JPWO2017150225A1 - Activity rhythm determination method and activity rhythm determination device - Google Patents

Abstract

An activity rhythm determination method and an activity rhythm determination apparatus capable of easily determining the state of an activity rhythm are provided. The activity rhythm determination method of the present invention measures the pulsation interval of a subject for a predetermined measurement time, and determines at least one of the following conditions [A] to [C].
[A] There is no position time zone in the awakening time zone.
[B] (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is (LF / HF) in the immediately preceding sleeping time zone Bigger than.
[C] The HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone.

Description

  The present invention relates to a method for determining whether there is any disturbance in the state of a person's activity rhythm and a determination apparatus therefor.

  It is known that disturbance of activity rhythm causes, for example, a decrease in concentration, distraction, fatigue, etc., and affects academic ability, exercise ability, a decrease in work efficiency, the onset of depression, and the like. For this reason, observing whether the activity rhythm is disturbed is useful for living a healthy social life, and thus effective for early detection of diseases and signs thereof. For example, Patent Document 1 discloses a storage unit that stores a sleep state, a calculation unit that calculates sleep regularity based on the plurality of stored sleep states, and a sleep quality based on the sleep regularity. And a sleep state evaluation device comprising: an evaluation means for evaluating a sleep state, and evaluation is performed using factors such as a daytime sleep time and a daytime bedtime. However, since the sleep state evaluation apparatus described in Patent Document 1 needs to be arranged on a mattress, the measurement place is limited, and the state of activity rhythm cannot be easily determined.

Japanese Patent Laying-Open No. 2015-171555

  An object of the present invention is to provide an activity rhythm determination method and an activity rhythm determination apparatus that can easily determine the state of an activity rhythm.

  The present inventors are studying a method for determining an activity rhythm using easily measurable biological information. In this study, the autonomous state based on the presence / absence of a supine position during awakening and sleeping and the pulse interval of the subject By evaluating the activity state of the nervous system, it was thought that the presence or absence of disturbance of activity rhythm can be easily acquired.

That is, the activity rhythm determination method of the present invention is characterized in that the pulsation interval of the subject is measured for a predetermined measurement time, and at least one of the following conditions [A] to [C] is determined.
[A] There is no position time zone in the awakening time zone.
[B] (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is (LF / HF) in the immediately preceding sleeping time zone Bigger than.
[C] The HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone.
Here, LF is a value obtained by integrating the power spectrum obtained by including the step of converting the beat interval into the frequency spectrum from frequencies Lf1 to Lf2, and HF is a value obtained by integrating the power spectrum from frequencies Hf1 to Hf2. Hf1> Lf1 and Hf2> Lf2.
According to the condition [A] of the activity rhythm determination method of the present invention, the state of the activity rhythm can be easily determined. Further, according to the conditions [B] and [C] of the activity rhythm determination method of the present invention, the state of the activity rhythm can be determined objectively and easily.

In the activity rhythm determination method of the present invention, the acceleration TA in the height direction of the subject is measured, the negative acceleration NA is calculated according to the following condition [D], the supine time zone is calculated, the awakening time zone and the sleep time It is preferable to classify the time zone.
[D] (1) Calculation of Negative Acceleration NA (1a) When TA ≧ 0 when the subject is standing, NA = (− 1) × (TA)
(1b) If TA <0 when the subject is standing, NA = TA
(2) Calculation of the prone time zone (2a) First prone time zone L _m1 : Time zone in which NA ≧ C1 (C1 is a constant) is equal to or greater than the first predetermined time T ₁ (2b) Second prone time zone L _m2 : There are two or more first _saddle time zones L _m1 , and a gap time zone L _sm where NA <C1 between two adjacent first _saddle time zones L _m11 and L _m12 is a second predetermined time. T ₂ If within the two bands first supine time adjacent L _m11, L _m12 and pore hours L _sm total time period of (3) awake time zone and sleep time zone classification (3a) sleeping time zone : The longest time zone among the first prone time zone L _m1 and the second prone time zone L _m2 during the predetermined measurement unit time (3b) Awakening time zone: Time excluding the sleep time zone from the predetermined measurement unit time In the above condition [D], the sleep time zone in the predetermined measurement unit time is specified as one, so the data comparison between the awake time zone and the sleep time zone Cormorant condition [B], it can be reduced determination count by [C].

In the activity rhythm determination method of the present invention, it is preferable to measure the acceleration TA in the height direction of the subject, calculate the negative acceleration NA according to the following condition [E], and calculate the supine time zone.
[E] (1) Calculation of negative acceleration NA (1a) When TA ≧ 0 when the subject is standing, NA = (− 1) × (TA)
(1b) If TA <0 when the subject is standing, NA = TA
(2) Calculation of supine time zone
Supine time zone: time zone satisfying NA ≧ C1 (C1 is a constant) In the above condition [E], the condition (2) relating to the calculation of the supine time zone is simplified, so that the supine time zone is easy. Can be calculated.

  In the condition [B], (LF / HF) in the sleep time zone is an average value of (LF / HF) in the sleep time zone, and (LF / HF) in the wake time zone is (( The average value of (LF / HF) is preferable. Thereby, since it becomes easy to compare (LF / HF) in the sleep time zone and (LF / HF) in the awakening time zone, it is possible to easily determine the activity rhythm.

  In the condition [C], it is preferable that HF in the sleep time zone is an average value of HF in the sleep time zone, and HF in the wake time zone is an average value of HF in the wake time zone. Thereby, since it becomes easy to compare HF of a sleep time slot | zone and HF of an awakening time slot | zone, activity rhythm can be determined easily.

  Under the condition [C], the increase rate of HF in the sleep time zone with respect to HF in the immediately preceding awake time zone is more than 10%, and the decrease rate of HF in the awake time zone with respect to HF in the immediately preceding sleep time zone is 10%. It is preferable to determine that it is super. Since HF preferably has a larger difference between the awakening time zone and the sleeping time zone than (LF / HF), the condition may be set in this way.

  As the pulsation interval, it is preferable to use an RR interval that is an interval between an R wave and an R wave in an electrocardiogram signal. This is because the R wave has a clear signal peak, so that the erroneous recognition of the peak position does not easily occur, and the accuracy of the pulsation interval becomes high.

In addition, the activity rhythm determination device of the present invention is a value obtained by including a measurement unit that measures the pulsation interval of the subject for a predetermined measurement time, and a step of performing frequency spectrum conversion of the pulsation interval (hereinafter, “power spectrum”). A value obtained by definite integration from the frequency Lf1 to Lf2 (hereinafter referred to as “LF”) and a value obtained by definite integration from the frequency Hf1 (> Lf1) to Hf2 (> Lf2). (Hereinafter referred to as “HF”)
And a determination unit that determines at least one of the following conditions [A] to [C].
[A] There is no position time zone in the awakening time zone.
[B] (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is (LF / HF) in the immediately preceding sleeping time zone Bigger than.
[C] The HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone.
According to the condition [A] of the activity rhythm determination device of the present invention, the state of the activity rhythm can be easily determined. Further, according to the conditions [B] and [C] of the activity rhythm determination device of the present invention, the state of the activity rhythm can be determined objectively and easily.

