KR100498794B1 - Apparatus for diagnosing condition of living organism and control unit - Google Patents

Abstract

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a living state diagnostic apparatus for diagnosing a living body based on pulse waves detected in the living body. In addition, an object of the present invention is to provide an apparatus for accurately diagnosing a living state at the present time, based on a change in the living state measured in a past lyric period, in consideration of periodic fluctuations of the living state. In order to realize this object, the apparatus of the present invention is a waveform extraction for extracting the characteristic information from the pulse wave detection unit 381 and the one-shot amount measuring unit 382, the detected pulse wave, respectively for detecting the pulse wave and the single stroke amount in the living body, respectively. The main portion includes a storage unit 386, a memory 383 in which the biometric state calculated from the feature information and a single ejection amount is stored, an output unit 385 for outputting an alarm, and a microcomputer 387 that manages each unit in the apparatus. do. The microcomputer calculates the cyclic dynamics parameter based on the characteristic information obtained from the waveform extraction storage unit, and stores it in the memory at predetermined time intervals. At that time, the microcomputer 387 calculates cyclic dynamic parameters from the pulse wave characteristic information and one stroke amount at predetermined time intervals, and stores them in the memory 383. In addition, at this time, the microcomputer 387 reads a predetermined amount of cyclic dynamics parameters from the memory 383 to calculate an average value and a standard deviation, and at this point, the calculated cyclic dynamics parameters are determined from these average values and standard deviations. It is determined whether or not it is within a predetermined range, and when it is determined that it is out of the range, the output unit 385 is controlled to generate an alarm.

Description

Apparatus for diagnosing condition of living organism and control unit

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a living body diagnostic apparatus and a control apparatus for extracting a living body state from a pulse wave and performing diagnosis of the living body and controlling the living body state in consideration of the periodic variation of the living body state.

The most commonly used in diagnosing the state of the human circulatory system is blood pressure or heart rate. Thus, conventionally, it is widely used as an indicator for measuring the state of the circulatory machine and, in a broader sense, to determine the physical state, such as blood pressure values such as the highest blood pressure and the lowest blood pressure extracted from the human body, and a pulse rate. . However, in order to carry out the diagnosis in more detail, it is necessary to measure a measured amount such as cyclic dynamic parameters such as viscous resistance, compliance, and the like of blood vessels described later.

Here, in order to measure indices of living states such as these circulating dynamic parameters, pressure waveforms and blood flows of the aortic starting and cutting portions are often measured. In addition, a method of directly measuring by inserting a catheter into an artery or indirectly by ultrasonic or the like has been adopted. However, the method of inserting the catheter into the artery requires a large device to be inserted. In addition, if the circulatory dynamics parameter is measured indirectly by ultrasound or the like, blood flow in the blood vessel can be observed by non-insertion, but there is a difficulty in requiring measurement, and the apparatus required for measurement is also large. There is a problem of becoming.

However, as the pulse wave research progresses, as the waveform of the pulse wave extracted from the human body is interpreted by various methods, various biological states obtained by not only knowing the blood pressure value or pulse rate are obtained, and the diagnosis can be made based on these biological states. I knew it was. Here, it is known that pulse wave is a wave of blood which is ejected from the heart and propagates blood vessels, and various medical information can be obtained by detecting and interpreting the pulse wave. In particular, when measuring the pulse wave at the distal end of the living body, the fingertip plethysmogram of the fingertip or the arterial wave of the finger node is measured, but in addition, the pulse wave is measured at various places of the human body. Although there are various kinds of pulse wave waveforms, three types of pulse wave waveforms of flat veins, bow veins, and strings shown in FIGS. 1A to 1C are shown as examples of typical pulse wave waveforms according to the classification of oriental medicine, one of oriental traditional medicine. . Here, the flat vein is a pulse of a "normal person", that is, a normal healthy person, and the pulse wave of a 34-year-old male is shown in FIG. 1A as a waveform example. As shown in the figure, the flat vein is characterized by a relaxed, gentle, constant rhythm and less dizziness. On the other hand, the tachycardia is caused by abnormal blood flow, swelling, liver and kidney diseases, respiratory diseases, gastrointestinal diseases, inflammatory diseases, such as the coming and going of the abnormal abnormal separation and smoothly occurs. Pulse wave of a 28 year old male as a representative waveform of the tachycardia is shown in FIG. 1B. As shown in the figure, the waveform of the tachycardia immediately descends immediately after rising, so that the aortic incision is deeply pied and the subsequent relaxation time is significantly higher than usual. On the other hand, the streak is caused by an increase in the tension of the blood vessel wall, and appears as a disease such as liver and phlegm diseases, skin diseases, high blood pressure, and painful diseases. This is thought to be due to the tension of the autonomic nervous system, which causes the walls of the blood vessels to tense, thereby reducing elasticity and making it difficult to show the effect of the pulsation of the extracted blood. A pulse wave of a 36 year old male is shown in FIG. 1C as a representative waveform example of a string. As shown in the figure, the waveform of the strings rises rapidly and is not immediately lowered. 1A to 1C, the vertical axis represents blood pressure (BP: mmHg), and the horizontal axis represents time (t: second).

As can be seen from the above description, it is possible to determine the specific disease of the patient or to diagnose the physical condition of the patient by finding out whether the pulse wave is, for example, flat veins, bow veins or strings according to the interpretation of the pulse wave waveform. . However, conventionally, there has been a problem that quantitative evaluation with such a point is not made.

On the other hand, as described in detail later, the human state repeats fluctuations (daily fluctuations, monthly fluctuations, annual fluctuations) according to regular rhythms in units of one day, one month, one year, and various kinds of pulse waves. The same applies to the indicators of the living state. Therefore, in consideration of such periodic fluctuations, diagnosis or control of the living state is meaningless unless the diagnosis of the living state is performed. However, since there has not been any device having a small device form capable of continuously measuring a living body state in daily life as a diagnostic technique so far, consideration of such periodic fluctuations of the living state is neglected.

1A is a waveform diagram of a flat vein that is a typical waveform of pulse waves.

1B is a waveform diagram of a bow vein, which is a representative waveform of pulse wave.

1C is a waveform diagram of a string, which is a typical waveform of pulse waves.

2 is a diagram illustrating the occurrence of sudden death.

3 illustrates the development of acute myocardial infarction.

4 shows a measurement form of an experiment for measuring periodic fluctuations of a living body state.

5 shows an experimental schedule of the experiment.

6 illustrates daily variation of cyclic dynamics parameters.

7 shows the spectrum of the daily fluctuation waveform of the cyclic dynamics parameter.

Fig. 8 shows the fundamental wave spectrum of the daily fluctuation waveform of the cyclic dynamics parameter.

9 illustrates daily variation of cyclic dynamics parameters.

10 shows year-round variation of cyclic dynamics parameters.

11 is a diagram showing a frequency analysis result of the resistance Rc of the arterial central part.

12A is a diagram illustrating an example of daily variation in the phase of the second harmonic of the pulse wave.

12B is a diagram showing an example of daily variation in the phase of the third harmonic of the pulse wave.

12C is a diagram showing an example of daily variation in the phase of the fourth harmonic of the pulse wave.

Fig. 13A is a diagram showing an example of daily variation in amplitude of the third harmonic of the pulse wave.

