JP2013081708A - Sleeping state discriminating apparatus and method - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a technique for discriminating the sleeping state of a bedded person with high precision.SOLUTION: A vibration detector 1 is installed under a bedded person or bedding such as a mattress or the like used by the bedded person to output an output signal corresponding to a detected vibration. In the lying case of the bedded person, the vibration caused by the pulsation, breathing, body movement or the like of the heart of the bedded person can be detected. The output signal from a vibration sensor is inputted to a processor 10. A feature quantity calculation part 14 calculates a plurality of feature quantities on the basis of a pulse wave. A sleeping state discrimination part 15 adapts the feature quantities calculated with respect to a support vector machine learned on the basis of teacher data to discriminate the sleeping state of the bedded person.

Description

  The present invention relates to a technique for discriminating a sleeping state of a bedridden person, and particularly to a technology for discriminating a sleeping state of a bedded person based on a pulse wave.

  Conventionally, there has been a demand for grasping sleep states of patients and residents in hospitals and elderly facilities. In recent years, it has been found that the quality of sleep is more important than the length of sleep, and therefore there is a desire to measure the quality of sleep.

  In order to meet such a demand, for example, a technique for discriminating a sleep state based on a subject's pulse interval data and body motion data has been proposed (see Patent Document 1). In the technique of this Patent Document 1, the sleep state is determined based on the autonomic nerve index from the pulse interval data excluding the pulse interval data when it is determined that there is body movement. This autonomic nerve index is acquired from a plurality of power spectra in the frequency spectrum distribution converted from the pulse interval data.

JP-A-2005-279113

  In the technique of the above-mentioned patent document 1, since the sleep state is determined by excluding the heartbeat interval data when there is a body motion, the influence of noise due to the body motion can be excluded, and the sleep state determination accuracy is improved. Can do. However, the sleep state discrimination processing is performed by threshold processing based on the power spectrum (LF) in the low frequency region and the power spectrum (HF) in the high frequency region, and these feature values are influenced by the influence of breathing. Therefore, it cannot be said that the activity of the autonomic nerve (particularly the parasympathetic nerve) serving as the sleep state index is sufficiently expressed. In addition, it is difficult to determine with high accuracy by simple threshold processing. Therefore, with the technique of cited document 1, there is a possibility that the sleep state cannot be accurately determined.

  This invention is made | formed in view of the said subject, The objective is to provide the technique which discriminate | determines a bedtime person's sleep state with high precision.

  In order to solve the above-described problem, the sleep state determination device of the present invention includes a pulse wave acquisition unit that acquires a pulse wave of a bedside person, a feature amount calculation unit that calculates a plurality of feature amounts based on the pulse wave, A sleep state determination unit that determines the sleep state of the occupant by applying the feature amount to the support vector machine learned based on the teacher data.

  In this configuration, since a support vector machine (hereinafter abbreviated as SVM) is used to determine the sleep state, it is possible to determine the sleep state with high accuracy.

  There is a correlation between the sleep state and the activity state of the parasympathetic nerve, and the power spectrum in the high frequency region includes information indicating the activity of the parasympathetic nerve. Therefore, it is considered that the feature amount calculated from the power spectrum in the high frequency region represents the activity state of the parasympathetic nerve, that is, the sleep state. Therefore, in one of the preferred embodiments of the sleep state determination device of the present invention, the feature amount calculation unit calculates a pulse interval information calculation unit that calculates pulse interval information representing a heart beat interval from the pulse wave. And a pulsation frequency characteristic calculation unit for calculating a pulsation frequency characteristic of the heart from the pulsation interval information, a power spectrum calculation unit for calculating a power spectrum of the pulsation frequency characteristic, and a logarithmic axis plane. And an inclination calculating unit that calculates an inclination in the high frequency region out of the power spectrum classified into an ultra-low frequency region, a low frequency region, and a high frequency region as the feature amount.

  In this configuration, the inclination of the high frequency region of the power spectrum of the pulsation frequency characteristic expressed by the logarithmic axis plane is used as the feature amount calculated based on the pulse wave. This inclination indicates the fractal nature of the power spectrum in the high frequency region. On the other hand, it is known that the fluctuation of the pulse wave is fractal modulated with respect to the activity (activity) of the parasympathetic nerve. Therefore, it is considered that the slope of the high frequency region of the power spectrum of the pulsation frequency characteristic expressed by the logarithmic axis plane reflects the parasympathetic nerve activity, that is, the sleep state well. Therefore, if such a value is used as a feature amount to determine the sleep state, it is possible to determine with high accuracy.