  According to the condition [A] of the activity rhythm determination method and the activity rhythm determination apparatus of the present invention, the state of the activity rhythm can be easily determined. Further, according to the conditions [B] and [C] of the present invention, the state of the activity rhythm can be determined objectively and easily.

FIG. 1 is an explanatory diagram of power spectrum integration according to the present invention. FIG. 2 is a block diagram showing the configuration of the activity rhythm determination apparatus according to Embodiment 1 of the present invention. FIG. 3 is a block diagram showing the configuration of the activity rhythm determination apparatus according to Embodiment 2 of the present invention. FIG. 4 is a block diagram showing the configuration of the activity rhythm determination apparatus according to Embodiment 3 of the present invention. FIG. 5 is a block diagram showing the configuration of the activity rhythm determination apparatus according to Embodiment 4 of the present invention. FIG. 6 is a block diagram showing a configuration of an activity rhythm determination apparatus according to Embodiment 5 of the present invention. FIG. 7 is a block diagram showing a configuration of an activity rhythm determination apparatus according to Embodiment 6 of the present invention.

1. Activity Rhythm Determination Method The activity rhythm determination method of the present invention is characterized by measuring the pulsation interval of a subject for a predetermined measurement time and determining at least one of the following conditions [A] to [C]. To do.
[A] There is no position time zone in the awakening time zone.
[B] (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is (LF / HF) in the immediately preceding sleeping time zone Bigger than.
[C] The HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone.
Here, LF is a value obtained by integrating the power spectrum obtained by including the step of converting the beat interval into the frequency spectrum from frequencies Lf1 to Lf2, and HF is a value obtained by integrating the power spectrum from frequencies Hf1 to Hf2. Hf1> Lf1 and Hf2> Lf2.
According to the method of the condition [A] of the present invention, it is possible to easily determine the state of the activity rhythm by determining the presence / absence of the supine time period during the awakening time period. Further, according to the method of the conditions [B] and [C] of the present invention, it is possible to objectively and easily observe the transition of the values of (LF / HF) and HF in the awakening time zone and the sleeping time zone. The state of activity rhythm can be determined.

  The activity rhythm determination method of the present invention measures the pulsation interval of a subject for a predetermined measurement time. The pulsation interval refers to the interval between heartbeats or pulses (unit: ms). The heartbeat interval is acquired by reading the interval between the R wave and the R wave from the electrocardiogram or by measuring the interval between adjacent heartbeats. The pulse interval is acquired by measuring the interval between adjacent pulses. The beat interval or its oscillation is said to indicate autonomic nerve activity.

  As the pulsation interval, it is preferable to use an RR interval (hereinafter referred to as “RRI”) that is an interval between the R wave and the R wave in the electrocardiogram signal. This is because the peak of the R wave is not clearly recognized, and the peak position is less likely to be erroneously recognized.

  The predetermined measurement time refers to the total time for measurement. In the conditions [B] and [C], since the data in the sleep time zone and the immediately preceding awake time zone, and the awake time zone and the immediately preceding sleep time zone are used, the predetermined measurement time is two or more sleep time zones, It is preferable that the time length is such that one or more awakening time zones can be obtained. Alternatively, the predetermined measurement time may be a time length in which two or more awakening time zones and one or more sleeping time zones are obtained. Therefore, the predetermined measurement time is preferably 2 days or more, more preferably 3 days or more, and further preferably 4 days or more. In addition, as the predetermined measurement time is longer, more reliable data can be acquired. However, in consideration of the burden on the subject, the predetermined measurement time can be set, for example, within 14 days, more preferably within 10 days. .

1-1. Condition [A]
In condition [A], it is determined that there is no lying time zone in the awakening time zone. The supine time zone indicates sleep outside the sleeping time zone or nap or nap, but if you have irregular life, chronic fatigue, depression, insomnia, etc. There is a tendency that the time zone is seen. For this reason, according to condition [A], the presence or absence of disturbance of an activity rhythm can be determined by the presence or absence of a lying time zone.

  In the present invention, the awakening time zone refers to a time zone in which the subject is awake, that is, awake. On the other hand, the sleep time zone is a time zone during which the subject is sleeping and refers to a time zone other than the awakening time zone. The awakening time zone and the sleeping time zone show various aspects depending on the living environment and mental state of the subject, and the time length and the time zone are not particularly limited.

  In the present invention, the wake-up time zone and the sleep time zone may be classified by self-reporting the sleep start time and the wake-up start time through a questionnaire to the subject. You may carry out by the input means provided. In addition, for example, a known sleep state measuring method described in JP 2010-179133 A or JP 2009-297474 A can be applied. In order to classify the awakening time zone and the sleep time zone more objectively, it is preferable to use acceleration measured along with the movement of the subject.

In the present invention, the acceleration is a composite value of the acceleration accompanying the movement of the subject and the gravitational acceleration acting on the subject, and is represented by a ratio to the gravitational acceleration g (= 9.8 m / s ² ) ( Unit: dimensionless quantity). When the subject is standing and there is no movement, the magnitude of acceleration in the height direction of the subject is 1.

  For classification of the awakening time zone and the sleep time zone, it is preferable to use a negative acceleration NA calculated from the acceleration TA in the height direction of the subject. In general, if the accelerometer is adjusted so that the acceleration in the height direction during sleep time is negative when standing, the acceleration in the height direction during sleep time is compared with the acceleration in the height direction during awake time This is because it tends to be large. Thus, the acceleration in the height direction is suitable for the classification of the awakening time zone and the sleeping time zone because there is a difference between the awakening time zone and the sleeping time zone. In the present invention, the height direction is a direction from the foot of the subject toward the head.