Fig. 13B is a diagram showing an example of daily variation in normalized amplitude of the third harmonic of the pulse wave.

14A is a plan view of a first pulse wave sensor using a distortion gauge.

14B is a plan view of a second pulse wave sensor using a strain gauge.

15 is a plan view of a third pulse wave sensor using a strain gauge.

16 is a plan view according to a modification of the pulse wave sensor using a strain gauge. ship

17 is a view showing a state in which the pulse wave sensor is mounted on a rubber glove.

18 is a plan view according to another modification of the pulse wave sensor using a strain gauge.

19 is a block diagram of a pulse wave detection unit using a strain gauge.

20 is a block diagram of a pulse wave detection unit using the pulse wave sensor shown in FIG. 17.

21 is a circuit diagram of a photoelectric pulse wave sensor 31.

Fig. 22A is a diagram showing driving timings of a pulse wave sensor and a pressure detection sensor.

Fig. 22B is a diagram showing another example of the drive timing of the pulse wave sensor and the pressure detection sensor;

The perspective view of the wrist watch in the form which combined the pressure pulse wave detection part with a wrist watch.

The perspective view of the wristwatch in the form which combined the pressure pulse wave detection part with a wristwatch.

25 is a cross-sectional view illustrating a detailed configuration of the wrist watch shown in FIG. 24.

Fig. 26 is a view when the photoelectric pulse wave sensor is combined with a necklace.

Fig. 27 is a diagram in which a photoelectric pulse wave sensor is combined with a necklace and a fragrance injection hole is provided;

FIG. 28 is a view of combining a photoelectric pulse wave sensor with a necklace and a tube for drug administration; FIG.

Fig. 29 is a view when the photoelectric pulse wave sensor is combined with glasses.

30 is a view in which the photoelectric pulse wave sensor is combined with the spectacles and a spraying hole for perfume is provided;

FIG. 31 is a view of combining a photoelectric pulse wave sensor with glasses and installing a tube for drug administration. FIG.

32 is a diagram in which a photoelectric pulse wave sensor is combined with a wrist watch and a photoelectric pulse wave sensor is installed on a wrist;

33 is a plan view showing the structure of a wrist watch in more detail in the form shown in FIG. 32;

Fig. 34 is a diagram in which the photoelectric pulse wave sensor is combined with a wrist watch and the photoelectric pulse wave sensor is installed at the fingertip;

35A is a perspective view showing a partial cross section of the pressure sensor 130 configuration.

35B is a perspective perspective view of the pressure sensor 130.

36 is an enlarged cross-sectional view of an essential part of the bonding portion between the elastic rubber 131 of the pressure sensor 130 and the semiconductor substrate 132.

37 is a circuit showing the configuration of a bias circuit 139 provided in the pressure sensor 130. FIG.

38A to 38D are timing diagrams each showing an example of the control signal T of the bias circuit 139. FIG.

38E and 38F both show waveforms of constant current pulses in the bias circuit 139;

39 is a simplified perspective view illustrating a principle of coordinate detection by the pressure sensor 130.

40 is an essential part cross sectional view for explaining the principle of pulse wave detection by the pressure sensor 130;

41 is a perspective view showing an appearance configuration of a wrist watch 146 incorporating a device using a pressure sensor 130.

42A is a perspective view illustrating a mounting state of the wrist watch 146.

42B is a sectional view of the wristwatch 146, in a mounted state.

43A and 43B are perspective views showing a deformed configuration of the pressure sensor 130.

44A is a plan view illustrating another example of the pressure sensor 130.

44B is an enlarged perspective view of an essential part showing the configuration of a junction portion of the elastic rubber 131 and the semiconductor substrate 132 in the same embodiment.

45 is a perspective view illustrating a partial cross section of a configuration of another example of the pressure sensor 130.

46 is a perspective view illustrating a partial cross section of a configuration of still another example of the pressure sensor 130.

47 shows another embodiment of pulse wave measurement.

Fig. 48 is a diagram explaining a systolic area method used for measuring a single ejection amount;

Fig. 49 is a view showing a measurement form for single ejection amount measurement and pulse wave detection;

50 shows another measurement form for one-time measurement and pulse wave detection.

FIG. 51 is a perspective view of a form in which a component part of the device except the sensor is embedded in a wrist watch, and the sensor is mounted as a band of the wrist watch; FIG.

52 is a perspective view of a form in which a component of the device except the sensor is incorporated in a wrist watch and the sensor is mounted on a finger;

Fig. 53 is a block diagram of a configuration in which a component part of the device except the sensor and the sensor are installed on the upper cuff by a cuff;

Fig. 54 is a diagram in which only one pulse wave detection unit is provided on the wrist, omitting the one-shot amount measuring unit;

Fig. 55 is a diagram showing correspondence between waveforms for one night of pulse waves and waveform parameters.

56 is a block diagram showing the configuration of the parameter extraction unit 180.

FIG. 57 is a diagram illustrating arterial waveforms of the finger nodes stored in the waveform memory 184. FIG.

58 is a diagram showing the contents of storage in the peak information memory 205;

Fig. 59 is a block diagram showing the construction of a frequency analyzer 210 for obtaining spectral information of a pulse wave waveform.

FIG. 60 is a diagram for explaining timing of turning over a waveform from the waveform extraction storage unit 180 to the frequency analysis unit 210. FIG.

Fig. 61 is a timing chart showing an operation in waveform extraction storage unit 180;

62 and 63 are diagrams for explaining the operation of the high speed playback unit 220;

64 is a view for explaining the operation of the fast reproducing unit 220 and the sine wave generator 221. FIG.

Fig. 65 is a circuit diagram of a four element concentrated constant model that is a dynamometer model of the human body.

Fig. 66 shows the blood pressure waveforms of the aortic starting portion of the human body;

Fig. 67 is a modeling waveform diagram of the blood pressure waveform of the aortic starting portion of the human body.

68 to 71 are flowcharts showing the parameter calculation processing operation in the four element centralized constant model.

Fig. 72 is a waveform diagram illustrating waveforms of arteries of finger joints obtained by the averaging process.

Fig. 73 is a diagram illustrating the waveform of the artery of the finger joint obtained by the averaging process and explaining the contents of the processing applied to the waveform.

Fig. 74 is a waveform diagram showing waveforms of arteries of the finger nodes obtained by the arithmetic processing and arteries of the finger nodes obtained by the averaging process;

75 is another modeling waveform diagram of the blood pressure waveform of the aortic starting portion of the human body.

FIG. 76A shows the correlation between central vascular resistance (R _c ) and distortion rate (d). FIG.

FIG. 76B shows the correlation between peripheral vascular resistance (R _p ) and strain (d).

Fig. 76C is a diagram showing a correlation between blood inertia (L) and strain (d).

FIG. 76D shows a correlation between the compliance C and the strain d. FIG.

77 is a diagram showing a relationship between a strain d and an S pulse wave;

Fig. 78 is a diagram showing the relationship between central vascular resistance (R _c ) and three pulse waves.

Fig. 79 is a diagram showing the relationship between peripheral vascular resistance (R _p ) and three pulse waves.

Fig. 80 is a diagram showing the relationship between the inertia (L) of blood and three pulse waves.