  The fractal nature of the power spectrum can also be seen in the low frequency region and the very low frequency region. Therefore, in one preferred embodiment of the sleep state determination device of the present invention, the slope calculation unit, as the feature amount, includes the ultra-low frequency region of the power spectrum expressed on the log-log plane and The slope in the low frequency region is calculated.

  The sleep state is classified into, for example, awakening / REM sleep / shallow non-REM sleep / deep non-REM sleep. However, since different conceptual levels are mixed in this classification, it is not desirable to handle them in the same row. Therefore, in one preferred embodiment of the sleep state determination device of the present invention, the sleep state is hierarchically defined, and the sleep state determination unit hierarchically corresponds to the sleep state hierarchy. Determine the state.

  In this configuration, sleep states are defined hierarchically for each concept level, and sleep state determination processing is performed hierarchically according to the layers. For example, the determination is performed in the first hierarchy (the highest hierarchy), and when the determination result state has the classification of the second hierarchy, the determination in the second hierarchy is performed. In this way, the determination accuracy can be improved by performing the determination in hierarchies.

  There are various feature quantities calculated from the pulse wave in addition to those described above. Therefore, there is a possibility that the unit of each feature amount is different. Therefore, in one preferred embodiment of the sleep state discriminating apparatus of the present invention, the support vector machine performs normalization using the average value and the standard deviation for each feature amount type for each feature amount type. The sleep state determination unit uses the feature amount normalized using the average value and the standard deviation for each feature amount type for each feature amount type. To determine.

  In this configuration, since each feature amount is normalized by the average value and standard deviation of the type, the weight between the feature amounts can be eliminated.

  In one preferred embodiment of the sleep state discriminating apparatus of the present invention, the teacher data is the feature amount acquired from the occupant and the sleep state when the feature amount is acquired. .

  In this configuration, since the feature amount and sleep state acquired from the occupant are used as the teacher data, individual differences in the feature amount can be eliminated, and teacher data specialized for the occupant can be obtained. By using such teacher data, it is possible to improve the sleep state discrimination accuracy.

  Moreover, in order to solve the said subject, the sleep state discrimination | determination method of this invention is based on the step which acquires the resident's pulse wave, the step which calculates several feature-value based on the said pulse wave, and teacher data And determining the sleep state of the occupant by applying the feature amount to the learned SVM. Naturally, the additional feature of the sleep state determination device described above can also be applied to such a sleep state determination method.

It is a block diagram of a sleep state discrimination device. It is a functional block diagram of a sleep state discrimination device. It is a hierarchy figure of a sleep state. It is a flowchart showing the flow of a feature amount calculation process. It is a flowchart showing the flow of the learning process of SVM. It is a flowchart showing the flow of the discrimination process of a sleep state. It is a table | surface of the discrimination result of a sleep state. It is an example of the power spectrum of the frequency characteristic of a heartbeat interval. It is the figure which represented the power spectrum of FIG. 8 with the logarithmic axis.

  Below, embodiment of the sleep state discrimination | determination apparatus of this invention is described using drawing. FIG. 1 is a configuration diagram of a sleep state determination device according to the present embodiment. As shown in the figure, the sleep state determination device according to the present embodiment includes a vibration detection device 1 and a vibration detection device that detect vibrations caused by a person who is present on the bedding (hereinafter referred to as a resident M). 1 is configured by a processing device 10 that determines the sleep state of the occupant M based on the output from 1.

  The vibration detection device 1 is installed under the occupant M or under a bedding such as a mattress or mattress used by the occupant M, and outputs an output signal corresponding to the detected vibration. When the occupant M is lying down, vibrations caused by the pulsation, breathing, body movement, etc. of the occupant M can be detected. As shown in the figure, the vibration detection device 1 in this embodiment includes six known vibration sensors 1 a, and an output signal from the vibration sensor 1 a is input to the processing device 10. In the following description, the flow of the output signal from the vibration sensor 1a is referred to as a channel. Therefore, in this embodiment, a 6-channel signal system is formed from the vibration detection unit 1 to the processing device 10. The number of vibration sensors 1a may be one, and can be changed as appropriate.