A method for classifying the awakening time zone and the sleeping time zone using the acceleration TA in the height direction of the subject will be described. In the present invention, the acceleration TA in the height direction of the subject is measured, the negative acceleration NA is calculated according to the following condition [D], the supine time zone is calculated, and the awakening time zone and the sleep time zone are classified. It is preferable. Hereinafter, the classification method of the awakening time zone and the sleeping time zone using the following condition [D] may be referred to as a “first classification method”.
[D] (1) Calculation of Negative Acceleration NA (1a) When TA ≧ 0 when the subject is standing, NA = (− 1) × (TA)
(1b) If TA <0 when the subject is standing, NA = TA
(2) Calculation of the prone time zone (2a) First prone time zone L _m1 : Time zone in which NA ≧ C1 (C1 is a constant) is equal to or greater than the first predetermined time T ₁ (2b) Second prone time zone L _m2 : There are two or more first _saddle time zones L _m1 , and a gap time zone L _sm where NA <C1 between two adjacent first _saddle time zones L _m11 and L _m12 is a second predetermined time. If it is within T _{2, the} time zone that is the sum of the two adjacent first lying time zones L _m11 , L _m12 and the gap time zone L _sm (3) Classification of awakening time zone and sleep time zone (3a) Sleep time zone : The longest time zone among the first prone time zone L _m1 and the second prone time zone L _m2 during the predetermined measurement unit time (3b) Awakening time zone: Time excluding the sleep time zone from the predetermined measurement unit time band

  In the first classification method shown as the condition [D], the sleep time zone in the predetermined measurement unit time is specified as one, so the condition [B] for comparing the data in the awake time zone and the sleep time zone, The number of determinations by [C] can be reduced.

[D] (1) Calculation of negative acceleration NA The negative acceleration NA is calculated from the acceleration TA in the height direction of the subject. As shown in the conditions (1a) and (1b), the negative acceleration is a value obtained by multiplying the acceleration in the height direction by -1 when the acceleration TA in the height direction when the subject is standing is 0 or more. If the acceleration TA in the height direction is a negative value, the negative value is set as the negative acceleration NA.

[D] (2) Calculation of the supine time zone The prone time zone is calculated by dividing it into two types, a first prone time zone and a second prone time zone. As conditions (2a), the first recumbent hours L _m1 NA ≧ C1 (C1 is a constant) is the time period is a first predetermined time above T _1. In the calculation of the first decubitus time zone L _m1 , a threshold value based on the first predetermined time T ₁ is provided in order to improve the classification accuracy of the awakening time zone and the sleep time zone. For example, the first predetermined time T ₁ can be set to preferably 30 minutes, more preferably 45 minutes, and still more preferably 1 hour. The time zone in which NA ≧ C1 is less than the first predetermined time T ₁ can also be said to be in a lying position, but from the viewpoint of activity rhythm such as nap and nap in a relatively short time, it should be evaluated as original sleep In order to prevent the time that cannot be classified into the sleep time zone, in this classification method, the time zone where NA ≧ C1 is less than the first predetermined time T ₁ is not regarded as the prone time zone.

  In the condition [D] (2), the supine time zone may be calculated using only the condition (2a). However, depending on the subject, the posture other than the supine position is frequently taken during the sleeping hours, and in this case, it is difficult to estimate the sleeping hours. For this reason, it is preferable to combine the method of calculating the second saddle time zone according to the condition (2b) as in the above [D] with the condition (2a).

As in the condition (2b), the second saddle time zone L _m2 includes two or more first _saddle time zones L _{m1 and} an NA between two adjacent first _saddle time zones L _m11 and L _m12. When the gap time zone L _sm which is <C1 is within the second predetermined time T _2, it is a time zone obtained by summing the two adjacent first _prone time zones L _m11 and L _m12 and the gap time zone L _sm . The second saddle time zone is calculated in this way when the first saddle time zone L _m1 is chopped, and the gap between the two first _saddle time zones L _m11 and L _m12 is _calculated. This is for classification as one saddle time zone (second saddle time zone L _m2 ) including the time zone L _sm . Here, the second predetermined time T ₂ are, for example, preferably 30 minutes, more preferably 45 minutes, can be more preferably set to 1 hour. Further, the first predetermined time T ₁ and the second predetermined time T ₂ may be the same or different.

  The value of the constant C1 (unit: dimensionless amount) is not particularly limited, but is preferably, for example, -0.85, more preferably -0.8, and further -0.75. preferable.

[D] (3) Classification of awakening time zone and sleeping time zone According to the condition (3a), the longest of the first prone time zone L _m1 and the second prone time zone L _m2 during the predetermined measurement unit time The time zone is set as the sleep time zone. Moreover, as a condition (3b), let the time remove | excluding the sleep time slot | zone from the predetermined measurement unit time be an awakening time slot | zone.

  The predetermined measurement unit time is a time length set in order to estimate a sleep time zone for each day. The predetermined measurement unit time is preferably 12 hours or more, more preferably 18 hours or more, and preferably within 24 hours. Since both day shifters and night shift workers are generally awake at around 18:00, the starting point of the predetermined measurement unit time is preferably set from 17:00 to 19:00.

The calculation of the prone position time zone may be performed by having the subject self-report the prone position start time and the end time in addition to the calculation method of [D] (2) above. Alternatively, the acceleration TA in the height direction of the subject may be measured, the negative acceleration NA may be calculated according to the following condition [E], and the supine time zone may be calculated.
[E] (1) Calculation of negative acceleration NA (1a) When TA ≧ 0 when the subject is standing, NA = (− 1) × (TA)
(1b) If TA <0 when the subject is standing, NA = TA
(2) Calculation of supine time zone
Supine time zone: Time zone satisfying NA ≧ C1 (C1 is a constant)

  Condition [E] (1) is the same method as condition [D] (1). Further, the condition [E] (2) is a time zone satisfying NA ≧ C1 and the saddle time zone is simplified. Since the conditional expression is simplified, this method makes it easy to set the saddle time zone. Can be calculated. The constant C1 can be set similarly to the above condition [D].

It is also possible to classify the awakening time zone and the sleeping time zone using the supine time zone calculated according to the condition [E]. A second classification method of the awakening time zone and the sleeping time zone using the supine time zone calculated by the condition [E] is shown in the following condition [F].
[F] (1) Awakening time zone and sleep time zone classification (1a) Sleeping time zone: Sum of supine time zones calculated in condition [E] (2) during a predetermined measurement unit time (1b) Awakening time zone : Time zone excluding the sleep time zone calculated by the condition [F] (1a) from the predetermined measurement unit time According to this method, the awake time zone and the sleep time zone can be easily classified. It is suitable when it is necessary to classify the awake time zone and the sleep time zone in real time.

A third classification method of the awakening time zone and the sleeping time zone using the supine time zone calculated by the condition [E] is shown in the following condition [G].
[G] (1) Classification of awakening time zone and sleeping time zone (1a) Sleeping time zone: longest time zone among the supine time zones calculated in condition [E] (2) during the predetermined measurement unit time (1b ) Awakening time zone: A time zone excluding the sleep time zone calculated in the condition [G] (1a) from the predetermined unit time. This method can be used to sleep continuously without having to wake up at a halfway time. Effective for examiners.