Fig. 81 shows the relationship between the compliance C and three pulse waves;

82 is a block diagram illustrating another configuration example of the deformation calculator.

83 is a diagram showing a relationship between an electrocardiogram and an RR interval.

84 is a diagram showing the relationship between an electrocardiogram and a pulse wave;

85A is a diagram showing a relationship between an RR interval variation and a frequency component constituting the variation;

Fig. 85B is a diagram showing the results of spectral analysis of RR interval variations.

86 shows a preferred measurement form when measuring pulse waves.

87 shows a face chart used as the notification means;

Fig. 88 is a sectional view of a wrist watch of an example in which a notification means is combined inside a wrist watch in a case where notification is made by vibration using a piezo element;

Fig. 89 is a view showing a wrist watch in which the apparatus of the present invention is combined, and a personal computer performing optical communication with the apparatus.

Fig. 90 is a detailed block diagram of a transmitting device installed inside an input interface combined with a device according to the present invention.

91 is a block diagram showing a first configuration of a diagnostic device according to the present invention.

92 is a flowchart showing the operation of the apparatus.

93 is a block diagram showing a second configuration of the device.

Fig. 94 shows a display example of the cyclic dynamics parameter by the apparatus;

Fig. 95 is a diagram showing another example of display of the cyclic dynamics parameter by the device, and is a diagram of a display mode using a clock hand;

Fig. 96 is a diagram showing another display example of the cyclic dynamics parameter by the same apparatus, wherein a display surface dedicated for displaying the cyclic dynamics parameter is provided;

Fig. 97 is a block diagram showing the structure of a diagnostic apparatus using a tidal wave of the present invention.

98 is a perspective view of a wristwatch 450 incorporating the device.

Fig. 99 is a bar graph of "LF / HF" displayed by the figure display section 23 of the apparatus.

100 is a bar graph of LF and HF displayed by the graphic display unit 23 of the apparatus.

Fig. 101 is a bar graph of RR50 displayed by the figure display section 23 of the apparatus.

Fig. 102 is a bar graph of the pulse rate displayed by the figure display section 23 of the apparatus.

Fig. 103 is a broken line graph showing the past week trend of "LF / HF" displayed by the figure display section 23 in the apparatus.

Fig. 104 is a line graph showing the past week's trend of LF and HF displayed by the figure display section 23 in the apparatus.

105 is a perspective view of a wrist watch according to another embodiment of the device;

106 shows the internal structure of the apparatus according to the embodiment;

107A to 107B show a guide message display example in the embodiment;

108 is a sectional view showing a structure of a micropump 501 according to the present invention.

Fig. 109 is a block diagram showing the structure of a drive unit for driving the micro pump 501;

110 and 111 illustrate the operation of the micropump 501.

112 is a block diagram showing a first configuration of a dosage control device according to the present invention.

113 and 114 are flowcharts showing the operation of the embodiment by the dosage control device of the same configuration.

115 is a block diagram showing a second configuration of a dosage control device according to the present invention;

Fig. 116A is a diagram showing the effect of single ejection amount SV due to perfume discharge.

116B is an illustration showing the effect on peripheral vascular resistance R _p by perfume discharge.

117-123 is a figure explaining the control form of fragrance discharge.

124 is a block diagram showing a configuration of a drug discharge device according to the present invention;

125A is a perspective view showing a mechanical configuration of the apparatus.

125B is a sectional view of the mechanical configuration of the apparatus.

126 is a block diagram showing a configuration of a drowsiness preventing apparatus according to the present invention;

127 is a perspective view of a wrist watch 790 incorporating the device.

128 is a block diagram illustrating another configuration example of the device.

SUMMARY OF THE INVENTION An object of the present invention is to provide an apparatus as follows while taking into account such periodic variation of a living body state.

1) A diagnostic apparatus for accurately diagnosing a subject's condition based on a change in a living body state measured in the past for a predetermined period.

2) A diagnostic device that presents various information about a living body using an indicator of pulse wave fluctuation.

3) A dosage control device that monitors a living state and performs necessary dosage.

4) A drug discharge device which discharges the perfume at an appropriate timing to control internal conditions such as excitement and sedation of the living body.

5) Drowsiness prevention device which detects drowsiness state by analyzing the arousal level of living body in pulse wave behavior.

In order to achieve the above object, 1st invention measures the indicator which shows the biological state which has periodical fluctuations in the said living body over predetermined period, and diagnoses the said biological state based on the indicator measured over these predetermined period. It is characterized by. According to the present invention, it is possible to realize a precise diagnosis of a living body state in consideration of periodic fluctuations of the living body state.

According to a second aspect of the present invention, a process of calculating an index indicating a living state is repeated, and each time the index is calculated, the index is compared with the index obtained in the past, and the result of the comparison is output. According to the present invention, since the comparison result between the currently obtained index and the past obtained index is obtained, it is possible to confirm the change of the living state.

According to a third aspect of the present invention, there is provided a measuring means, a memory means, and a control means, wherein the measuring means measures an indicator indicating a living state at a plurality of times every day, and the control means measures the living state at the plurality of times. Characterized in that the indicator to be recorded is recorded in the storage means, and based on the stored contents of the storage means, a corresponding determination result of whether or not the indicator at the current time is within the variation range at the same time within the past fixed period is characterized. It is done. According to the present invention, it is possible to confirm whether or not the indicator at the current time falls within the variation range of the indicator at the same time in the past period, so that when there is a change between the physical condition of the day and the physical condition of the last few days, I can see it. That is, when the indicator at the present time falls within the above variation range and is notified that the physical condition is in good condition, the indicator of the quality of life (QOL) is provided in a mentally relaxed manner from the notified user. Can be obtained. On the other hand, when it is notified that it does not fall in the fluctuation range, it can confirm that a physical condition is not normal.

A fourth aspect of the invention has a measuring means, a memory means, and a control means, wherein the measuring means measures an indicator indicating the living state at a plurality of times every day, and the control means is configured to measure the living state at the plurality of times. Is recorded in the storage means, and a deviation between the index at the present time and the reference index calculated from the index at the same time in the past period is characterized by the above-mentioned. . According to the present invention, since the deviation between the indicator at the present time and the reference indicator at the same time within the past fixed period can be known, the state of the body of the day can be known accurately.

A fifth invention includes measuring means, storage means and control means, wherein the measuring means measures an indicator representing a living state at a plurality of times every day, and the control means measures the living state at the plurality of times. The indicators indicated are recorded in the storage means, and the state of the change of each index calculated on the day is obtained and recorded in the storage means, and based on the storage contents of the storage means, It is characterized in that it is determined whether or not, and the corresponding determination result of whether or not according to the state of the past change.

Moreover, 6th invention has a measuring means, a memory means, and a control means, The said measuring means measures the indicator which shows a living state at a some time every day, The said control means is said at the said some time. An indicator indicating a living state is recorded in the storage means, and based on the indicators calculated on that day, the time at which the indicator becomes the maximum is obtained, recorded in the storage means, and based on the stored contents of the storage means, It is characterized by judging whether or not the change state of the indicator at the time is in accordance with the change state of the indicator at the same time within the past period, and notifying the result of the determination as to whether or not it is according to the past change state.