  As shown in FIG. 1, the processing apparatus 10 includes a display 20 for displaying various information on the front surface thereof, and a touch panel 21 formed on the surface of the display 20. A user such as a resident M can give an instruction to the processing apparatus 10 by operating the touch panel 21. Further, a push type power switch 22 is provided at the lower right corner of the front surface of the processing device 10, and the sleep state determination device can be activated and terminated by the power switch 22.

  FIG. 2 is a functional block diagram showing functional units provided in the processing apparatus 10. In the present embodiment, the processing device 10 is configured by software with a CPU (Central Processing Unit) or memory that executes various processes as the core, but each function unit may be configured by hardware. Alternatively, hardware and software may be configured to cooperate.

  As shown in the figure, the processing device 10 includes a control unit 11 that controls the entire processing device 10, an output signal acquisition unit 12 that acquires an output signal from the vibration sensor 1 a, and a pulse wave of the bed person M based on the output signal. A pulse wave calculation unit 13 that calculates a plurality of feature amounts based on the pulse wave, and a sleep state determination unit 15 that determines the sleep state of the occupant M based on the calculated feature amounts. It has. The vibration detection device 1, the output signal acquisition unit 12, and the pulse wave calculation unit 13 constitute a pulse wave acquisition unit of the present invention.

  The control unit 11 has a function of controlling the processing of the entire processing apparatus 10, and in order to notify the occupant M and the like of the determination results and various information about the sleep state of the occupant M, the display 20 Control the display. Also, it has a function of acquiring an operation on the touch panel 21. Furthermore, you may provide the function to transmit the discrimination | determination result about a sleep state to a remote place via a network. The display and transmission of the determination result may be in real time, and the determination result may be stored in a memory (not shown) and displayed and transmitted for each unit period or for a specified period. it can.

  The output signal acquisition unit 12 receives 6-channel output signals from the vibration sensor 1a measured in real time. The output signal acquisition unit 12 samples an input output signal at a predetermined sampling interval and performs A / D conversion. In the present embodiment, the sampling interval is 10 msec. The 1-channel output signal A / D converted by the output signal acquisition unit 12 is temporarily stored in a memory (not shown). In the following description, an A / D converted output signal is also simply referred to as an output signal.

  The pulse wave calculation unit 13 calculates a pulse wave from the output signal stored in the memory. In the present embodiment, a pulse wave is obtained by applying a filter process for extracting a frequency component corresponding to the heartbeat of the bedded person M to the output signal acquired at a predetermined period, for example, 10 msec. The calculated pulse wave is temporarily stored in the memory. As described above, in the present embodiment, 6-channel output signals are input to the pulse wave calculation unit 13, but one of the output signals is selected and a pulse wave is calculated from the output signal. ing. The selection of the output signal can be performed based on the magnitude of the amplitude, for example.

  The feature amount calculation unit 14 calculates a plurality of feature amounts from the pulse wave calculated by the pulse wave calculation unit 13. In this embodiment, as feature amounts, (1) an elapsed time after entering the floor (hereinafter referred to as Time value), (2) an average value (hereinafter referred to as RR value) of RR intervals (details will be described later) in a predetermined period. (3) Ratio of standard deviation of RR interval to average value of RR interval in a predetermined period (= standard deviation / average; hereinafter referred to as RR interval variation coefficient), (4-6) Power spectrum of RR interval (Hereinafter referred to as RR power spectrum) area of ultra low frequency region, low frequency region, high frequency region (hereinafter referred to as VLF value, LF value, HF value, respectively), (7) ratio of LF value to HF value ( (Hereinafter referred to as LF / HF values), (8-10) slopes in the ultralow frequency region, low frequency region, and high frequency region of the RR power spectrum expressed in the logarithmic axis plane (hereinafter referred to as VLF slopes, respectively). Tilt LF, referred to as HF gradient), it is used. In this embodiment, the predetermined period for calculating the RR value and the predetermined period for determining the RR interval variation coefficient are 20 seconds, but these can be changed as appropriate. The ultra-low frequency region, the low-frequency region, and the high-frequency region are set to 0.0001 to 0.04 Hz, 0.04 to 0.15 Hz, and 0.15 to 0.4 Hz, respectively.

