is displayed.

(Explanation of Flowchart of Respiratory Abnormality Notification Processing of Physical Information Measurement Program AP1 of Example 1)
FIG. 9 is a flowchart of the respiratory abnormality notification process of the physical information measurement program AP1 of Example 1, and is an explanatory diagram of the subroutine of ST17 of FIG.
In ST201 of FIG. 9, it is determined whether or not the respiration rate r [bpm] is calculated, that is, whether r = 0 [bpm]. If no (N), the process proceeds to ST202, and if yes (Y), the process proceeds to ST205.
In ST202, it is determined whether or not the subject has been in an apnea state for a long time by determining whether or not the apnea counter i has exceeded a preset apnea determination threshold value Si (i> Si). ). If yes (Y), the process proceeds to ST203, and, if no (N), the process proceeds to ST204.
In ST203, the following processes (1) and (2) are executed, and the process proceeds to ST204.
(1) The long-term apnea notification information is transmitted to the receiving client personal computer PCb.
(2) The long-term apnea notification image 107 shown in FIG. 6E is displayed.

In ST204, +1 is added to the apnea counter i (i = i + 1). Then, the respiratory abnormality notification process is terminated, and the process returns to ST17 of FIG.
In ST205, the apnea counter i is reset to 0 (i = 0). Then, the process proceeds to ST206.
In S206, it is determined whether or not the heart rate h [bpm] is outside the normal breathing range (10 to 25 [bpm]). If yes (Y), the process proceeds to ST207, and, if no (N), the respiratory abnormality notification process ends, and the process returns to ST17 of FIG.
In ST207, the following processes (1) and (2) are executed, the respiratory abnormality notification process is terminated, and the process returns to ST17 in FIG.
(1) The respiratory abnormality notification information is transmitted to the receiving client personal computer PCb.
(2) The respiratory abnormality notification image 106 shown in FIG. 6D is displayed.

(Explanation of the flowchart of the sleep notification process of the physical information measurement program AP1 of the first embodiment)
FIG. 10 is a flowchart of the sleep notification process of the physical information measurement program AP1 according to the first embodiment, and is an explanatory diagram of the subroutine of ST18 of FIG.
In ST301 of FIG. 10, it is determined whether or not the subject has turned over by determining whether or not the strength of the body motion component has exceeded the threshold for turning over. If yes (Y), the process proceeds to ST302, and, if no (N), the process proceeds to ST303.
In ST302, the following processes (1) and (2) are executed, the sleep notification process is terminated, and the process returns to ST18 in FIG.
(1) The sleep notification information is transmitted to the receiving client personal computer PCb.
(2) The sleep notification image 108 shown in FIG. 6F is displayed.
(3) The non-sleeping counter j is reset to 0 (j = 0).
In ST303, it is determined whether or not the subject has not turned over for a long period of time by determining whether or not the counter for unturning j has exceeded a preset threshold for determination of unturning Sj (j>). Sj). If yes (Y), the process proceeds to ST304, and, if no (N), the process proceeds to ST305.

In ST304, the following processes (1) and (2) are executed, the sleep notification process is terminated, and the process returns to ST18 in FIG.
(1) The long-term unsleeping notification information is transmitted to the receiving client personal computer PCb.
(2) The long-term unsleeping notification image 109 shown in FIG. 6G is displayed.
In ST305, +1 is added to the non-sleeping counter j (j = j + 1). Then, the sleep notification process is terminated, and the process returns to ST18 of FIG.

(Operation of Example 1)
In the physical information measurement system S of Example 1 having the above-described configuration, as shown in FIG. 7, physical information measurement for measuring the heart rate [bpm] and the respiratory rate [bpm], which are physical information of the subject. Processing is executed.
In the physical information measurement process of the first embodiment, as shown in ST2 of FIG. 7, when the subject lies on the mattress 1b, the subject detection member SN3 shown in FIGS. 1 and 2 detects the subject. Further, as shown in ST1 and ST9 of FIG. 7, output signals from the microwave radars SN1 and SN2 shown in FIGS. 1 and 2 are output to the control unit of the computer main body H1 of the measurement client personal computer PCa, and measurement is performed. A history waveform of each output signal is stored for each interval TM1. Further, as shown in ST10 of FIG. 7, the stored waveform of each output signal has the frequency component outside the heartbeat passband (0.5 to 3.0 [Hz]) removed. Each heartbeat passband waveform is obtained, and each breathing passband waveform is obtained by removing frequency components outside the breathing passband (0.05 to 0.5 [Hz]).

Also, as shown in ST11 of FIG. 7, the intensity of each frequency component is calculated for each frequency component by fast Fourier transform (FFT) from the generated passband waveform for each heartbeat and each passband waveform for respiration. To be normalized. In addition, as shown in ST12 of FIG. 7, the heart rate combined intensity of each frequency component, which is the product of the intensities of the frequency components included in each heartbeat passband waveform, and the respiratory passband waveform. The respiratory combined intensity of each frequency component, which is the product of the intensities of the included frequency components, is calculated. In addition, as shown in ST13 (1), (2), and ST14, a heartbeat component that maximizes the combined intensity for heartbeat and a respiratory component that maximizes the combined intensity for breathing are extracted, and Based on the frequencies f _h and f _r [Hz] and the expressions (1-1) and (1-2), the heart rate h [bpm] and the respiration rate r [bpm] are calculated and stored. .