According to a seventh aspect of the present invention, there is provided a measurement means, a storage means, and a control means, wherein the measurement means measures an indicator indicating a living state at a plurality of times every day, and the control means measures the living state at the plurality of times. The indicator to be stored is stored in the storage means, and on the basis of the respective indicators calculated on that day, the time at which the indicator becomes the minimum is obtained and recorded in the storage means, based on the storage contents of the storage means. It is characterized by judging whether or not the change state of the indicator is in accordance with the change state of the indicator at the same time within a certain period of time in the past, and notifying the result of the determination as to whether or not it is in accordance with the past change state.

According to these inventions, a warning is issued when a change state such as rising or falling of the indicator indicating the living state does not correspond to the changing state in the past, so that an unnatural change in the living state can be accepted. On the contrary, if the form of change is in accordance with the state of change in the past and the body is in good condition, the user who is notified has a mental margin, and the degree of QOL of the user is determined. It can be an indicator.

Eighth invention accepts measuring means for measuring an indicator representing a living body state, storage means for storing an indicator representing the living body state, and the indicator measured by the measuring means in a predetermined time period, and as the storage means. The first control means to store, the instruction | indication from a user, the calculation means which takes out the said index memorize | stored in the said storage means, performs a predetermined | prescribed operation, and outputs the result, and the instruction from the said user And second control means for receiving the indicator at the time of the instruction by the measuring means, and notifying means for notifying the calculation result and the indicator at the time of the indicator. According to the present invention, the user of the device can know the information regarding his or her state of health at any time.

A ninth invention includes measuring means for measuring an indicator representing a living body state, storage means for storing an indicator representing the living body state, and the indicator measured by the measuring means in a predetermined time frame, and accepting the indicator as the storage means. A first control means for storing, an instruction means for taking out an index of a past predetermined number of days from the storage means, and obtaining a maximum value from an index of the past predetermined number of days from the storage means; and an instruction from the user When the indicator at the instruction point is accepted by the measuring means, the indicator at the instruction point is compared with the maximum value, and the indicator at the instruction point is larger than the maximum value, Second control means for determining that there is no abnormality when the indicator is not larger than the maximum value. , And it is characterized in that it comprises a notifying means for notifying the determination result of the abnormality.

A tenth invention includes measuring means for measuring an indicator representing a living body state, storage means for storing an indicator representing the living body state, and the indicator measured by the measuring means in a predetermined time frame. A first control means for storing, an instruction from the user, an arithmetic means for taking out an index of the past predetermined number of days from the storage means, and obtaining a minimum value from the index of the past predetermined number of days; and an instruction from the user The indicator at the point in time of the instruction is accepted by the measuring means, and the indicator at the point in time of the instruction is compared with the minimum value, and when the indicator at the point in time of the instruction is smaller than the minimum value, it is determined that there is an abnormality. Second control means for determining that there is no abnormality when the indicator is not smaller than the minimum value; And a notification means for notifying the determination result of the above abnormality.

According to these inventions, when the user's state of health of the device is significantly out of the recent state of health, attention can be urged for the user. In addition, when it is determined that there is no abnormality, since the physical condition is in a good state, by notifying this meaning, there is a mental margin for the notified user, and it may be an index indicating the degree of QOL of the corresponding user.

The eleventh invention is a memory for storing measurement means for measuring an indicator representing a living body state, physical motion detecting means for detecting a physical activity of the living body, an indicator representing the living body state and a measured value of the body moving detection means; Means, a first control means for receiving the indicators in the measurement means at a predetermined time and at the same time receiving the measured values of the body motion detecting means and storing them as the first control means for storing them together in the storage means; As an instrument of, the current value of the body motion measured by the body motion detection means is received, and among the measured values of the body motion detection means stored in the memory means, the measured value closest to the current value of body motion is selected. Calculation means for reading out and outputting an indicator stored in the storage means together with the selected measurement value; Instructing the instruction in the above, the second control means for receiving the indicator at the time of the instruction by the measuring means, the indicator outputted by the calculation means, and the indicator received by the second control means at the instruction time It is characterized by comprising a notification means. According to the present invention, even if the user of the device is training, for example, the situation affecting the measurement of the living state, based on the similar activity state in the past, the user's activity is matched. Indicators can be presented.

The twelfth invention measures an indicator having a change in synchronism over a predetermined period of time in the living body, analyzes the living body state based on the measured indicator over the predetermined time period, and the living body state is preferred according to the analysis result. It characterized in that the control to the state. According to the present invention, it is possible to accurately grasp the living body state by taking into account the periodic fluctuations of the living body state, so that it is possible to more precisely control various living body states for bringing the living body state into a desired state.

A thirteenth invention is characterized in that measuring means for measuring an indicator of a living state in relation to an excited state or a calm state in a patient, discharging means for administering a drug to the patient, and an indicator representing the living state satisfy a predetermined condition. In this case, it is characterized in that it is provided with a dosage control means for commanding the dosage to the discharge means. According to the present invention, it is possible to control the patient's condition to be in a good state by monitoring the patient's condition and automatically taking medication as needed to stabilize the patient's circulation dynamics.

The fourteenth invention determines when to discharge a drug on the basis of measuring means for measuring an indicator representing a living state, memory means for storing the indicator measured up to the present point of time, and a rhythm of fluctuation of the indicator in a past predetermined period. And control means for outputting a drug ejection command at that time, and ejection means for ejecting the drug in accordance with the drug ejection command. According to the present invention, since the time at which the drug should be discharged is determined based on the fluctuation rhythm of the living body state, operations such as controlling or promoting the excited state or suppressing or promoting the calm state by the drug discharge are automatically performed as the optimum timing. This can be done.

A fifteenth invention includes measuring means for measuring an indicator representing a living state, storage means for storing the indicator measured up to the present time, and an indicator representing a rhythm of change of the indicator in a past predetermined period and a living state at the present time. And control means for outputting the drug discharge command on the basis of the discharge means and discharge means for discharging the drug in accordance with the drug discharge command. According to the present invention, since the ejection of the drug is controlled based on the fluctuation rhythm of the living state and the present living state, the ejection of the drug can be performed to rhythmically change the living state according to the constant rhythm fluctuation waveform.

A sixteenth aspect of the present invention provides measurement means for measuring an indicator representing a living state, control means for comparing the indicator with a predetermined reference value to determine a user's drowsiness status, and outputting a warning indication when the drowsiness status is detected; And a notification means for alerting the user based on the warning instruction. According to the present invention, the user's drowsiness can be detected by a relatively simple method, and the user can insert the device into a portable device that is always free to carry.

In a seventeenth aspect of the present invention, measurement means for measuring an indicator indicating a living state, storage means for storing the indicator measured over a predetermined time period, and an indicator indicating a living state in a past predetermined period are read out by the storage means, Calculating means for calculating a moving average of the indicator, control means for determining a user's drowsiness state by comparing the moving average of the indicator with a predetermined reference value, and outputting a warning instruction when the drowsiness state is detected; And notification means for alerting the user based on the instructions. According to the present invention, since the drowsiness state can be detected in consideration of the fluctuation rhythm of the living body state, it is possible to reduce the probability of error detection or omission of the drowsiness state.

EMBODIMENT OF THE INVENTION Hereinafter, the best form for implementing this invention with reference to drawings is demonstrated. In this embodiment, the present invention is divided into the following chapters so that those skilled in the art can easily implement the present invention.