  In order to calculate the feature amount, the feature amount calculation unit 14 of the present embodiment includes a timer 14a for calculating the Time value, and pulse interval information that calculates pulse interval information representing the heart beat interval from the pulse wave. A calculation unit 14b, a pulsation frequency characteristic calculation unit 14c that calculates a frequency characteristic of the heart beat (hereinafter referred to as a pulsation frequency characteristic) from the pulsation interval information, and a power spectrum (RR power spectrum) of the pulsation frequency characteristic. Power spectrum calculation unit 14d to calculate, slope calculation unit 14e to calculate the gradient in the ultra-low frequency region, low frequency region and high frequency region of the RR power spectrum expressed on the logarithmic axis plane, RR to calculate the RR interval variation coefficient An interval variation coefficient calculation unit 14f is provided. Details of the calculation method of each feature amount will be described later.

  The sleep state determination unit 15 determines the sleep state of the occupant M based on the feature amount calculated by the feature amount calculation unit 14. The sleep state is determined by applying a feature amount calculated from the pulse wave of the bedridden M to the SVM learned from the teacher data.

  The sleep state of this embodiment is sleep / wake, REM sleep / non-REM sleep, non-REM sleep (shallow) / non-REM sleep (deep), and this sleep state is hierarchical as shown in FIG. Defined. That is, the sleep state is divided into sleep or awakening in the first hierarchy. Moreover, sleep is divided into REM sleep or non-REM sleep in the second hierarchy. Furthermore, non-REM sleep is divided into non-REM sleep (shallow) or non-REM sleep (deep) in the third hierarchy.

  In the following, the flow of processing of feature quantity calculation and SVM learning as a discrimination rule will be described based on the flowcharts of FIGS. 4 and 5. In addition, although learning of SVM can be performed using a device different from the sleep state determination device and installed in the sleep state determination device, the feature amount (teacher data) for learning is the above-described feature amount calculation unit 14. In this example, learning is performed using a sleep state determination device. In this embodiment, the sleep state is obtained from the electroencephalogram together with the feature amount, and the sleep state is used as a correct answer. Therefore, the sleep state discriminating apparatus during learning has an electroencephalogram sensor (not shown) that acquires an electroencephalogram, an electroencephalogram analysis unit (not shown) that discriminates a sleep state based on the acquired electroencephalogram, and an SVM based on teacher data. A learning unit (not shown) for learning is provided.

[Feature value calculation]
First, the subject enters the bed on which the vibration detection device 1 is installed with the electroencephalogram sensor attached. At this time, the subject or the operator operates the touch panel 21 to explicitly instruct the start of acquisition of teacher data (learning data) (# 01). At this time, the timer 14a is reset to 0 and starts measuring the elapsed time since entering the floor (# 02).

  The output signal acquisition unit 12 performs A / D conversion on the output signal from the sequential vibration detection device 1 and stores it in the memory. The pulse wave calculation unit 13 performs a filtering process on the output signal stored in the memory to calculate a pulse wave, and stores it in the memory again (# 03).

  When a pulse wave for 20 seconds that is a predetermined period is acquired by this processing (Yes branch of # 04), the feature amount is calculated by the following processing.

  The pulsation interval information calculation unit 14b calculates pulsation interval information from the pulse wave stored in the memory (# 05). Here, the pulsation interval information is a time interval of a characteristic waveform appearing on the pulse wave corresponding to a characteristic waveform called R wave appearing on the electrocardiogram (hereinafter, this waveform is also called R wave). This is information that can be obtained by a known method. Specifically, the relationship between the time when the R wave appears and the time interval between the R wave and the immediately preceding R wave is pulsation interval information. The time interval between the R wave and the R wave is the RR interval.

  The pulsation interval information obtained by the above processing has a value (RR interval) only at the time when the R wave is detected, and is sparse in time. Therefore, the pulsation interval information calculation unit 14b upsamples the pulsation interval information into a temporally dense RR interval, that is, an RR interval every predetermined time, by interpolation processing in order to obtain an RR interval for every predetermined time. (# 06). Hereinafter, the upsampled beat interval information is referred to as an RR interval trendgram. In the present embodiment, the predetermined time is 1 second.

  The feature amount calculation unit 14 calculates an RR value based on the RR interval trendgram (# 07). Specifically, the average value of the RR interval trendgram for 20 seconds, which is a predetermined period, is set as the RR value.