  Therefore, in the body information measuring system S of the first embodiment, the body information (heart rate h [bpm], respiratory rate) of the subject without contacting or contacting the subject with a contact-type sensor such as a silver plate electrode. r [bpm]) can be measured. The body information measurement system S of the first embodiment includes the two microwave radars SN1 and SN2, and the measurement areas A1 and A2 for measuring the reflected waves from the subject are the mattress 1b. Two are set on the upper surface. For this reason, the body information measurement system S of the first embodiment does not output an output signal due to the subject turning over or the like, compared with the technique of Patent Document 1 in which measurement is performed by one microwave radar, and the heartbeat It is reduced that the number h [bpm] and the respiration rate [bpm] cannot be detected.

(Experimental example)
Here, the physical information measurement and measurement process of the first embodiment is based on the output signals from the two microwave radars SN1 and SN2, and the physical information (heart rate h [bpm], respiratory rate of the subject). In order to examine how accurately r [bpm]) can be measured, the following Experimental Example 1 and Comparative Example 1 were prepared.
(Experimental example 1)
In Experimental Example 1, the physical information measurement process (see ST1 to ST15 in FIG. 7) by the physical information measuring apparatus U of Example 1 was performed for 30 seconds. The subject in Experimental Example 1 is a human (subject, subject) who is resting and lying on the mattress 1b.
(Comparative Example 1)
The physical information measuring device U of Comparative Example 1 is a contact-type electrocardiogram in which measurement electrodes are attached to the chest of the subject instead of the microwave radars SN1 and SN2 of the physical information measuring device U of Experimental Example 1. Has a respiration sensor. In Comparative Example 1, the measurement electrode is attached to the chest of the subject in Experimental Example 1, and simultaneously with Experimental Example 1, physical information (heart rate h [bpm], Measurement of respiration rate r [bpm]) was carried out for 30 seconds.

(Experimental result)
FIG. 11 is an explanatory diagram of measurement results obtained by the sensors of Experimental Example 1 and Comparative Example 1, and is an explanatory diagram of a waveform graph in which the vertical axis indicates amplitude [V] and the horizontal axis indicates time [sec]. FIG. 11A shows an output waveform relating to the heartbeat of the subject when the waveform of each output signal of each microwave radar in Experimental Example 1 and the output waveform of the electrocardiogram in Comparative Example 1 are passed through a high-pass filter of 0.5 Hz. FIG. 11B is a diagram illustrating a history waveform of each output signal of each microwave radar of Experimental Example 1 and an output waveform of the respiratory sensor of Comparative Example 1 when passing through a 0.05 Hz high-pass filter. It is explanatory drawing of the output waveform regarding the respiration of a test substance.
FIG. 12 is an explanatory diagram of the removal result by band-pass filtering for the measurement results of Experimental Example 1 and Comparative Example 1. FIG. 12A shows the output waveform of FIG. 11A in the passband for heartbeat (0.5 to 3.0 [Hz]. ]) Is an explanatory diagram of each heartbeat passband waveform from which the external frequency components have been removed, and FIG. 12B shows each output waveform in FIG. 11B outside the breathing passband (0.05 to 0.5 [Hz]). It is explanatory drawing of each pass band waveform for respiration from which the frequency component was removed.

FIG. 13 is an explanatory diagram of the removal result by band-pass filtering for the measurement results of Experimental Example 1 and Comparative Example 1. FIG. 13A shows the passband waveforms for heartbeats shown in FIG. 12A displayed at intervals of 30 seconds at intervals of 5 seconds. FIG. 13B is an enlarged explanatory diagram in which each respiratory passband waveform of FIG. 12B displayed at intervals of 30 seconds is displayed at intervals of 5 seconds.
FIG. 14 is an explanatory diagram of calculation results by fast Fourier transform on the removal results of Experimental Example 1 and Comparative Example 1, and an explanatory diagram of a graph of a spectrum waveform in which the vertical axis indicates intensity and the horizontal axis indicates frequency [Hz]. 14A is an explanatory diagram of a spectrum waveform obtained by fast Fourier transforming each of the heartbeat passband waveforms of FIGS. 12A and 13A, and FIG. 14B is a diagram of each of the respiratory passband waveforms of FIGS. It is explanatory drawing of the converted spectrum waveform.

FIG. 15 is an explanatory diagram of the calculation result of the combined intensity (the product of each normalized intensity) with respect to the calculation result of Experimental Example 1. The vertical axis indicates the ratio [%] to the total combined intensity, and the horizontal axis indicates the body information. It is explanatory drawing of the graph of the spectrum waveform which took (heart rate h [bpm], respiration rate r [bpm]), and FIG. 15A is the synthetic | combination intensity | strength for every frequency component contained in each passband waveform for heartbeats of FIG. 14A. FIG. 15B is an explanatory view of the spectrum waveform of the combined intensity for each frequency component included in each respiratory passband waveform of FIG. 14B.
As shown in FIG. 11, the output waveforms of the non-contact type microwave radars SN <b> 1 and SN <b> 2 of Experimental Example 1 (refer to the waveform of the history of the output signal, refer to the one-dot chain line and the two-dot chain line). It can be seen that the phases are almost the same, although the phase is shifted compared to the output waveform (see solid line) of the electrocardiogram of the type and the respiratory sensor. The phase shift is considered to be affected by the delay time until each of the microwave radars SN1 and SN2 irradiates the microwave and receives the reflected wave.

Further, as shown in FIG. 11A, it can be seen that the output waveform related to the heartbeat of each of the microwave radars SN1 and SN2 contains more noise than the output waveform of the electrocardiogram of Comparative Example 1.
As shown in FIG. 11B, the output waveforms related to respiration of the microwave radars SN1 and SN2 are not as large as the output waveforms related to the heartbeat, but contain more noise than the output waveform of the respiration sensor of Comparative Example 1. You can see that This is because the measurement results of the non-contact type microwave radars SN1 and SN2 are more susceptible to the body movement of the subject than the measurement results of the contact type electrocardiogram and the respiratory sensor. it is conceivable that.
In Experimental Example 1, it can be seen that the output waveform of the first microwave radar SN1 has a larger amplitude [V] than the output waveform of the second microwave radar SN2 (particularly regarding the respiration in FIG. 11B). Refer to each output waveform). This is because the subject's respiration and heartbeat micromotion in the first measurement region A1 are larger than the subject's respiration and heartbeat micromotion in the second measurement region A2. it is conceivable that.