In the first chapter, the periodic fluctuations of the biological state underlying the present invention will be described by mixing experimental results and the like. Next, in order to analyze the pulse wave, a means for extracting the pulse wave from the human body is required. Therefore, Chapter 2 describes various types of sensors for detecting pulse waves. Next, in Chapter 3, the realization means for taking out parameters which are good for the pulse wave analysis process from the detected pulse wave is described. Subsequent chapter 4 describes various biological states obtained from pulse waves and explanations of the analysis method of pulse wave waveforms for obtaining these biological states.

Chapter 5 also describes devices that can be commonly applied to the various devices introduced in Chapter 6, with respect to input and output means for interfacing humans and devices. In each apparatus described in Chapter 6, description is made using a means selected appropriately from each of these means, but most of them can be replaced by other means described in Chapter 5. The same applies to the pulse wave detection section of Chapter 2 and the pulse wave analysis method of Chapter 3.

In Chapter 6, various embodiments realized in the background of the knowledge obtained in Chapter 5 have been described in detail.

Chapter 1 Periodic Variation in Biological State

Section 1 Overview

Regarding the living state obtained by the pulse wave or the like, if attention is paid only to the living state at each measurement point, much knowledge can be obtained by using various pulse wave analysis methods as described in Chapter 4.

By the way, even in a healthy state, the living body state is actually changed to a predetermined rhythm. Therefore, it is considered that the analysis of the pulse wave in consideration of such fluctuating rhythms and the diagnosis thereof make it possible to grasp the living state more accurately. As a study from the viewpoint of the biological rhythm, a field called time biology has recently been attracting attention.

The state of the circulatory machine is changed according to a constant rhythm by a load such as stress, and more specifically, it is reported to repeat the change of periodicity with one cycle per day. For example, although sudden death has been a hot topic recently, the occurrence probability of sudden death also fluctuates periodically from one day to one cycle, and it has been reported that there are time zones with low probability of death and low time zones. Figure 2 illustrates the daily fluctuations in the occurrence of sudden death, Figure 3 illustrates the daily fluctuations in the occurrence of acute myocardial infarction. In addition, these data are described in Muller JE. Et al .: Circulation, 79: 733 to 734, 1989.

In addition to these, blood pressure, pulse rate, cardiac output, lung capacity, oxygen consumption, body temperature, hormone secretion, central nerve activity, cell division time, sleep, brain waves, pain, weight, incidence of angina, etc. There are more than 300 actual rhythms of physical function.

These rhythms become conscious of movement or excitement, resulting in a rapid pulse or breathing. In addition, it is possible to clearly recognize the abnormalities of the rhythm even when the physical condition is destroyed or when a disease occurs. In addition, the worsening of the body (body) control the day after overnight, not only sleep deprivation, but also caused by the decrease in body temperature caused by the activity rhythm and body temperature rhythm rhythm caused de-synchronization. Moreover, it is what is called parallax maladaptation to feel such an abnormality of rhythm singly. Parallax maladjustment is a symptom that occurs when a short time travels between points having a parallax of about 4 hours or more by an aircraft or the like, and such parallax maladjustment is common in the United States and the like where a country has a large area. This parallax mismatch occurs as the rhythm of a type of clock (bio clock) existing inside a living body does not synchronize with the outer rhythm of where it moves.

Since the living body state shows natural fluctuations according to a constant rhythm, it is difficult to accurately determine the living state only by diagnosis even at any point of time. For example, even if good results are obtained when the patient is diagnosed at a certain time, it cannot be concluded that the disease state of the patient is treated. This is because such a result may be obtained because the diagnosis is sometimes performed at a time when the biological state becomes good. In addition, when the patient was diagnosed at a certain point of time, even if the cardiac output amount, which is an example of the living state, was slightly increased, such a result was obtained because the diagnosis was sometimes performed at a time when the cardiac output amount was increased. This is because there is a possibility that there is no need to be particularly urgent. On the other hand, if the body state has always made an unnatural change that is different from the usual natural change, for example, if the cardiac output increases during the time when the cardiac output should drop, for example, even if the cardiac output value itself is in the normal range, It is because there is a possibility that some abnormality is occurring in the living body, and it is necessary to cope with this promptly. In this way, the diagnosis or treatment that does not take into account the rhythm of the living body (periodic fluctuation of the biological state) is not only meaningful but can be said to be dangerous.

Based on all the above points, the present inventor first tried the experiment on the periodic behavior of the living body state obtained from the pulse wave of a human body, and confirmed the presence of the periodic variation. Thus, the contents of the experiment and the details of the results will be described below with respect to the periodic variation of the living state.

Section 2 Daily Changes in Cyclic Dynamic Parameters

(1) Configuration of apparatus for experiment

The structure of the apparatus used for experiment is shown in FIG. In this figure, the pulse wave detection unit 160 detects an artery waveform of a finger node through a pressure sensor mounted on a subject's right wrist, and detects blood pressure through a cap mounted on an upper cuff of the subject, and detects an artery of the finger node. An electrical signal representing the waveform whose waveform has been corrected by blood pressure is output. In addition, the one-time ejection amount measuring unit 161 measures the one-time ejection amount in the subject and outputs an electric signal indicating the result. In addition, the detail of each part shall be demonstrated in "Chapter 2, Section 2-Section 3." In addition to the above devices, a personal computer (not shown) for controlling these devices and analyzing the measurement results was used. In addition, a single ejection amount is the quantity of blood which flows out by a single beat from a heart.

(2) measurement conditions

Thirteen healthy males (age 21 ± 9) were subjected to the same behavior in the same facility over 36 hours over two days. In addition, the temperature was kept at 24.0-24.5 ° C and the humidity was 40-50%.

5 shows a schedule of the experiment. As shown in this figure, the meal was given at noon and 6 pm and was given about 1700 Kcal per day as the same menu for two days. At bedtime 0 o'clock in the middle of the night and 6 o'clock in the morning, the patient wakes up for 6 hours and measures the arterial waveform and the amount of ejection of the finger node every 2 hours.

At the time of measurement, the subject was given a stable position for 15 minutes before the measurement, and during the measurement, normal breathing with a metronome of 0.25 Hz was performed at the stable position. And based on 10 heartbeats after 20 second, 30 second, 40 second, and 50 second after a measurement start, the average addition waveform for one night was calculated | required, and it was made into the object of the analysis demonstrated below.

(3) interpretation

The present inventors assume that the circulatory dynamic parameters of the human body constitute a 4-element concentrated constant model, and to confirm what temporal change each element of the 4-element concentrated constant model has, the arterial waves of the finger nodes measured in each subject and The cyclic dynamics parameter value corresponding to one stroke amount was calculated | required. The four-element concentrated constant model refers to an electrical model in which the human circulatory system is replaced as described in "Chapter 4 Section 1". This electrical model is composed of the elements of the resistors R _c , R _p , capacitance C, and inductance L, and these correspond to cyclic dynamic parameters representing the state of the human body's circulatory system.

(4) results

① Comparison between the first day and the second day

6, the shape of the temporal change over two days of the value of each element _Rc , _Rp , C, L of a 4-element lumped constant model is shown. In the figure, the plot of black round display shows the value of each element of 13 subjects extracted on the 1st day as an average value, and the plot of square display shows the average value of each element value extracted on the 2nd day. According to FIG. 6, it can be seen that the value of each element of the four-element concentrated constant model is changed in time substantially on the second day as in the first day.