A fourth classification method of the awakening time zone and the sleeping time zone using the supine time zone calculated by the condition [E] is shown in the following condition [H].
[H] (1) Classification of awakening time zone and sleeping time zone (1a) Sleeping time zone: The third predetermined time T among the supine time zones calculated in the condition [E] (2) during the predetermined measurement unit time. Total of _three or more consecutive time zones (1b) Awakening time zone: During the predetermined measurement unit time, the time zone excluding the sleep time zone calculated in the condition [H] (1a) The third predetermined time T ₃ is other than during sleep It is a time length set in order to regard the time zone estimated to be in the recumbent state as the awakening time zone. Third predetermined time T _3, for example 15 minutes or more, preferably 30 minutes or more, more preferably be at least 1 hour. In the fourth classification method, since the substantial sleep time zone is estimated by integrating the sleep time zones classified into small pieces, the patient with insomnia with mid-wake awakening that occurs at a half-way time during sleep. Effective for examiners.

  As described above, when the awakening time zone and the sleep time zone are classified using acceleration, for example, the acceleration represented by the acceleration TA in the height direction and the negative acceleration NA performs a morphological operation on the acceleration-time waveform. It is preferable that the value is after. The morphological operation is used for noise removal in image processing. For this reason, if the value after performing the morphological operation on the acceleration-time waveform is applied to each conditional expression, the obtained acceleration is compared with a predetermined measurement time for a short time (for example, a predetermined measurement time). Values that change within 1/150 hours) are eliminated. For this reason, the whole outline of the acceleration-time waveform is extracted, and it becomes easy to classify the awakening time zone and the sleeping time zone. The morphological operation may be performed on the acceleration TA in the height direction or on the negative acceleration NA.

  In order to shorten the processing time required for the morphological operation, it is also preferable to perform the morphological operation on the acceleration-time waveform that has been binarized. In the binarization process, for example, when the acceleration is a predetermined value (threshold value) C2 or more, the acceleration is regarded as 0, and when the acceleration is less than the predetermined value C2, the acceleration is regarded as 1. The value of the predetermined value C2 is not particularly limited, but is preferably, for example, −0.85, more preferably −0.8, and further preferably −0.75.

  The morphological operations include, for example, an expansion operation for performing a process for thickening a line, a contraction operation for performing a process for thinning a line, an opening process for performing an expansion operation after the contraction calculation, and a closing process for performing a contraction operation after the expansion operation. In the present invention, when the awakening time zone and the sleep time zone are classified using the acceleration after the morphological calculation, the morphological calculation is preferably at least one of an opening process and a closing process performed in a predetermined time width. . It is more preferable to perform both the opening process and the closing process as the morphological operation. By combining the expansion operation and the contraction operation in this way, it becomes easier to extract the entire contour of the acceleration-time waveform, and thus it becomes easier to classify the awakening time zone and the sleep time zone.

  The number of times the opening process and the closing process are performed is not particularly limited, but the opening process and the closing process are each preferably performed once or more, and more preferably each of the opening process and the closing process is performed twice or more.

  The time width for performing the expansion operation and the contraction operation may be set as appropriate. For example, the time width of the first opening process and the closing process is set to 2 minutes, and the time width of the second opening process and the closing process is set as follows. It can be 5 minutes. Thus, it is preferable to increase the time width at the time of processing each time the number of processing is repeated. In this way, by increasing the time width of the opening process and the closing process in stages, it is possible to suppress removal of acceleration data that has changed in a short time compared to the predetermined measurement time.

1-2. Condition [B], [C]
The condition [B] uses (LF / HF), and the condition [C] uses HF to determine the activity rhythm. First, LF and HF will be described.

LF is a value obtained by integrating the power spectrum obtained by including the step of frequency spectrum conversion of the pulsation interval, which is the time signal f, from frequencies Lf1 to Lf2. HF is a value obtained by defining the power spectrum from frequencies Hf1 to Hf2. The integrated values are Hf1> Lf1 and Hf2> Lf2. For example, LF is a definite integral from frequency Lf1 to Lf2 of a power spectrum F ² (first power spectrum) obtained by squaring a frequency spectrum converted from a beat interval which is a time signal f (frequency spectrum F). HF can be a value obtained by definitely integrating the power spectrum F ² (first power spectrum) from the frequency Hf1 (> Lf1) to Hf2 (> Lf2). The unit of LF and HF calculated using the first power spectrum F ² is ms ² . As a frequency spectrum conversion method, for example, fast Fourier transform (FFT), wavelet analysis, maximum entropy method, or the like can be used. In this specification, the case where FFT is used is described as an example, but other methods can be used as a matter of course.

In this specification, the discrete Fourier transform G of the pulsation interval RRI _{k obtained} by re-sampling the pulsation interval by spline interpolation and represented by the sampling interval Δt is expressed by the following equation (I), and the power spectrum F ² (first The power spectrum (unit: ms ² / Hz) is expressed by the following formula (II). Here, k represents a time series, N represents the number of data, S is an arbitrary scale, and generally S = 1 in the power spectrum.

  On the other hand, as the values of LF and HF, the power spectrum F (second power spectrum) (unit: ms) obtained from the value obtained by frequency spectrum conversion of the pulsation interval is definitely integrated in a predetermined section. Included in the rhythm determination method. Thus, if the value obtained by converting the pulsation interval to the frequency spectrum is used as the power spectrum, the values of LF and HF can be calculated more easily. The units of LF and HF calculated using the second power spectrum F are dimensionless quantities. The power spectrum F (second power spectrum) is represented by the following formula (III).

Next, the detailed calculation method of LF and HF is demonstrated using FIG. FIG. 1 is an explanatory diagram of power spectrum integration according to the present invention. The vertical axis in FIG. 1 is power spectral density (unit: ms ² / Hz), and the horizontal axis is frequency (unit: Hz). LF is a value obtained by definite integration of a power spectrum (for example, the first power spectrum F ² ) from, for example, 0.04 Hz (Lf1) to 0.15 Hz (Lf2), and the hatched portion in FIG. It is an area. On the other hand, HF is a value obtained by definite integration of a power spectrum (for example, the first power spectrum F ² ) from, for example, 0.15 Hz (Hf1) to 0.4 Hz (Hf2), and is hatched by a vertical line in FIG. It is the area of the part. In FIG. 1, the integration range is set so that both Lf2 and Hf1 are equal to 0.15 Hz. However, if the relationship of Lf1 <Hf1 and Lf2 <Hf2 is satisfied, Lf2 and Hf1 are the same value. May be different values. Here, the method of power spectrum integration has been described using the first power spectrum F ² , but the definite integration using the second power spectrum F can be performed in the same manner. Before determining the condition [B] or [C], which will be described later, it is determined whether or not the calculated LF and HF include what should be regarded as an abnormal value, and the value determined as an abnormal value is determined. It is preferable to exclude from the determination target. Thereby, it can prevent that an abnormal value influences the determination result of activity rhythm.