(Measurement results of heart rate h in Experimental Example 1 and Comparative Example 1)
Here, the measurement result of the heart rate h of the subject in Experimental Example 1 and Comparative Example 1 will be described. First, as shown in FIG. 12A and FIG. 13A, the first heartbeat passband waveform (refer to the one-dot chain line) of Experimental Example 1 has a different period from the heartbeat passband waveform of Comparative Example 1 (refer to the solid line). (In particular, see the dashed line in FIG. 13A). In addition, the second heartbeat passband waveform (refer to the two-dot chain line) of Experimental Example 1 is out of phase with the heartbeat passband waveform of Comparative Example 1 and the period remains substantially the same. It can be seen that the shape is also approximate.
Regarding the difference in the period of the first heartbeat passband waveform, since the amplitude [V] of the output waveform of the first microwave radar SN1 is large, it is affected by noise such as body movement other than the heartbeat of the subject. This is thought to be because of the strong appearance of.

Further, as shown in FIG. 14A, the peak frequency f _h is about 1.03 [Hz] for the spectrum waveform of the intensity of the first heartbeat passband waveform of Experimental Example 1 (see the one-dot chain line), which is a comparative example. a peak frequency f _h of the spectral waveform of the intensity of one heartbeat for the passband waveform (see solid line), it can be seen that differs from the approximately 1.05 [Hz]. In addition, it can be seen that relatively large values are scattered as compared with Comparative Example 1 except for the peak frequency f _h , that is, the intensity of the noise frequency component. Further, the spectrum waveform of the intensity of the second heartbeat passband waveform in Experimental Example 1 (see the two-dot chain line) has a higher frequency component of noise than the spectrum waveform of the intensity of the heartbeat passband waveform in Comparative Example 1. Although it is large, it can be seen that the peak frequencies f _h coincide with each other and are about 1.05 [Hz] (f _h ≈1.05 [Hz]).
Note that the peak frequency f _h of the spectrum waveform of the first heartbeat passband waveform intensity is different from that of the first heartbeat passband waveform (see the one-dot chain line in FIG. 13A). However, it is thought that it appeared directly as a calculation result by Fast Fourier Transform (FFT).

However, as shown in FIG. 15A, the spectrum waveform of the combined intensity of each heartbeat passband waveform in Experimental Example 1 (see the dashed line) is the spectrum waveform of the intensity of the heartbeat passband waveform in Comparative Example 1 (see FIG. 14A). And the peak frequency f _h coincides (f _h ≈1.05 [Hz]), that is, the heart rate h [bpm] coincides and becomes approximately 63 [bpm]. (H≈63 [bpm]). That is, in Experimental Example 1, the influence of noise in the first heartbeat passband waveform is greatly reduced by calculating the combined strength for heartbeats, which is the product of the intensities of the frequency components in the passband waveforms for each heartbeat. It can be seen that the approximation was possible until the same value (h≈63 [bpm]) as the heart rate h [bpm] of Comparative Example 1 was obtained.

(Measurement results of respiratory rate r in Experimental Example 1 and Comparative Example 1)
The measurement results of the respiratory rate r of the subject in Experimental Example 1 and Comparative Example 1 will be described. First, as shown in FIGS. 12B and 13B, the first breathing passband waveform (one-dot chain line) and the second breathing passband waveform (refer to the two-dot chain line) in Experimental Example 1 are passed through the second heartbeat pass. Similar to the band waveform (see the two-dot chain line in FIG. 13A), the shape of the waveform is also approximated while the phase is out of phase with the passband waveform for respiration (see the solid line) of Comparative Example 1 and the period remains substantially the same. You can see that
Further, as shown in FIG. 14B, the spectrum waveform of the intensity of the first respiratory passband waveform in the experimental example 1 (see the dashed-dotted line) and the spectrum waveform of the intensity of the second respiratory passband waveform (see the dashed-two dotted line). Similarly to the intensity spectrum waveform of the second heartbeat passband waveform (see the two-dot chain line in FIG. 14A), the noise is compared with the intensity spectrum waveform of the breathing passband waveform of Comparative Example 1 (see the solid line). It can be seen that the peak frequency _fr is matched and is about 0.2 [Hz] ( _fr ≈ 0.2 [Hz]).

Further, as shown in FIG. 15B, the spectrum waveform of the intensity of the respiratory passband waveform of Comparative Example 1 (see FIG. 15B) is also obtained for the spectrum waveform of the combined intensity of each respiratory passband waveform of Experimental Example 1 (see the dashed line). 14B, see the solid line in FIG. 15B), and the peak frequencies f _r coincide (f _r ≈0.2 [Hz]), that is, the respiration rates r [bpm] coincide, and about 12 [bpm]. (R≈12 [bpm]).
Accordingly, the non-contact type physical information measuring device U of Experimental Example 1 has the same accuracy as the contact type physical information measuring device U of Comparative Example 1 with the heart rate h [bpm] and the respiration rate r [ bpm] can be measured.