② Rhythm analysis of daily fluctuations

Rhythm analysis of the temporal change of the mean value of 13 subjects regarding vascular resistance (R _c ) was performed. This result is shown in FIG. As shown in the figure, the daily fluctuation waveform of the resistor R _c consists of the fundamental spectrum and its harmonic spectrum about 20 hours before and after. Although not shown, the basic spectrum of the daily fluctuation waveforms of the other elements R _p , C, and L, like the resistor R _c , also has a period of about 20 hours.

8 shows waveforms of the fundamental wave spectrum of the daily fluctuation waveforms of the elements R _c , R _p , C, and L of the four-element concentrated constant model for each subject. In these figures, it can be seen that the daily variation of the cyclic dynamics parameter is an individual difference in both amplitude and phase.

On the other hand, Fig. 9 shows the average value of 13 subjects, the fundamental wave spectrum and the second harmonic spectrum obtained by the rhythm analysis for each of the elements R _c , R _p , C, L of the 4-element concentrated constant model. This is in contrast to the synthesized daily variation waveform.

③ Characteristic of daily fluctuation of circulation dynamics

According to the above experimental results, although there are individual differences in the daily fluctuation waveforms of the cyclic dynamic parameters R _c , R _p , C, and L, it can be said that all subjects also have common characteristics. That is, the values of R _c , R _p and L are large in the morning, gradually decrease over noon, and rise in the evening again after a small peak occurs. In addition, the value of C tends to be high in the first half of the day and decrease in the second half.

Section 3 Annual Changes in Cyclic Dynamic Parameters

In addition to the daily fluctuations, the cyclic dynamics parameter has a cyclical rhythm fluctuation (annual fluctuations) on a yearly basis. For example, compliance (C) is high in summer and low in winter. FIG. 10 is a graph showing an example of annual variation of the cyclic dynamics parameter, and FIG. 11 is a graph showing the results of the spectral analysis of the viscous resistance R _c of the central part.

Section 4 Daily Fluctuations in the Pulse Wave Spectrum

When frequency analysis was performed on the pulse wave waveform and the spectrum was observed, it was found that there was a daily variation similar to the cyclic dynamic parameters described above. According to the experiments of the present inventors, in particular, it is known that the phase of the fourth harmonic (phase based on the granularity of the pulse wave) changes greatly in accordance with the change of the physical state.

12A to 12C show examples of daily variation of the second, third, and fourth harmonic phases of the pulse wave, respectively. 13A shows an example of the daily variation of the amplitude of the third harmonic, and FIG. 13B shows an example of the daily variation of the normalized amplitude of the third harmonic.

Section 5 Theorem

By grasping the state of the human body on the basis of the periodic fluctuations of the indicators of the living state as described above, it becomes possible to grasp the living state very accurately and to detect abnormalities in the physical state.

In addition, although the spectrum obtained by the frequency analysis of a pulsation dynamics parameter and a pulse wave waveform as a living body is a problem here, it is thought that there exist a daily variation and an annual variation similarly also to the various living states demonstrated so far.

Chapter 2 Pulse Wave Detection Unit and One-Time Meter

This chapter describes the various sensors that various devices related to the present invention use for pulse wave measurement. In addition, in the diagnosis based on the pulse wave analysis and the analysis result described later, a single ejection amount may be required. Since this one-time ejection amount is to be measured together with the pulse wave, the meaning and measurement method will also be described here.

Section 1 pulse wave detector

Pulse wave sensor using strain gauge

(1) prototype 1

First, the present inventors test-operated the pulse wave sensor shown in FIG. 14A. In the illustrated example, the linear strain gauges 1-1 to 1-4 are fixed in parallel to the inside of the finger of the surgical rubber glove 5. By putting this rubber glove 5 on one hand and attaching the fingertip of the hand to the other cuff and measuring the resistance value of each strain gauge 1-1 to 1-4, a pulse wave can be detected.

(2) prototype 2

Next, the pulse wave sensor shown in FIG. 14B was tested. In the pulse wave sensor shown in the prototype 1, only the deformation | transformation of the longitudinal direction of a finger is measured, and this structure is enough if it is simply measuring the strength of a pulse. On the other hand, the pulse wave sensor of the said figure detects the deformation | transformation of the width direction as well as the longitudinal direction inside a finger. In the illustrated example, band-shaped strain gauges 2-1 to 2-4 are fixed to the inner side of the finger of the rubber glove 5 in parallel, and these strain gauges 2-1 to 2-4 are integrally formed. Formed.

(3) improved pulse wave sensor

By the way, in the structure of the prototype 2, each strain gauge 2-1, 2-4 is integrally formed, and there exists a possibility that interference may arise between strain gauges. In view of the above, the present inventors also developed the sensor described below. This sensor can detect the pressure distribution in the width direction of a finger, and can easily perform high-precision pulse wave detection.

The top view of the pulse wave sensor after improvement is shown in FIG. In this figure, 3-1 to 3-4 are thin band-shaped strain gauges, and are arrange | positioned in parallel in the longitudinal direction in the inside of the finger | tip of the rubber glove 5. Moreover, the thickness of the rubber gloves 5 is about "200 micrometers", and the means for fixing the strain gauges 3-1 to 3-4 to the rubber gloves 5 may be an adhesive for general gauges.

Here, the details of the strain gauges 3-1 to 3-4 will be described. The strain gauges 3-1 to 3-4 are thin film gauges, gauge rate "2.1", resistance "120 Ω", and width D "2. 8 mm ", length (L ₀ )" 9. 4 mm "and thickness" 15 micrometers. " The overall width M ₀ of the strain gauges 3-1 to 3-4 is set to about "12 mm" corresponding to the contact width when the finger of the true terminal is lightly pressed on the subject's arm. Therefore, the interval S between each gauge is about " 0 ". 27 mm ".

<Variation example>

① Quantity of strain gauge

(a) Although "4" strain gauges were set for each finger in the above, the number of strain gauges is not limited to "4" pieces. For example, as shown in FIG. 16, by providing a strain gauge of "5" or more, it is thought that the pulse wave detection with higher reliability becomes possible. Contrary to this, the number of strain gauges may be "4" or less.

② Characteristics of strain gauge

Although various specifications of the strain gauges 3-1 to 3-4 have been described, the strain gauges 3-1 to 3-4 are not limited to the above-described specifications. For example, the gauge rate is "2. It goes without saying that various values can be taken in addition to 1 &quot;, and various modifications can be made in the measurable range even with respect to the dimensions of the strain gages 3-1 to 3-4. .

Fig. 17 shows a state in which the pulse wave sensor is mounted on a rubber glove. In the figure, 5 is the surgical rubber glove described above, and the strain gauges 4-1 to 4-3 are attached to the inner side of the fingers of the first nodes of the second, third and fourth fingers. It is. In this example, a different specification from the strain gauge described above is used. That is, the strain gauges 4-1 to 4-3 are thin film gauges, gauge rate "170", resistance "2 KΩ", and width "0." 5 mm "and a length" 4 mm ". Each strain gauge 4-1 to 4-3 is fixed on a bendable thin plate base of "4 mm x 11 mm", and is bonded to the rubber glove 5 together with the thin plate base.