  The power spectrum obtained by frequency spectrum conversion is divided into a component derived from blood pressure fluctuation, which is also referred to as a Mayer-Wave related component, and a component HF derived from respiration. The blood pressure fluctuation component LF is a power spectrum around 0.1 Hz, and is related to both sympathetic nerve activity and parasympathetic nerve activity. On the other hand, the component HF derived from respiration has a power spectrum around 0.3 Hz and is considered to be related to parasympathetic nerve activity. From the above, it is preferable that the integration range of LF indicating sympathetic nerve activity and parasympathetic nerve activity includes at least 0.1 Hz and Lf1 <0.1 <Lf2. Further, Lf1 is more preferably 0.03 Hz, and further preferably 0.04 Hz. Lf2 is more preferably 0.16 Hz, and further preferably 0.15 Hz. Further, the integration range of HF showing parasympathetic nerve activity preferably includes at least 0.3 Hz, and Hf1 <0.3 <Hf2. Hf1 is more preferably 0.14 Hz, and further preferably 0.15 Hz. Hf2 is more preferably 0.41 Hz, and further preferably 0.4 Hz.

  In the condition [B] of the activity rhythm determination method of the present invention, (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is smaller. It is determined that it is greater than (LF / HF) of the immediately preceding sleep time zone. As described above, since LF indicates both sympathetic nerve activity and parasympathetic nerve activity, LF / HF represents the superiority of sympathetic nerve activity over parasympathetic nerve activity. Therefore, in the present invention, LF / HF is used as an index indicating sympathetic nerve activity. Condition [B] is a method for determining the presence or absence of disturbance in the activity rhythm by observing whether the value of LF / HF indicating sympathetic nerve activity changes regularly. Sympathetic nerve activity during the awakening period usually tends to be more active than during the sleeping period.

  In the condition [B], (LF / HF) in the sleep time zone is an average value of (LF / HF) in the sleep time zone, and (LF / HF) in the wake time zone is (( The average value of (LF / HF) is preferable. Thereby, since it becomes easy to compare (LF / HF) in the sleep time zone and (LF / HF) in the awakening time zone, it is possible to easily determine the activity rhythm.

  In order to improve the determination accuracy, in the condition [B], (LF / HF) in the sleep time zone is smaller than all values of (LF / HF) in the immediately preceding wakeup time zone, and It is preferable to determine that (LF / HF) in the time zone is larger than all values of (LF / HF) in the immediately preceding sleep time zone.

  In the condition [C] of the activity rhythm determination method of the present invention, the HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone. judge. As described above, HF indicates parasympathetic nerve activity as well as the beat interval. Therefore, the condition [C] is a method for determining the presence / absence of disturbance in the activity rhythm by observing whether the value of HF indicating parasympathetic nerve activity changes regularly. Parasympathetic nerve activity during the awakening period usually tends to be lower than during the sleeping period.

  In the condition [C], it is preferable that HF in the sleep time zone is an average value of HF in the sleep time zone, and HF in the wake time zone is an average value of HF in the wake time zone. Thereby, since it becomes easy to compare HF of a sleep time slot | zone and HF of an awakening time slot | zone, activity rhythm can be determined easily.

  In the above condition [C], the increase rate of HF in the sleep time zone with respect to HF in the immediately preceding awakening time zone is more than 5% (more preferably more than 10%), and the awakening time zone for HF in the immediately preceding sleeping time zone It is preferable to determine that the decrease rate of HF is more than 5% (more preferably more than 10%). Since HF preferably has a larger difference between the awakening time zone and the sleeping time zone than (LF / HF), the condition may be set in this way.

  The activity rhythm determination method of the present invention can combine conditions [A] to [C]. The determination of the activity rhythm may be performed using, for example, the conditions [A] and [B], may be performed using the conditions [A] and [C], and the conditions [B] and [C] are determined. May be used. In order to increase the determination accuracy, it is preferable to perform determination using all of the conditions [A] to [C].

  When the determination is made using all of the conditions [A] to [C], when each condition is satisfied and when the condition is not satisfied, a score to be given is determined in advance, and the total score exceeds a predetermined standard It may be determined that the activity rhythm is disturbed. For example, as shown in Table 1, 0 is given when the condition [A] is satisfied, 1 is given when the condition is not satisfied, 0 is given when the condition [B] is satisfied, and 3 is given when the condition is not satisfied. The standard is defined as 0 points when [C] is satisfied and 3 points when [C] is not satisfied. If the total score is high, the activity rhythm needs to be improved, and if the total score is low, it may be determined that there is no problem in the activity rhythm.

  If the autonomic nervous system determined using LF / HF or HF is considered to have a greater influence on the disturbance of the activity rhythm than when there is no lying time zone in the awakening time zone, Table 1 As shown in FIG. 6, the score of the condition [A] may be set lower than the conditions [B] and [C]. Moreover, it is not limited to the example of Table 1, Condition [A] ≧ Condition [B] ≧ Condition [C], Condition [A] ≧ Condition [C] ≧ Condition [B], Condition [C] ≧ Condition [A] The score may be set lower or higher in the order of ≧ condition [B].

2. Activity Rhythm Determination Device The activity rhythm determination device of the present invention includes a measurement unit, a processing unit, and a determination unit. The measurement unit is at least an electrocardiograph or a heart rate sensor that measures the heartbeat of the subject, or a pulse wave sensor that measures the pulse wave of the subject and obtains the pulse. The processing unit performs frequency spectrum conversion based on the beat interval measured by the measurement unit, calculates a power spectrum integrated value, and calculates LF and HF. The determination unit determines whether each condition is satisfied using the data obtained by the processing unit. The processing unit and the determination unit are a computer, a tablet terminal, a smartphone, a measurement device, and the like including software and applications that can create data used for determination and determine various conditions.

(Embodiment 1)
FIG. 2 is a block diagram showing the configuration of the activity rhythm determination apparatus 1 according to Embodiment 1 of the present invention. 2 includes a sensor 10 and an analyzer 30. The activity rhythm determination apparatus 1 illustrated in FIG.

  The sensor 10 includes a measurement unit 20 including a pulsation measurement unit 25 that measures a pulsation interval of a subject for a predetermined measurement time. The sensor 10 is small and light, and can be attached to the subject's skin with the electrode (not shown) on the back of the main body in close contact with the subject's chest, so it is hidden under clothes. Inconspicuous. The activity rhythm determination device 1 of the present invention preferably uses an RR interval (RRI) that is an interval between an R wave and an R wave in an electrocardiogram signal as a beating interval. This is because the peak of the R wave is not clearly recognized, and the peak position is less likely to be erroneously recognized.