  Further, in Experimental Example 1, the output waveform of the first microwave radar SN1 is strongly affected by noise, and the heart rate of the single microwave radar SN1 with the same accuracy as the contact-type physical information measuring device U of Comparative Example 1 is used alone. It was confirmed that the number h [bpm] and the respiration rate r [bpm] may not be measured. Therefore, the physical information measuring device U of Experimental Example 1 uses the low-pass filter for breathing (0.3 [Hz]) and the high-pass filter for heartbeat (1 [Hz]) for the output waveform of one microwave radar. Compared with the technique of Patent Document 1 or the like that measures the heart rate h and the respiratory rate r using the above, the influence of noise based on the body motion of the subject is reduced, and the heart rate h [bpm] and the respiratory rate r are reduced. It was confirmed that [bpm] can be measured with high accuracy.

  Further, in the body information measuring system S of Example 1 having the above-described configuration, as shown in ST2 to ST4 of FIG. 7, the subject does not lie on the mattress 1b, and the heart rate h [bpm] Alternatively, when the respiration rate r [bpm] is not calculated, it is determined that the subject is away from the bed 1. Then, as shown in ST5 (1) and (2) of FIG. 7, the get-off notice information is transmitted to the receiving client personal computer PCb, and the get-off notice image 102 shown in FIG. It is displayed on the display H2 of the PCb. For this reason, the body information measurement system S according to the first embodiment does not calculate the heart rate h [bpm] or the respiration rate r [bpm] when the subject is away from the bed 1. be able to. In addition, for example, use of the receiving client personal computer PCb (an observer, a monitor, a caregiver, a caretaker, a doctor, a nurse, etc.) placed in a separate room or a remote place of the room where the bed 1 is placed Person) can confirm that the subject is separated from the bed 1, and if necessary, can go to the subject.

  Further, as shown in ST5 (3) to ST7 in FIG. 7, when it is determined that the subject has left the bed 1, the bed leaving time is counted by the bed leaving timer TM ′, and the bed leaving time during the time counting is measured. Exceeds a preset threshold for determining bed separation, it is determined that the subject has been separated from the bed 1 for a long period of time. Then, as shown in ST8 of FIG. 7, the long-term leaving notice information is transmitted to the receiving client personal computer PCb, and the long-term leaving notice image 103 shown in FIG. 6B is displayed on the display H2 of each client personal computer PCa, PCb. Is displayed. For this reason, for example, the user who is away from the subject can confirm that the subject has been away from the bed 1 for a long period of time, and the subject requiring monitoring, nursing care, maintenance or the like is out. -It is possible to go to search to confirm whether or not he / she is wrinkled, or to check the safety of the subject away from the bed 1.

Further, in the physical information measuring system S of Example 1 having the above-described configuration, when the subject lies on the mattress 1b and the physical information measuring process is executed, ST16 in FIG. 7 and the above-described in FIG. Heart rate abnormality notification processing is executed.
In the heartbeat abnormality notification process of the first embodiment, as shown in ST101 and ST102 of FIG. 8, when the heart rate h [bpm] is not calculated (h≈0 [bpm]), the normal range for heartbeats If it is outside (40 to 100 [bpm]), it is determined that the heartbeat of the subject is abnormal. Then, as shown in ST103 in FIG. 8, the heartbeat abnormality notification information is transmitted to the receiving client personal computer PCb, and the heartbeat abnormality notification image 104 shown in FIG. 6C is displayed on the display H2 of each client personal computer PCa, PCb. Is displayed. Therefore, the user of each of the client personal computers PCa and PCb can confirm that the life support of the subject is in a dangerous state (state of cardiopulmonary arrest, bradycardia, tachycardia, etc.), and a position away from the subject The user of the receiving client personal computer PCb in the office rushes to confirm the safety of the subject, or the user (doctor, nurse, etc.) near the measuring client personal computer PCa (medical room, etc.) Can be done.

Further, in the physical information measuring system S of the first embodiment having the above-described configuration, the abnormal breath notification process shown in ST17 of FIG. 7 and the respiratory abnormality notification process shown in FIG.
In the respiratory abnormality notification process of the first embodiment, as shown in ST206 of FIG. 9, when the respiratory rate r [bpm] is outside the normal breathing range (10 to 25 [bpm]), the subject Is determined to be in an abnormal state. Then, as shown in ST207 of FIG. 8, the respiratory abnormality notification information is transmitted to the reception client personal computer PCb, and the respiratory abnormality notification image 106 shown in FIG. 6D is displayed on the display H2 of each client personal computer PCa, PCb. Is displayed. For this reason, as in the case of the abnormal heart rate notification process, the user of each of the client personal computers PCa and PCb confirms that the life of the subject is in a dangerous state (cardiopulmonary arrest, slow breathing, tachypnea, etc.). The user of the receiving client personal computer PCb located away from the subject rushes to confirm the safety of the subject, or the user near the measuring client personal computer PCa promptly performs a medical action or the like. be able to.

  In the respiratory abnormality notification process of the first embodiment, as shown in ST201 to ST202, ST204, ST205 of FIG. 9, the respiratory rate r [bpm] is not calculated, and the apnea counter i is set in advance. If the set apnea discrimination threshold Si is exceeded (i> Si), it is determined that the subject is in an apnea state for a long time. Therefore, the physical information measurement system S of Example 1 determines that the respiration rate r [bpm] has not been measured for about 30 seconds to 2 minutes, for example, according to the value of the apnea determination threshold Si. (Si × TM1> 30 [sec], Si × TM1> 120 [sec]). Then, as shown in ST203, the long-term apnea notification information is transmitted to the receiving client personal computer PCb, and the long-term apnea notification image 107 shown in FIG. 6E is displayed on the display H2 of each of the client personal computers PCa and PCb. Is done.