By using this sensor, it becomes possible to detect the pressing force of a finger simultaneously with a pulse wave. In addition, since the sensor is attached to the rubber glove, the measurement based on the sensor and the diagnosis based on the touch of the true terminal can be performed at the same time.

③ Structure of strain gauge

In Fig. 15, the strain gauges 3-1 to 3-4 are required to be adhered to the rubber gloves 5 at predetermined intervals, which makes production complicated. Thus, the strain gauge may be configured as shown in FIG. 18. In this figure, 6 is a thin film formed in a lattice form, and the strain gauges 7-1 to 7-4 are fixed to each lattice, respectively. Moreover, the edge part of each grating is narrow enough so that the lead wires 7-1a to 7-4a of each strain gauge can be arrange | positioned, respectively.

According to this structure, by simply adhering the thin film 6 to the rubber gloves 5, it becomes possible to arrange the strain gauges 7-1 to 7-4 at predetermined intervals. Further, the thin film film 6 is drilled between the strain gauges 7-1 to 7-4, and the width of each lattice becomes narrow at the end, so that each strain gauge 7-1 through the thin film film 6 is reduced. To 7-4), it is possible to prevent mutual interference.

④ Strain gauge installation position

Pulse wave sensors, such as a strain gauge, may be attached not only to the observer's hand but also to a measurement aid tool. That is, you may comprise so that a measurement auxiliary tool may be attached to a subject's vein and etc., and a measurement is performed. In addition, it is also possible to provide a pulse wave sensor to a robot hand etc. and to make automatic measurement by a robot.

The pulse wave detector for the strain gauge pulse wave sensor

Hereinafter, the pulse wave detection part which detects a pulse wave using the pulse wave sensor which consists of a strain gauge demonstrated in "Item 1" is demonstrated.

First Embodiment

<Configuration of Circuit>

The configuration of the pulse wave detection unit using the strain gauges 3-1 to 3-4 will be described with reference to FIG. 19. In this figure, the strain gauge 3-1 and the resistor 12 are connected in series, and a predetermined direct current voltage E is applied by the power supply 11. Therefore, the voltage Vi according to the resistance ratio of these resistors is generated at both ends of the strain gauge 3-1. 13 is a direct current | flow cut off filter and removes and outputs the direct current component of voltage Vi.

The output signal of the direct current cut filter 13 is amplified by the amplifier 14, and the output voltage Vo comes out through the low pass filter 15 having a cutoff frequency of "20 Hz".

19 shows the apparatus for the strain gauge 3-1 described above, but the same circuit is provided for the other three strain gauges 3-2 to 3-4, respectively.

<Operation of Circuit>

First, in order to operate the circuit correctly, the rubber glove 5 is attached to one hand in advance and pressed at the pulse wave detection site. In this state, the voltages Vi are respectively output from the strain gauges according to the pulsation. These voltages Vi are respectively removed by the corresponding DC blocking filter 13, and are respectively output through the corresponding amplifier 14 and the low pass filter 15, respectively.

<Variation example>

① Correction of temperature drift

In the circuit of FIG. 19, although the pulse wave was detected by directly measuring the voltage Vi which appears in the both ends of the strain gauge 3-1, the bridge circuit which makes the strain gauge 3-1 one side constitutes this bridge circuit. The pulse wave may be detected by detecting the voltage appearing on the diagonal side of. That is, by attaching the strain gage 3-1 and three thin film resistors having the same resistance temperature coefficient to the rubber glove 5 to form a bridge circuit, temperature drift due to body temperature or the like can be corrected. It is also possible to improve the sensitivity.

② Supply current to strain gauge

In the circuit of FIG. 19, a current is continuously supplied to the strain gauge 3-1, but the current supplied to the strain gauge 3-1 may be an intermittent one. That is, according to the circuit of this figure, since only the component of the frequency component of the voltage Vi is finally detected as a pulse wave below 20 Hz, for example, a pulse wave is sufficient by the result of sampling at the frequency of "40 Hz." It is possible to reproduce.

In this way, when the current supplied to the strain gauge 3-1 is made intermittent, power consumption can be reduced, and therefore, it is particularly suitable for use in portable equipment.

<< Second Embodiment >>

Hereinafter, the pulse wave detection part which detects a pulse wave by the strain gauge shown in FIG. 17 is demonstrated.

<Configuration of Circuit>

The configuration of the circuit according to the present embodiment will be described with reference to FIG. 21 is a constant current source, and supplies a constant current to the above-described strain gauge 4-1. As a result, a voltage V _g due to physical deformation is generated at both ends of the strain gauge 4-1. This voltage V _g is amplified by the DC amplifier 22 and supplied to the DC blocking circuit 23 and the averaging circuit 25.

The voltage output from the DC amplifier 22 can be expressed as "V _o + V _d + ΔV". Here, the voltage V _o is the voltage generated when the rubber glove 5 is mounted on the hand, and the voltage V _d is the voltage generated by the pressing force when the finger is pressed on the arm. AC voltage caused by pulse pressure.

In the DC blocking circuit 23, the former two of the voltages V _o , V _d and ΔV are removed, and a voltage ΔV, that is, an AC component, that is, a pulse wave signal is output. The pulse wave signal is output from the low pass filter 24 after the noise is removed through the low pass filter 24 having a cutoff frequency of "20 Hz".

On the other hand, in the averaging circuit 25, the maximum value of the voltage "V _o + V _d + DELTA V" is detected, and the voltage is over several cycles as one cycle until the next maximum value occurs after one maximum value occurs. " _Vo + V _d + DELTA V" is averaged. Thereby, voltage (DELTA) V which is an AC component is removed, and the voltage " _Vo + _Vd " which is a DC component is output.

Reference numeral 26 denotes a level memory circuit. When the switch 26a is pressed, the output voltage level of the averaging circuit 25 at that time is stored, and then the voltage of the stored level is continuously output.

27 is a subtractor. The output voltage of the level memory circuit 26 is calculated from the output voltage of the averaging circuit 25, and the subtraction result is output.

Although not directly related to pulse wave detection, 28 is a well-known sphygmomanometer, and when it is necessary to measure blood pressure in a subject, blood pressure is measured and output through the cap S2.

In addition, although each component of 21-27 is the strain gauge of FIG. 17, it is provided corresponding to the strain gauge 4-1, but is actually the same circuit corresponding to the strain gauges 4-2 and 4-3. Is installed.

<Operation of Circuit>

When the rubber glove 5 is mounted, the voltage V _o is output from the DC amplifier 22. When the switch 26a is pressed in this state, the voltage _Vo is stored in the level memory circuit 26. Next, when the fingertip is pressed on the arm with the rubber glove 5 attached, the voltage V _o + V _d is output from the averaging circuit 25, so that the voltage V _d corresponding to the pressing force through the subtractor 27 is obtained. ) Is output. At the same time, the voltage DELTA V corresponding to the pulse wave is output through the DC blocking circuit 23 and the low pass blocking filter 24 in sequence.