  Next, the RR interval variation coefficient calculation unit 14f calculates the standard deviation of the RR interval trendgram for 20 seconds, and calculates the standard deviation / RR value as the RR interval variation coefficient (# 08).

  On the other hand, the pulsation frequency characteristic calculation unit 14c performs a Fourier transform on the RR interval trendgram for five minutes accumulated in the memory to calculate the pulsation frequency characteristic of the heart (# 09). Here, the RR interval trendgram used for the Fourier transform is set to be shifted by 20 seconds from the earliest time of the RR interval trendgram used for the previous Fourier transform. That is, the RR interval trendgram used for the previous Fourier transform and the RR interval trendgram used for the current Fourier transform overlap by 4 minutes and 40 seconds.

  The power spectrum calculation unit 14d calculates the power spectrum from the pulsation frequency characteristic and sets it as the RR power spectrum (# 10). The power spectrum in the present invention is also called a power spectrum density and represents a power distribution at each frequency. The feature amount calculation unit 14 divides the RR power spectrum into an ultra-low frequency region, a low-frequency region, and a high-frequency region, obtains the area (integrated value) of each region as a VLF value, an LF value, and an HF value. HF value = LF value / HF value is calculated (# 11).

  In addition, the slope calculation unit 14e maps the above-described RR power spectrum onto the logarithmic axis plane, and sets the slopes of the RR power spectrum in the ultralow frequency region, the low frequency region, and the high frequency region on the logarithmic axis plane to VLF. The inclination, LF inclination, and HF inclination are calculated (# 12). The inclination can be obtained by a known method such as a least square method.

  On the other hand, the feature quantity calculation unit 14 reads the time of the timer 14a as a Time value (# 13).

In this way, as the feature vector v _{t at} time t, v _t = [Time value, RR value, RR interval variation coefficient, VLF value, LF value, HF value, LF / HF value, VLF slope, LF slope, HF Slope] is obtained. [V _t , sleep state] obtained by adding the sleep state calculated from the electroencephalogram by the electroencephalogram analysis unit to the feature vector v _t becomes teacher data at time t.

The above process is performed for a predetermined time, and a vector sequence {[v _t , sleep state]} is acquired. Note that in the present embodiment, teacher data is acquired with only the occupant M as subjects. Thereby, teacher data specialized for the occupant M is obtained. Therefore, it is possible to improve the discrimination accuracy for the occupant M. On the other hand, when teacher data is acquired from a plurality of subjects, individual differences in feature quantities are absorbed, and general-purpose teacher data is obtained. Moreover, when the in-bed person M is included in a plurality of subjects, the teacher data reflecting the characteristics of the in-bed person M can be obtained while being versatile.

[Learning]
When a sufficient amount of teacher data is acquired, the learning unit learns the SVM from the teacher data, that is, constructs the SVM. Note that, as described above, in the present embodiment, since a plurality of feature quantities having different units (scales) are used, teacher data is normalized in the present embodiment (# 21). Specifically, an average value and a standard deviation are obtained for each feature quantity type, (teacher data-average value) / standard deviation is calculated for each feature quantity type, and the calculated value is used as new teacher data. That's fine. Thus, by normalizing the teacher data, it is possible to reduce the influence of the scale difference on the SVM as the discrimination rule.

As described above, the sleep state of the present embodiment is hierarchically defined. Therefore, learning is also performed hierarchically. First, data [v _t , awakening] is extracted from the teacher data to generate awakening teacher data set, and the rest is set as a sleep teacher data set (# 22). Specifically, an SVM for discriminating wakefulness and sleep is constructed from a wakeup teacher data set and a sleep teacher data set by a known method (# 23).

Next, data [v _t , REM sleep] is extracted from the sleep teacher data set to generate a REM sleep teacher data set, and the rest is used as a non-REM sleep teacher data set (# 24). From this teacher data set for REM sleep and teacher data set for non-REM sleep, an SVM for discriminating REM sleep and non-REM sleep is constructed (# 25).

Next, the data [v _t , non-REM sleep (deep)] is extracted from the non-REM sleep teacher data set, a deep non-REM sleep teacher data set is generated, and the rest is shallow. It is set as a teacher data set for non-REM sleep (# 26). An SVM for discriminating non-REM sleep (deep) and non-REM sleep (shallow) is constructed from this deep non-REM sleep teacher data set and shallow non-REM sleep teacher data set (# 27).