  Therefore, the user of each of the client personal computers PCa and PCb can confirm that the subject is in a dangerous state (long-term cardiopulmonary arrest, sleep apnea syndrome, etc.). Therefore, for example, the user of the receiving client personal computer PCb located at a position away from the subject can rush to confirm the safety of the subject. In addition, for example, a user near the measurement client personal computer PCa wakes up the subject and prompts the subject to breathe directly, or adjusts the posture of the subject to make it easy to breathe ( For example, the body can be turned sideways, the airway can be secured with the chin facing up), or the subject can be encouraged to breathe indirectly. Also, for example, for the treatment of sleep apnea syndrome, the history of the respiratory rate r [bpm] of the subject is recorded and used for a severe examination of symptoms, or the test result (test record) is used for treatment. It can also be used.

Further, in the physical information measuring system S of the first embodiment having the above-described configuration, the sleep notification process shown in ST18 of FIG. 7 and the sleep notification process shown in FIG. 10 is executed together with the heartbeat abnormality notification process and the respiratory abnormality notification process.
In the sleep notification process of the first embodiment, as shown in ST301 of FIG. 10, the body motion component that is the second highest frequency component of the combined intensity of each heartbeat passband waveform and each heartbeat passband waveform is obtained. When the intensity exceeds a preset threshold value for turning determination, it is determined that the subject has turned over. Therefore, the body information measurement system S according to the first embodiment can determine whether or not the subject has turned over based on the body motion component that is a frequency component of noise. Then, as shown in ST302 (1) and (2), the sleep notification information is transmitted to the receiving client personal computer PCb, and the sleep notification information image 108 shown in FIG. 6F is displayed on each of the client personal computers PCa and PCb. It is displayed on the display H2. For this reason, the user who is away from the subject can confirm that the subject has turned over, for example, an ecological survey record of the subject under observation (such as a hibernating animal). It can be performed.

  Further, in the sleep notification process of the first embodiment, as shown in ST302 (3), ST303, and ST305 in FIG. When the turning determination threshold value Sj is exceeded (j> Sj), it is determined that the subject has not turned over for a long time. Then, as shown in ST304, the long-term non-sleeping notification information is transmitted to the receiving client personal computer PCb, and the long-term non-sleeping notification image 109 shown in FIG. 6G is displayed on the display H2 of each of the client personal computers PCa and PCb. Is done. Therefore, the user of each of the client personal computers PCa and PCb can confirm that the subject has not turned over for a long time. Further, for example, in order to prevent the subject requiring care or maintenance from rubbing the floor or the like, the user who is near the measurement client personal computer PCa or rushes to the bed 1 from a position away from the subject. The user of the receiving client personal computer PCb can urge the subject to turn over or assist in turning over.

(Example of change)
As mentioned above, although the Example of this invention was explained in full detail, this invention is not limited to the said Example, A various change is performed within the range of the summary of this invention described in the claim. It is possible. Modification examples (H01) to (H018) of the present invention are exemplified below.
(H01) In the above embodiment, the subject is a human (subject, subject), but is not limited to this. For example, the present invention can also be applied to living bodies such as other animals.
(H02) In the above embodiment, the size of the bed 1 is configured as a single, but is not limited to this. For example, the bed 1 is configured as a semi-single, semi-double, double, wide double, queen, king, or other sizes. It is also possible. Further, the dimensions and arrangement distances L1 to L7 of the bed 1 and the sensors SN1 to SN3 can be arbitrarily changed according to the size of the bed 1 and the height and width of the subject.

(H03) In the above-described embodiment, the number of the microwave radars SN1 and SN2 is two, but is not limited thereto, and may be three or more. In this case, the number of microwave radars in which noise appears strongly in the output waveform can be reduced, the accuracy of extraction of the heart rate component and the respiratory component based on the combined intensity can be improved, and the heart rate h [bpm] and The accuracy of the measurement result of the respiration rate r [bpm] can be improved. Further, the areas of the measurement areas A1 and A2 of the microwave radars SN1 and SN2 can be arbitrarily changed according to the measurement accuracy of the device actually used. In addition, when the area of each measurement area | region A1, A2 is enlarged, it can also be set as the structure which 1st measurement area | region A1 and 2nd measurement area | region A2 overlap, for example.
(H04) In the embodiment, each of the microwave radars SN1 and SN2 is supported on, or attached to, the lower surface of the mattress 1b. However, the present invention is not limited to this, and may be incorporated in the mattress 1b. Is possible. The microwave radars SN1 and SN2 are fixedly supported on the lower surface of the mattress 1b. However, the present invention is not limited to this. For example, the mattress 1b is interposed between the mattress support 1a and the mattress 1b. By providing a slider or the like that can move in the front-rear direction and the left-right direction, it can be configured to be variably set at an arbitrary position.

(H05) In the embodiment, each of the microwave radars SN1 and SN2 is supported on, or attached to, the lower surface of the mattress 1b. However, the present invention is not limited to this, and may be incorporated in the mattress 1b. Is possible. The microwave radars SN1 and SN2 are fixedly supported on the lower surface of the mattress 1b. However, the present invention is not limited to this. For example, the mattress 1b is interposed between the mattress support 1a and the mattress 1b. By providing a slider or the like that can move in the front-rear direction and the left-right direction, it can be configured to be variably set at an arbitrary position.
(H06) In the embodiment, the connection between the client personal computers PCa and PCb is configured by the wired LAN 2. However, the present invention is not limited to this. For example, a dedicated line such as a wireless LAN, the Internet, and a nurse call, a telephone line It is also possible to configure other information communication lines such as the above or a combination thereof.
(H07) In the above-described embodiment, the subject detection member SN3 is configured by a so-called bed separation sensor (a heel sensor), but is not limited thereto, and is configured by, for example, a strain gauge, a pressure sensor, or the like, It is also possible to detect the subject by determining whether or not pressure is applied to the mattress 1b.