  The pulsation measurement unit 25 measures an electrocardiogram signal in a state where the electrode is in close contact with the subject's chest, calculates an RRI based on the electrocardiogram signal, and transmits the RRI to the processing unit 40 of the analyzer 30. The pulsation measuring unit 25 of the sensor 10 calculates the RRI based on the electrocardiogram signal, but the RRI may be calculated by the processing unit 40 described later.

  The pulsation measurement unit 25 may measure a pulse wave instead of measuring the heartbeat. The pulse wave can be measured by irradiating a human fingertip or earlobe with near infrared light having a wavelength of 700 nm to 1200 nm, and measuring the amount of reflection of the near infrared light in a contact or non-contact manner. When measuring pulse waves, there is the advantage that it is relatively easy to attach the measuring instrument to the body, especially when using a non-contact measuring type, it eliminates the hassle of attaching the measuring instrument to the body, so it is widely spread there's a possibility that. The pulse interval can be obtained from the interval between adjacent peaks of the pulse wave measured in this way.

  As a method for transmitting the beat interval data measured by the measuring unit 20 to the receiving unit 50 of the processing unit 40 of the analyzer 30, wireless communication or wired communication may be used. In particular, when transmitting and receiving data by wireless communication, it is preferable to reduce the frequency of transmission and reception by, for example, transmitting three RRIs in a lump in order to improve the holding of a built-in battery.

  From the viewpoint of suppressing power consumption, it is preferable that the sensor 10 according to the present invention is automatically turned off after a predetermined time has elapsed since the power was turned on. The predetermined time may be set in consideration of the number of data necessary for determining the activity rhythm, and can be set to 24 hours or 48 hours, for example.

  The analyzer 30 includes a processing unit 40 and a determination unit 60, and the processing unit 40 includes a reception unit 50, a frequency spectrum conversion unit 51, and a power spectrum integration calculation unit 52. The receiving unit 50 receives the RRI transmitted from the sensor 10.

The frequency spectrum conversion unit 51 converts the RRI that is a time signal transmitted from the reception unit 50 into a frequency spectrum using a frequency spectrum conversion method such as FFT. Next, the power spectrum integration calculation unit 52 calculates LF and HF by calculating a power spectrum from the spectrum obtained by the frequency spectrum conversion unit 51 and performing integration in a predetermined frequency range. Specifically, the following processing is performed. First, when a power spectrum is calculated from the frequency spectrum obtained by the frequency spectrum conversion unit 51, a power spectrum density is plotted on the vertical axis and a frequency distribution map is plotted on the horizontal axis. Next, LF and HF are obtained by integrating the power spectrum in the range of Lf1 to Lf2 and the range of Hf1 to Hf2. Note that Lf1 <Hf1 and Lf2 <Hf2. The specific calculation method of the power spectrum is as described in “1. Activity rhythm determination method”. For example, the first power spectrum F ² may be used as the power spectrum. It may be used. Although not shown, the processing unit 40 of the analyzer 30 determines whether the LF and HF calculated by the power spectrum integration calculation unit 52 should be regarded as abnormal values or not. A detection unit and an LF / HF abnormal value removal unit that removes data determined as an abnormal value by the LF / HF abnormal value detection unit from the determination target may be provided. Thereby, since the data from which the abnormal value is removed can be transmitted to the determination unit 60, the abnormal value can be prevented from affecting the determination result of the activity rhythm.

The determination unit 60 of the activity rhythm determination apparatus of the present invention determines whether at least one of the following conditions [A] to [C] is satisfied using the data created by the processing unit 40. For example, when it is determined that any one of the conditions [A] to [C] is satisfied, it can be evaluated that the activity rhythm is not significantly disturbed, and when it is determined that the conditions are not satisfied, the activity rhythm is disturbed. Can be evaluated.
[A] There is no position time zone in the awakening time zone.
[B] (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is (LF / HF) in the immediately preceding sleeping time zone Bigger than.
[C] The HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone.

  The analyzer 30 is preferably provided with a notification unit 70 that notifies the subject or the like of the determination result of the activity rhythm state from the determination unit 60. The notification method is not particularly limited, such as sound, a still image, and a moving image. It is also possible to change the notification content according to the expert knowledge level of the notification subject such as a specialist such as a doctor or a counselor, the subject or their family. Here, an example in which the notification unit 70 is provided in the activity rhythm determination device 1 is shown. However, even if the determination result is transmitted to a notification device different from the activity rhythm determination device 1 and the result is notified to the subject or the like. Good. Examples of the notification device include an external monitor, a mobile phone, a smartphone, a tablet terminal, a speaker, and an earphone.

  Although not shown, the processing unit of the analyzer may be provided with input means for inputting the awakening time zone and the sleep time zone, and the supine time zone.

(Embodiment 2)
The second embodiment is a configuration example of a device having a function of removing abnormal values of beat interval data. FIG. 3 is a block diagram showing the configuration of the activity rhythm determination device 2 according to Embodiment 2 of the present invention. The activity rhythm determination device 2 illustrated in FIG. 3 includes a sensor 10 and an analyzer 31. In addition, the same number is attached | subjected to the component similar to the activity rhythm determination apparatus 1 of Embodiment 1, and the description is abbreviate | omitted.

  The analyzer 31 includes a processing unit 41 and a determination unit 60. The processing unit 41 includes a receiving unit 50, a beat interval abnormal value detecting unit 53, a beat interval abnormal value removing unit 54, a frequency spectrum converting unit 51, and a power. A spectrum integration calculation unit 52 is included.

  The pulsation interval abnormal value detection unit 53 determines whether or not the RRI output from the receiving unit 50 should be regarded as an abnormal value. Whether RRI should be regarded as an abnormal value is determined as follows. In the second embodiment, the instantaneous heart rate is calculated by multiplying the reciprocal of RRI (in seconds) by 60, and the absolute value of the difference from the instantaneous heart rate one beat before is the first predetermined number (this embodiment). Then, an average is calculated at the most recent points (referred to as “8 points” in the present embodiment) that are equal to or less than “18”. Next, when the absolute value of the difference between the average and the instantaneous heart rate corresponding to the RRI to be evaluated is equal to or greater than a second predetermined number (in this embodiment, “35”), the RRI to be evaluated is Considered as an abnormal value. Here, the first predetermined number is preferably 30, more preferably 20, and even more preferably 15. The second predetermined number is preferably 50, more preferably 40, still more preferably 30.

  Note that the first predetermined number, the second predetermined number, and the number of the latest plural points may be appropriately changed according to individual differences and the like. For example, the first predetermined number may be appropriately changed within a range of 30 or less, the second predetermined number may be 30 or more, and the number of the nearest plural points may be within a range of 4-20.