  The SVM obtained in this way is recorded in a memory or the like accessible from the sleep state determination unit 15. Also, the average value and standard deviation for each feature amount are recorded in the same manner.

  In this way, the influence of noise on the SVM can be reduced by generating the SVM as a discrimination rule hierarchically.

[Discrimination process]
FIG. 6 is a flowchart showing the flow of the discrimination process. First, the resident M enters the bed and operates the power switch 22 to turn on the sleep state determination device (# 31).

  The output signal acquisition unit 12 acquires an output signal from the vibration detection device 1 (# 32), and a feature amount every 20 seconds is calculated by the above-described processing (# 33). When the feature amount is calculated, the sleep state determination unit 15 inputs the normalized feature amount to the SVM to determine the sleep state of the occupant M (# 34 to # 38). The normalization here is the same processing as normalization at the time of learning, and the average value and standard deviation for each feature amount recorded by the above processing are used. In the present embodiment, the average value and the standard deviation for normalizing the feature quantity to be discriminated are the same as those obtained by normalizing the teacher data, but the feature quantity acquired from the occupant M is used. An average value and a standard deviation may be used. In this case, the average value and the standard deviation may be updated sequentially, or values calculated in advance may be used.

  As described above, the SVM of this embodiment is defined so as to correspond to the sleep state hierarchy. Therefore, the sleep state is also determined hierarchically as follows. First, the feature amount calculated in # 33 is input to the awakening / sleep determination SVM to determine whether the sleep state is awakening or sleep (# 34). Here, if the sleep state is awake, the determination ends (Yes branch of # 35). On the other hand, if the sleep state is sleep (No branch of # 35), whether the sleep state is REM sleep or non-REM sleep is input to the REM sleep / non-REM sleep discrimination SVM. Is discriminated (# 36). If the sleep state is REM sleep, the determination ends (Yes branch of # 37). On the other hand, if the sleep state is non-REM sleep (No branch of # 37), the feature amount is input to the SVM for determining non-REM sleep (deep) / non-REM sleep (shallow), and the sleep state is non. It is discriminated whether it is REM sleep (deep) or non-REM sleep (shallow) (# 38).

  The sleep state determined in this way is associated with the time and stored in the memory, and is displayed on the display 20 by the control unit 11 or sent to a remote place.

  In this way, by performing the sleep state determination hierarchically, the determination accuracy can be improved by the narrowing effect.

  FIG. 7 shows the result of the discrimination experiment. In this discrimination experiment as well, when acquiring teacher data, the brain wave signal from the electroencephalogram sensor is analyzed by the electroencephalogram analysis unit to calculate the sleep state, and the result and the discrimination result of the sleep state discrimination device of the present invention are used. In comparison, correct / incorrect is discriminated. Moreover, the data used for correct / incorrect discrimination was selected according to the sleep state based on the electroencephalogram signal. For example, the discrimination between the REM sleep and the non-REM sleep in the second hierarchy is performed on the feature amount determined to be in the sleep state based on the electroencephalogram signal.

  FIG. 7A shows the discrimination result of the sleep state discriminating apparatus according to the present invention, and FIG. 7B shows the result of discriminating the sleep state using a discriminant analysis method instead of SVM. The column described as the total feature amount is a case where all the feature amounts described above are used, and the column described as the slope exclusion is the determination result when the VLF inclination, the LF inclination, and the HF inclination are excluded from the feature amount described above. It is. From this result, it can be seen that the discrimination accuracy is higher when the SVM is used than when the discriminant analysis method is used. That is, the advantage of using SVM to determine the sleep state has been clarified.

  From this result, it is also possible to confirm the effectiveness of using the VLF inclination, LF inclination, and HF inclination as the feature amount.

  FIGS. 8A and 8B are examples of RR power spectra in wakefulness and non-REM sleep (deep), respectively. When these RR power spectra are expressed by logarithmic axes, the oscillating waveforms shown in FIGS. 9A and 9B are obtained. In this figure, a straight line fitted to the RR power spectrum is superimposed in the ultra-low frequency region, the low-frequency region, and the high-frequency region. The inclinations of these straight lines are the VLF inclination, the LF inclination, and the HF inclination. In this example, the VLF slope, LF slope, and HF slope at awakening are 0.724, −2.066, and −2.298, respectively. On the other hand, the VLF slope, LF slope, and HF slope during non-REM sleep (deep) are 0.057, -0.357, and -2.708, respectively. From these, it can be seen that VLF slope, LF slope, and HF slope are clearly different between awakening and non-REM sleep (depth). That is, it is clear that if these values are used to discriminate the sleep state, it can be expected to improve the discrimination accuracy of the sleep state.