(H08) In the state where the subject detection member SN3 detects the subject as in the embodiment, the heart rate h [bpm] and the respiration rate r [bpm] by the microwave radars SN1 and SN2 are set. Although it is preferable to perform measurement, the subject detection member SN3 can be omitted. That is, it is also possible to employ a configuration in which the heart rate h [bpm] and the respiration rate r [bpm] are constantly measured by the microwave radars SN1 and SN2. In this case, the bed leaving determination process (see ST4 in FIG. 7), the long-term bed leaving determination process (see ST7 in FIG. 7), the heartbeat abnormality determination process (see ST16 in FIG. 7, ST101 and ST102 in FIG. 8), respiratory abnormality determination Processing (see ST17 in FIG. 7 and ST206 in FIG. 8), long-term apnea discrimination processing (see ST17 in FIG. 7, ST201 and ST202 in FIG. 8), rollover discrimination processing (see ST18 in FIG. 7 and ST301 in FIG. 8), The long-term non-sleeping determination process (see ST18 in FIG. 7 and ST301 and ST303 in FIG. 8) can also be performed based only on the measurement results of the heart rate h [bpm] and the respiration rate r [bpm]. .

(H09) In the above embodiment, the receiving terminal for receiving each piece of information is configured by the receiving client personal computer PCb. However, the present invention is not limited to this, and for example, a PDA that can be connected to an information communication line such as a wireless LAN or the Internet ( (Personal Digital Assistant, Personal Data Assistance) or a portable information terminal such as a cellular phone can be used. The physical information measuring system S preferably includes these receiving terminals. However, the physical information measuring system S is not limited to this, and only the physical information measuring device U in which the wired LAN 2 and the receiving client personal computer PCb are omitted. Even when configured, the effects of the present invention can be achieved.
(H010) In the above embodiment, each combined intensity is calculated by the product of the intensities of the frequency components. However, the present invention is not limited to this. For example, it is also possible to calculate by the sum of the intensities of the frequency components. . In this case, for example, an output waveform (a waveform of an output signal history) is obtained from one of the microwave radars SN1 and SN2, but an output waveform is obtained from the other microwave radars SN2 and SN1. The product of the intensities of the respective frequency components cannot be obtained, that is, even if the frequency components become 0, the sum of the intensities of the respective frequency components can be obtained by the one of the microwave radars SN1 and SN2. Each combined intensity can be calculated from only the output waveform. For this reason, only when the output waveform is not obtained from the other microwave radars SN2 and SN1, it is possible to adopt a configuration in which the sum is obtained instead of the product of the intensities of the respective frequency components.

(H011) In the above embodiment, an output waveform (waveform of output signal history) is obtained from one of the microwave radars SN1 and SN2, but an output waveform is obtained from the other microwave radars SN2 and SN1. If not, it is also possible to execute a sleeping position determination process for determining that the sleeping position of the subject is biased toward the one of the microwave radars SN1 and SN2. If the microwave radars SN1 and SN2 are arranged three or more, for example, two microwave radars SN1 and SN2 are arranged in four rows at equal intervals in the vertical direction (2 × 4 = 8), it is possible to further improve the accuracy of the sleeping position determination process.
(H012) In the above embodiment, the Fast Fourier Transform (FFT) is used to calculate the intensity of each frequency component of each passband waveform. However, the present invention is not limited to this. Discrete Fourier Transform (DFT) and other frequencies used to efficiently calculate frequency analysis, partial differential equations and convolution integrals of digital signals that are not high-speed but discretized by signal processing, etc. It is also possible to use analysis means.

(H013) In the embodiment, in order to improve the accuracy of the measurement result of the heart rate h [bpm] and the respiration rate r [bpm], the bandpass filtering process (see ST10 in FIG. 7) and the normalization It is preferable to execute the process (see ST11 in FIG. 7), but these processes can be omitted.
(H014) In the above embodiment, the heart rate h [bpm] and the respiration rate r [bpm] are measured based on the output signals of the microwave radars SN1 and SN2, but the present invention is not limited to this. It is also possible to measure only the heart rate h [bpm] or only the respiratory rate r [bpm].
(H015) In the above-described embodiment, in the long-term bed leaving determination process (see ST7 in FIG. 7), when the bed leaving time during the measurement exceeds a predetermined bed leaving detection threshold, the subject is long from the bed 1. Although it is determined that the period is separated, the present invention is not limited to this. For example, if the bed leaving time during measurement is within 10 minutes, it is determined that the subject has added a small amount, and within 20 minutes. If it is within 30 minutes, it is determined that the subject is taking a walk, and if it is 30 minutes or more, the subject is determined to be It can be configured to determine that it has been away from the bed 1 for a long time and needs to be searched.

(H016) In the embodiment, as the method of notifying each information, the images 101 to 109 shown in FIG. 6 are displayed on the display H2. However, the present invention is not limited to this. For example, an alarm sound is generated. It is also possible to announce each warning message that explains each piece of information or by turning on a warning color.
(H017) In the above embodiment, the physical information image 101 is configured by an image that describes only the values of the heart rate h [bpm] and the respiratory rate r [bpm]. The measurement results obtained by the microwave radars SN1 and SN2 after high-pass filtering shown in FIG. 11 can be displayed as output waveforms relating to heartbeat and respiration, and the waveforms of the respective processes shown in FIGS. 12 to 15 can be displayed. It is.