  The pulsation interval abnormal value removal unit 54 excludes the RRI regarded as an abnormal value by the pulsation interval abnormal value detection unit 53 from the data processing target in the frequency spectrum conversion unit 51. The pulsation interval abnormal value removal unit 54 excludes RRIs regarded as abnormal values by the pulsation interval abnormal value detection unit 53 from the data processing targets in the determination unit 60.

(Embodiment 3)
The third embodiment is a configuration example of an apparatus having functions of measuring the acceleration of a subject and calculating a supine time zone in addition to the first embodiment. FIG. 4 is a block diagram showing the configuration of the activity rhythm determination device 3 according to Embodiment 3 of the present invention. The activity rhythm determination device 3 illustrated in FIG. 4 includes a sensor 11 and an analyzer 32. In addition, the same number is attached | subjected to the component similar to the activity rhythm determination apparatus of Embodiment 1-2, and the description is abbreviate | omitted.

  The measurement unit 21 of the sensor 11 includes a pulsation measurement unit 25 and an acceleration measurement unit 26. The analyzer 32 includes a processing unit 42 and a determination unit 60. The processing unit 42 includes a reception unit 50, a frequency spectrum conversion unit 51, a power spectrum integration calculation unit 52, a negative acceleration calculation unit 55, and a lying time zone calculation unit 56. Prepare.

  The acceleration measuring unit 26 measures at least one of the accelerations in the X-axis, Y-axis, and Z-axis directions of the subject and transmits it to the analyzer 32. The type of sensor for measuring acceleration is not particularly limited, and for example, a piezoresistive acceleration sensor, a piezoelectric acceleration sensor, a capacitive acceleration sensor, or the like can be used. A piezoresistive acceleration sensor is small and easily mass-produced because it uses a semiconductor. Piezoelectric acceleration sensors are easy to detect relatively high accelerations. A capacitive acceleration sensor is more sensitive than a piezoresistive acceleration sensor, has a wide range of detectable acceleration, and is less temperature dependent.

  In order to classify the awakening time zone and the sleep time zone according to the condition [D] or [E] of “1. Activity Rhythm Determination Method”, the acceleration measuring unit 26 measures the acceleration TA in the height direction of the subject. It is preferable. That is, it is preferable that any one of the X axis, the Y axis, and the Z axis measured by the acceleration measuring unit 26 coincides with the acceleration TA in the height direction of the subject.

  In order to transmit the acceleration data measured by the acceleration measuring unit 26 to the receiving unit 50 of the analyzer 32, wireless communication or wired communication may be used in the same manner as the pulsation interval data. In particular, the acceleration is preferably transmitted and received at the same timing as the RRI in order to reduce the frequency of wireless communication.

  The negative acceleration calculation unit 55 calculates the negative acceleration NA from the acceleration TA in the height direction of the subject obtained by the acceleration measurement unit 26. The negative acceleration can be calculated by, for example, the condition [D] (1) or the condition [E] (1). By calculating the negative acceleration, the time zone in which the posture of the subject is in the supine position is calculated as described later in the third embodiment, or the awakening time zone and the sleep time as described later in the fourth embodiment. Band classification becomes easy.

  The lying time zone calculation unit 56 calculates the lying time zone using the negative acceleration obtained by the negative acceleration calculation unit 55. For example, as shown in the condition [E] (2), a time zone satisfying NA ≧ C1 may be set as the supine time zone.

  Although not shown, the sensor may be provided with a data storage unit that temporarily stores biological information acquired by a measurement unit including a pulsation measurement unit and an acceleration measurement unit. Since it is not necessary to sequentially transmit data acquired by the sensor to the analyzer and process the data, the amount of power consumed by data communication can be suppressed. For example, it is suitable for a case where a subject performs measurement using a sensor at home, and a doctor determines an activity rhythm state later using an analyzer in a medical institution. In order to obtain a small and light sensor, it is preferable to use a known semiconductor memory for the data storage unit.

(Embodiment 4)
In the fourth embodiment, a configuration example of an apparatus having a function of measuring a subject's acceleration, calculating a decubitus time zone, and classifying an awakening time zone and a sleeping time zone will be described. FIG. 5 is a block diagram showing the configuration of the activity rhythm determination device 4 according to Embodiment 4 of the present invention. The activity rhythm determination device 4 shown in FIG. 5 includes a sensor 11 and an analyzer 33. In addition, the same number is attached | subjected to the component similar to the activity rhythm determination apparatus of Embodiment 1-3, and the description is abbreviate | omitted.

The sensor 11 includes a measurement unit 21, and the measurement unit 21 includes a pulsation measurement unit 25 and an acceleration measurement unit 26. The analyzer 33 includes a processing unit 43 and a determination unit 60. The processing unit 43 includes a reception unit 50, a frequency spectrum conversion unit 51, a power spectrum integration calculation unit 52, a negative acceleration calculation unit 55, a lying time zone calculation unit 56, An awakening / sleep classification unit 57 is provided.
The awakening / sleep classification unit 57 classifies the awakening time zone and the sleeping time zone based on the lying time zone data calculated by the lying time zone calculation unit 56. The method shown in “1. Activity rhythm determination method” can be used for the classification of the awakening time zone and the sleeping time zone.

(Embodiment 5)
FIG. 6 is a block diagram showing the configuration of the activity rhythm determination apparatus 5 according to Embodiment 5 of the present invention. 6 includes a sensor 11 and an analyzer 34. The activity rhythm determination apparatus 5 illustrated in FIG. In addition, the same number is attached | subjected to the component similar to the activity rhythm determination apparatus of Embodiment 1-4, and the description is abbreviate | omitted.
The analyzer 34 includes a processing unit 44 and a determination unit 60. The processing unit 44 includes a reception unit 50, a frequency spectrum conversion unit 51, a power spectrum integration calculation unit 52, an average calculation unit 58, a negative acceleration calculation unit 55, A rank time zone calculation unit 56 and an awakening / sleep classification unit 57 are included.

  The average calculator 58 calculates at least one of an average value of (LF / HF) in each time zone and an average value of HF in each time zone. Thereby, since it becomes easy to observe the transition of (LF / HF) or HF for each time zone, it is possible to easily determine the conditions [B] and [C].

(Embodiment 6)
FIG. 7 is a block diagram showing the configuration of the activity rhythm determination apparatus 6 according to Embodiment 6 of the present invention. The activity rhythm determination device 6 shown in FIG. 7 includes a sensor 11 and an analyzer 35. In addition, the same number is attached | subjected to the component similar to the activity rhythm determination apparatus of Embodiment 1-5, and the description is abbreviate | omitted.