It is known that the pulse wave is fractal-modulated with respect to the action potential of the parasympathetic nerve, and the heartbeat fluctuation has a 1 / f ^β type power spectrum. It is also known that this fractal property varies depending on the sleep state. The difference in VLF inclination, LF inclination, and HF inclination in FIGS. 9A and 9B is considered to be due to this difference in fractal nature. That is, according to the VLF inclination, the LF inclination, and the HF inclination, it is considered that the fractal nature of heart rate variability can be evaluated and the sleep state can be discriminated based on the fractal nature.

  As described above, in the present invention, as a characteristic amount for determining the sleep state, the ultra low frequency region, the low frequency region, and the high frequency region of the Fourier power spectrum of the RR interval (RR interval trendgram) on the logarithmic axis plane are used. By using the slope at, the discrimination accuracy is increased.

[Another embodiment]
(1) In the above-described embodiment, ten feature amounts are used. However, the type of feature amount and the number of types can be changed as appropriate. For example, the number of body movements, the respiratory variation coefficient, etc. may be used.

(2) In the above-described embodiment, the pulse wave is acquired based on the vibration of the occupant acquired by the vibration sensor. However, the pulse wave is acquired from a sensor that measures the pulse wave attached to the occupant. You may acquire a pulse wave.

  The present invention can be applied to a sleep state determination device that determines the sleep state of a person who is present based on a pulse wave.

1: Vibration detection device (pulse wave acquisition unit)
12: Output signal acquisition unit (pulse wave acquisition unit)
13: Pulse wave calculation unit (pulse wave acquisition unit)
14: Feature amount calculation unit 14b: Pulsation interval information calculation unit 14c: Pulsation frequency characteristic calculation unit 14d: Power spectrum calculation unit 14e: Inclination calculation unit 14f: RR interval variation coefficient calculation unit 15: Sleep state determination unit

Claims (7)

A pulse wave acquisition unit for acquiring the pulse wave of the bedridden person,
A feature amount calculation unit that calculates a plurality of feature amounts based on the pulse wave;
A sleep state discriminating apparatus comprising: a sleep state discriminating unit that discriminates a sleep state of the bedridden person by applying the feature amount to a support vector machine learned based on teacher data. The feature amount calculation unit includes:
A pulsation interval information calculation unit for calculating pulsation interval information representing the pulsation interval of the heart from the pulse wave;
A pulsation frequency characteristic calculator that calculates a pulsation frequency characteristic of the heart from the pulsation interval information;
A power spectrum calculation unit for calculating a power spectrum of the pulsation frequency characteristic;
An inclination calculating unit that calculates an inclination in the high-frequency region out of the power spectrum expressed on a log-log plane as a feature amount, which is classified into an ultra-low frequency region, a low-frequency region, and a high-frequency region. Item 3. The sleep state discrimination device according to Item 1.   The sleep state determination apparatus according to claim 2, wherein the inclination calculation unit calculates, as the feature amount, an inclination in the ultralow frequency region and the low frequency region of the power spectrum expressed on the logarithmic axis plane. The sleep states are defined hierarchically;
The sleep state determination device according to any one of claims 1 to 3, wherein the sleep state determination unit determines the sleep state in a hierarchical manner corresponding to the sleep state hierarchy. The support vector machine is learned based on the teacher data normalized using the average value and the standard deviation for each type of the feature amount for each type of the feature amount,
5. The method according to claim 1, wherein the sleep state determination unit performs the determination using the feature amount normalized by using an average value and a standard deviation for each feature amount type for each feature amount type. The sleep state discrimination device according to claim 1.   The sleep state determination device according to any one of claims 1 to 5, wherein the teacher data is the feature amount acquired from the person in bed and a sleep state when the feature amount is acquired. . Acquiring a pulse wave of a bed person;
Calculating a plurality of feature amounts based on the pulse wave;
A sleep state determination method comprising: determining the sleep state of the occupant by applying the feature amount to a support vector machine learned based on teacher data.

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