(H018) In the above embodiment, in ST13 (3) of FIG. 7, each frequency component having the second highest combined strength for heartbeat and the combined strength for respiration is extracted as a body motion component, but the present invention is not limited to this. For example, the entire frequency component of noise other than the heartbeat component and the respiratory component can be used as the body motion component. In this case, in the embodiment, in the turning determination process (see ST18 in FIG. 7 and ST301 in FIG. 8), it is determined whether or not the combined strength of the body motion components has exceeded the turning determination threshold. Whether or not the sample has been turned over is determined, for example, whether or not the subject has turned over by determining whether or not the total value of the combined intensity of the body motion components has exceeded the threshold for determining the turn over. It is also possible to determine. That is, when the ratio (rate, ratio, composition ratio, composition ratio) to the total composition intensity, which is the value of the combined intensity for heartbeat or the combined intensity for breathing, is equal to or less than a preset threshold value, the body motion component It is also possible to determine whether or not the total value of the combined intensities exceeds the threshold for turning over and whether or not the subject has turned over.

  The physical information measuring device U and the physical information measuring system S of the present invention can be used, for example, in a hospital where a doctor, a nurse, or the like is in a hospital such as an examination room or a nurse station, or in a remote place when going out or going home. This is useful when confirming the safety of hospitalized patients. Also, for example, it is useful when a home caregiver confirms the safety of a care recipient (care recipient) in a separate room at home or in a remote place when going out. It is also useful when observing in a remote place, for example, to study the ecology of animals such as bears that are hibernating in a zoo.

DESCRIPTION OF SYMBOLS 1 ... Bed, 101 ... Body information image, A1 ... 1st measurement area | region, A2 ... 2nd measurement area | region, CA1 ... Output signal history storage means, CA2 ... Frequency component removal means, CA2a ... Frequency component removal means for heartbeat, CA2b ... Frequency component removing means for breathing, CA3 ... Frequency component intensity calculating means, CA4 ... Intensity normalizing means, CA5 ... Synthetic intensity calculating means, CA6 ... Frequency component extracting means, CA7a ... Heart rate calculating means, CA7b ... Respiration rate calculating means, CA11, CB11 ... physical information image display means, CA12 ... getting bed judging means, CA13 ... getting bed judging means, CA14, CB14 ... getting out bed notification means, CA15 ... leaving time measuring means, CA16 ... long-term bed leaving judgment means, CA17, CB17 ... long term Bed leaving notification means, CA18 ... heartbeat abnormality determination means, CA19, CB19 ... heartbeat abnormality notification means, CA20 ... breathing abnormality determination means, CA21, CB21 ... breathing abnormality notification means, CA22 Apnea discrimination means, CA23 ... Apnea time measurement means, CA24 ... Long-term apnea discrimination means, CA25, CB25 ... Long-term apnea notification means, CA26 ... Lay-down discrimination means, CA28 ... Non-sleep time measurement means, CA29 ... Long-term non-sleep Discriminating means, CA30, CB30 ... long-term non-sleep notification means, h ... heart rate, r ... respiration rate, S ... physical information measurement system, Si × TM1 ... apnea discrimination threshold, Sj × TM1 ... no-sleep discrimination threshold, SN1 ... 1st electromagnetic wave transmission / reception member, SN1a ... 1st electromagnetic wave irradiation part, SN1b ... 1st electromagnetic wave reception part, SN2 ... 2nd electromagnetic wave transmission / reception member, SN2a ... 2nd electromagnetic wave irradiation part, SN2b ... 2nd electromagnetic wave reception part, SN3 ... Subject detection member, TM2 ... apnea time, TM3 ... non-sleeping time, U ... physical information measuring device.

Claims (15)