  The analyzer 35 includes a processing unit 45 and a determination unit 60. The processing unit 45 includes a reception unit 50, a frequency spectrum conversion unit 51, a power spectrum integration calculation unit 52, a negative acceleration calculation unit 55, and a lying time zone calculation unit. 56, an awakening / sleep classification unit 57, and a morphology operation unit 59.

  The morphological operation unit 59 performs a morphological operation on the negative acceleration-time waveform in order to remove noise of the negative acceleration-time waveform calculated by the negative acceleration calculation unit 55. Here, as the morphological operation, as described above, for example, an expansion operation, a contraction operation, an opening process, a closing process, or a combination thereof can be applied. Although not shown in FIG. 7, the processing unit 45 performs binarization that binarizes the magnitude of the negative acceleration value with the predetermined value C2 as a threshold value before the processing in the morphological operation unit 59. A processing unit can also be provided. In the binarization processing unit, for example, if the negative acceleration NA is C2 or more, the negative acceleration NA is regarded as 0, and if the negative acceleration NA is less than C2, it is regarded as 1. In this way, by performing binarization processing on acceleration prior to morphological computation, processing time required for morphological computation can be shortened. In this embodiment, an example in which morphological calculation is performed on negative acceleration NA data has been described. However, morphological calculation is performed by morphological calculation unit 59 on acceleration TA in the height direction received by receiving unit 50. Thereafter, the negative acceleration NA may be calculated by the negative acceleration calculator 55.

  This application claims the benefit of priority based on Japanese Patent Application No. 2016-39893 filed on Mar. 2, 2016. The entire contents of the specification of Japanese Patent Application No. 2016-39893 filed on March 2, 2016 are incorporated herein by reference.

1, 2, 3, 4, 5, 6: Activity rhythm determination device 10, 11: Sensor 20, 21: Measurement unit 25: Beat measurement unit 26: Acceleration measurement unit 30, 31, 32, 33, 34, 35: Analyzers 40, 41, 42, 43, 44, 45: processing unit 50: reception unit 51: frequency spectrum conversion unit 52: power spectrum integral calculation unit 53: pulsation interval abnormal value detection unit 54: pulsation interval abnormal value removal Unit 55: Negative acceleration calculation unit 56: Depression time zone calculation unit 57: Awakening / sleep classification unit 58: Average calculation unit 59: Morphology calculation unit 60: Determination unit 70: Notification unit

Claims (8)

Measure the subject's beat interval for a predetermined measurement time,
An activity rhythm determination method, wherein at least one of the following conditions [A] to [C] is determined.
[A] There is no position time zone in the awakening time zone.
[B] (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is (LF / HF) in the immediately preceding sleeping time zone Bigger than.
[C] The HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone.
Here, LF is a value obtained by integrating the power spectrum obtained by including the step of converting the beat interval into the frequency spectrum from frequencies Lf1 to Lf2, and HF is a value obtained by integrating the power spectrum from frequencies Hf1 to Hf2. Hf1> Lf1 and Hf2> Lf2. Measure the acceleration TA in the height direction of the subject,
The activity rhythm determination method according to claim 1, wherein a negative acceleration NA is calculated according to the following condition [D] to calculate the supine time zone, and the awakening time zone and the sleep time zone are classified.
[D] (1) Calculation of Negative Acceleration NA (1a) When TA ≧ 0 when the subject is standing, NA = (− 1) × (TA)
(1b) If TA <0 when the subject is standing, NA = TA
(2) Calculation of the prone time zone (2a) First prone time zone L _m1 : Time zone in which NA ≧ C1 (C1 is a constant) is equal to or greater than the first predetermined time T ₁ (2b) Second prone time zone L _m2 : A gap time zone L _sm in which NA <C1 between two adjacent first _saddle time zones L _m11 and L _{m12 when} the first _saddle time zone L _m1 is 2 or more is a second predetermined value. When the time is within the time T _{2, a} time zone in which the two adjacent first _prone time zones L _m11 and L _m12 and the gap time zone L _sm are summed up. (3) Awakening time zone and sleep time zone classification (3a) Sleep time zone: longest time zone among the first prone time zone L _m1 and the second prone time zone L _m2 during a predetermined measurement unit time (3b) awakening time zone: sleep from a predetermined measurement unit time Time zone excluding time zone The activity rhythm determination method according to claim 1, wherein the acceleration TA in the height direction of the subject is measured, the negative acceleration NA is calculated according to the following condition [E], and the supine time zone is calculated.
[E] (1) Calculation of negative acceleration NA (1a) When TA ≧ 0 when the subject is standing, NA = (− 1) × (TA)
(1b) If TA <0 when the subject is standing, NA = TA
(2) Calculation of supine time zone
Supine time zone: Time zone satisfying NA ≧ C1 (C1 is a constant)   In the condition [B], (LF / HF) in the sleep time zone is an average value of (LF / HF) in the sleep time zone, and (LF / HF) in the wake time zone is (( The rhythm determination method according to any one of claims 1 to 3, which is an average value of (LF / HF).   5. In the condition [C], HF in the sleep time zone is an average value of HF in the sleep time zone, and HF in the wake time zone is an average value of HF in the wake time zone. The activity rhythm determination method according to the item.   Under the condition [C], the increase rate of HF in the sleep time zone with respect to HF in the immediately preceding awake time zone is more than 10%, and the decrease rate of HF in the awake time zone with respect to HF in the immediately preceding sleep time zone is 10%. The activity rhythm determination method according to claim 1, wherein the activity rhythm is determined to be super.   The activity rhythm determination method according to claim 1, wherein an RR interval that is an interval between an R wave and an R wave in an electrocardiogram signal is used as the pulsation interval. A measurement unit that measures the pulse interval of the subject for a predetermined measurement time;
A value obtained by converting the pulsation interval into a frequency spectrum (hereinafter referred to as “power spectrum”) is obtained, and a value obtained by definite integration of the power spectrum from frequencies Lf1 to Lf2 (hereinafter referred to as “LF”). And a processing unit that calculates a value (hereinafter referred to as “HF”) obtained by definite integration from the frequency Hf1 (> Lf1) to Hf2 (> Lf2),
An activity rhythm determination apparatus comprising: a determination unit that determines at least one of the following conditions [A] to [C].
[A] There is no position time zone in the awakening time zone.
[B] (LF / HF) in the sleeping time zone is smaller than (LF / HF) in the immediately preceding awakening time zone, and (LF / HF) in the awakening time zone is (LF / HF) in the immediately preceding sleeping time zone Bigger than.
[C] The HF in the sleeping time zone is larger than the HF in the immediately preceding awakening time zone, and the HF in the awakening time zone is smaller than the HF in the immediately preceding sleeping time zone.

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