A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a heartbeat component that is the frequency component corresponding to the heartbeat of the subject based on the combined intensity for each frequency component;
Heart rate calculating means for calculating a heart rate per unit time of the subject based on the extracted heart rate component;
A physical information image display means for displaying a physical information image for notifying the calculated heart rate per unit time of the subject;
An apparatus for measuring physical information, comprising: The frequency component extraction means for extracting a respiratory component that is the frequency component corresponding to the breathing of the subject based on the combined intensity for each frequency component;
Respiration rate calculating means for calculating the respiration rate per unit time of the subject based on the extracted respiration component;
The physical information image display means for displaying the physical information image for notifying the calculated heart rate and respiratory rate per unit time of the subject;
The physical information measuring device according to claim 1, further comprising: A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a respiratory component that is the frequency component corresponding to the breathing of the subject based on the combined intensity for each frequency component;
Respiration rate calculating means for calculating the respiration rate per unit time of the subject based on the extracted respiration component;
A physical information image display means for displaying a physical information image for notifying the computed respiratory rate per unit time of the subject;
An apparatus for measuring physical information, comprising: The combined intensity calculating means for calculating the combined intensity by calculating a product of intensity of each frequency component of the waveform of the history of the first output signal and the waveform of the history of the second output signal;
The body information measuring device according to claim 1, further comprising: Of the history waveform of each output signal, frequency component removing means for removing frequency components outside the passband from a preset minimum frequency to a maximum frequency;
The frequency component intensity calculating means for calculating the intensity of each frequency component in the passband;
The body information measuring device according to any one of claims 1 to 4, further comprising: A heartbeat frequency component removing means for removing a frequency component outside the heartbeat passband from a preset heartbeat minimum frequency to a heartbeat maximum frequency in the history waveform of each output signal;
Breathing frequency component removing means for removing a frequency component outside a breathing passband from a preset breathing minimum frequency to a breathing maximum frequency in a history waveform of each output signal;
The frequency component intensity calculating means for calculating the intensity of each frequency component in the heartbeat passband and calculating the intensity of each frequency component in the breathing passband;
Of the frequency components of the history waveform of the first output signal and the history waveform of the second output signal, the combined intensity for heartbeats obtained by combining the intensities of the frequency components in the passband for heartbeats is the frequency. The combined intensity calculating means for calculating for each frequency component, calculating for each frequency component, calculating for each component, and calculating for each frequency component a combined intensity for respiration in which the intensity of each frequency component in the respiration passband is combined.
The frequency component extracting means for extracting the heartbeat component based on the heartbeat synthetic intensity and extracting the respiratory component based on the respiratory synthetic intensity;
The physical information measuring device according to claim 5, further comprising: An object detection member for detecting the object on the bed;
When the subject detection member detects the subject and the heart rate or respiratory rate per unit time of the subject is calculated, it is determined that the subject is lying on the bed. Floor discrimination means;
When the subject detection member does not detect the subject and the heart rate and respiration rate per unit time of the subject are not calculated, it is determined that the subject is separated from the bed. Leaving bed discrimination means;
When it is determined that the subject is separated from the bed, a bed leaving notification means for notifying that the subject is separated from the bed;
The body information measuring device according to any one of claims 1 to 6, further comprising: A bed leaving time measuring means for measuring a bed leaving time which is an elapsed time since it was determined that the subject has left the bed;
A long-term bed leaving judging means for judging that the subject is separated from the bed for a long time when the bed leaving time during timing exceeds a preset bed leaving threshold;
When it is determined that the subject is away from the bed for a long time, long-term bed notification means for notifying that the subject is away from the bed for a long time;
The physical information measuring device according to claim 7, further comprising: When the subject detection member detects the subject and the heart rate per unit time of the subject is outside the normal heart rate range from a preset minimum heart rate to a maximum heart rate, A heartbeat abnormality determining means for determining that the heartbeat of the subject is in an abnormal state;
A heartbeat abnormality notification means for notifying that the heartbeat of the subject is in an abnormal state when it is determined that the heartbeat of the subject is in an abnormal state;
The physical information measuring device according to claim 7 or 8, further comprising: When the subject detection member detects the subject, and the respiratory rate per unit time of the subject is outside a normal breathing range from a preset minimum respiratory rate to a maximum respiratory rate, Breathing abnormality determining means for determining that the subject's breathing is in an abnormal state;
A breathing abnormality notification means for notifying that the subject's breathing is in an abnormal state when it is determined that the subject's breathing is in an abnormal state;
10. The body information measuring device according to claim 7, further comprising: An apnea discrimination means for discriminating that the subject is in an apnea state when the subject detection member detects the subject and the respiration rate per unit time of the subject is not calculated; ,
An apnea time measuring means for measuring an apnea time which is an elapsed time since it is determined that the subject is in an apnea state;
Long-term apnea discrimination means for discriminating that the subject is in an apnea state for a long time when the apnea time during timing exceeds a preset threshold for apnea discrimination;
Long-term apnea notification means for notifying that the subject is in a long-term apnea state when it is determined that the subject is in a long-term apnea state;
The body information measuring device according to claim 7, further comprising: Of the frequency components of the history waveform of the first output signal and the history waveform of the second output signal, the frequency components other than the heartbeat component and the respiratory component, and the body motion of the subject. The frequency component extracting means for extracting the body motion component which is the corresponding frequency component;
The strength of the body motion component included in the history waveform of the first output signal or the strength of the body motion component included in the history waveform of the second output signal is set to a preset threshold for turning determination. When it exceeds, the turning determination means for determining that the subject has turned over,
When it is determined that the subject has turned over, the bed notifying means for notifying that the subject has turned over; and
The body information measuring device according to claim 7, comprising: A non-sleep time measuring means for measuring a non-sleep time which is an elapsed time since it was determined that the subject has turned over;
Long-term non-sleep determination means for determining that the subject has not turned over for a long period of time when the non-sleep time exceeds a preset non-sleep determination threshold,
When it is determined that the subject has not turned over for a long time, a long-term non-sleeping notification means for notifying that the subject has not turned over for a long time;
The physical information measuring device according to claim 12, comprising: A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a heartbeat component that is the frequency component corresponding to the heartbeat of the subject based on the combined intensity for each frequency component;
Heart rate calculating means for calculating a heart rate per unit time of the subject based on the extracted heart rate component;
A physical information image display means for displaying a physical information image for notifying the calculated heart rate per unit time of the subject;
A body information measuring system characterized by comprising: A bed on which the subject lies;
A first electromagnetic wave irradiation unit configured to irradiate a first electromagnetic field to a first measurement region set in advance on the bed; and the first electromagnetic wave reflected from the subject lying in the first measurement region. A first electromagnetic wave receiving unit, and a first electromagnetic wave transmitting / receiving member that outputs a first output signal in response to the first electromagnetic wave received by the first electromagnetic wave receiving unit;
From a second electromagnetic wave irradiation unit that irradiates a second measurement region preset in a region shifted from the first measurement region of the bed with a second electromagnetic wave, and the subject lying in the second measurement region A second electromagnetic wave receiving unit that receives the reflected second electromagnetic wave, and a second electromagnetic wave transmitting / receiving member that outputs a second output signal in response to the second electromagnetic wave received by the second electromagnetic wave receiving unit; ,
Output signal history storage means for storing the history of the first output signal and the history of the second output signal;
The intensity of the frequency component contained in the waveform of the history of the first output signal stored in the output signal history storage means is calculated for each frequency component, and the second output stored in the output signal history storage means Frequency component intensity calculating means for calculating the intensity of the frequency component included in the waveform of the signal history for each frequency component;
A combined intensity calculating means for calculating, for each frequency component, a combined intensity obtained by combining the intensity of each frequency component of the history waveform of the first output signal and the history waveform of the second output signal;
Frequency component extraction means for extracting a respiratory component that is the frequency component corresponding to the breathing of the subject based on the combined intensity for each frequency component;
Respiration rate calculating means for calculating the respiration rate per unit time of the subject based on the extracted respiration component;
A physical information image display means for displaying a physical information image for notifying the computed respiratory rate per unit time of the subject;
A body information measuring system characterized by comprising:

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