3. Photoelectric (Optical) Pulse Wave Sensor

(1) configuration and operation

As an example of the pulse wave sensor using light, there is a photoelectric pulse wave sensor, and FIG. 21 shows the configuration of the photoelectric pulse wave sensor 31. In the figure, the light emitting element 32 is composed of an infrared light emitting diode having a wavelength of 940 nm, and the optical sensor 33 is composed of a phototransistor or the like.

The light emitted from the infrared light emitting diode 32 is absorbed by the hemoglobin of red blood cells in the blood vessel passing directly under the skin that the photoelectric pulse wave sensor 31 contacts, and the amount of reflected light reflected by the subcutaneous tissue or the like changes. This reflected light is received by the optical sensor 33, and the pulse wave detection signal M is obtained as a result of photoelectric conversion.

(2) low power

When the pulse wave sensor is combined with, for example, a battery watch, it is preferable to drive the source of the photoelectric pulse wave sensor 31 only when it is necessary to measure the pulse wave in order to reduce the power consumption. For this reason, the switch as shown by the symbol SW of FIG. 21 is provided in the line which supplies power to a pulse wave sensor. A switch circuit (not shown) changes the on / off state of each of these switches and continuously supplies power to a sensor or the like.

For example, when the battery wrist watch operates only as a normal wrist watch, the switch SW is turned off, and the photoelectric pulse wave sensor 31 is supplied with power, while pulse wave measurement is required. The switch SW is turned on and power is supplied to the photoelectric pulse wave sensor 31.

Fig. 22A is a timing signal for switching the on / off state of each switch, and shows a signal that is in the " H " (high level) state only in the mode (denoted as an analysis mode in the drawing) when pulse wave is measured. In the figure, during the non-magnet mode (i.e., while the battery watch is only operating as a normal wrist watch), this timing signal is in the "L" (low level) state, and the switch SW is It is off and no power is supplied to the sensor. On the other hand, when the analysis mode is set, the timing signal is in the "H" state, the switch SW is turned on, and power is supplied to the sensor. After that, when the analysis mode ends, the timing signal is set to the "L" state again, the switch SW is turned off, and power is not supplied to the sensor.

If the time of pulse wave measurement is short in view of the entire time the user wears the wrist watch, the sensor is supplied with power based on the timing signal as described above, so that the current is supplied to the sensor only when the pulse wave needs to be measured. The overall power consumption can be significantly reduced.

(3) Modification

(1) In consideration of the signal-to-noise (SN) ratio, blue light is more preferable as the light emitting diode used in the light emitting device.

(2) As a further countermeasure for power saving, as shown in Fig. 22B, in the analysis mode, when the on / off state of the switch SW is changed based on the timing of the pulse signal which becomes the "H" state only when the pulse wave detection signal is actually put in. do.

(3) Regardless of whether it is in analysis mode or not, the on / off state of the switch SW may be switched on the basis of the timing of the pulse signal that becomes the "H" state only when the detection signal from the sensor is used.

Section 4 pressure pulse wave sensor

Hereinafter, the pulse wave detection unit in which the pulse wave sensor is combined with a portable device will be described. In addition, it is not limited to the form demonstrated below actually, It is also possible to combine with what exists around other everyday bodies.

In this section, a form in which the pressure sensor is combined with a wrist watch will be described with reference to FIG. 23. In this figure, 40 is a wrist watch, 41 is a main body of the wrist watch, and 42 and 43 are display sections for performing various displays. In addition, 44-46 are buttons, and since these functions differ with respect to the various apparatuses mentioned later, they are demonstrated individually when describing each apparatus. In addition, 47 is a pressure sensor, 48 is an installation tool, and the pressure sensor 47 and the installation tool 48 comprise the pulse wave detection part for detecting a pulse wave.

The pressure sensor 47 is provided on the surface of the mounting tool 48, and the mounting tool 48 is slidably mounted to the watch band 49. Then, by attaching the wrist watch 40 to the wrist, the pressure sensor 47 is pressed to the artery of the finger joint at an appropriate pressure. The pressure sensor 47 is composed of, for example, a strain gauge, and a pulse wave signal representing the arterial waveform of the finger joint is obtained as an analog amount at terminals (not shown) provided at both ends of the pressure sensor 47. This pulse wave signal is outputted to the main part of the device incorporated in the main body 41 of the wrist watch through a signal line (not shown) which has entered the watch band 49.

Section 5 pressure pulse wave sensor

(1) configuration and operation

In this section, the form which combined the pulse wave detection part using a pressurized pulse wave sensor with a wrist watch is demonstrated. 24 shows the mechanical configuration of this pulse wave detection unit. In the figure, reference numeral 50 denotes a main body of the wrist watch, and a finger contact portion 51 and various buttons or display portions are provided. The finger contact portion 51 is such that the user presses, for example, the fingertip of the second finger on the side of the side on which the wrist watch is not mounted. In addition, the functions of the display sections 52, 52a, 52b and the buttons 53 to 55 are different for each device in which the pulse wave sensor is used. In addition, the arrow in FIG. 24 means the viewing direction of a display part.

25 shows a more detailed configuration of the pulse wave detection unit. In this figure, a photoelectric pulse wave sensor 56 and a strain gauge 57 are provided on the rear side of the finger contact portion 51. This photoelectric pulse wave sensor 56 has the above-described configuration and outputs a pulse wave detection signal M. As shown in FIG. In addition, since the resistance value of the strain gauge 57 changes in accordance with the deformation, the pressure signal P according to the pressing force of the user's finger pressed through the finger contact portion 51 is detected.

This pressure signal P is used for the user to adjust the pressing force of a finger so that the value of the pulse wave detection signal M obtained by the photoelectric pulse wave sensor 56 may become the maximum. As a result, the device connected to the pulse wave detector inserts a pressure signal P and indicates whether or not the pressure applied by the finger is within the range of the appropriate pressure, so that the user adjusts the pressure of the finger so as to receive the pressure within the range. It is.

(2) Modification

(1) The pressure contacting means is not limited to the strain gauge, and the finger contact portion 51 may be a movable mechanism by a spring, and the pressing force may be detected by the elasticity of the spring.

(2) The portion in contact with the finger contact portion 51 is not limited to the tip of the finger, but may be pressure-measured to the toe or the other end portion in the same manner.

(3) A window may be provided on the back of the main body 50 of the watch, and a plastic plate or the like may be inserted to expose the photoelectric pulse wave sensor 56 from this window. In this way, the pulse wave of the blood vessel which passes just under the skin which contacts the said plastic board provided in the back surface of the main body 50 is obtained.

(4) As described above, the photoelectric pulse wave sensor 56 is provided with a switch for lowering power consumption. However, if the strain gauge 57 is provided with a synchronous switch, the lower power consumption can be similarly achieved.

Section 6 pulse wave detection unit in combination with a portable device other than the wristwatch

In the above, the case of combining with a wrist watch has been described. However, as described in this section, a combination with a portable device can be considered.

(1) Necklace-type pulse wave detector

Here, the case where the photoelectric pulse wave sensor is combined with an accessory (or jewelry) will be described. Here, the necklace shown in FIG. 26 is handled as an example of an accessory. 61 in this figure is a sensor pad, for example, which consists of a cushioning material on a sponge. In the sensor pad 61, a photoelectric pulse wave sensor 62 is provided to contact the skin surface. Thereby, when this necklace is put on a neck, the photoelectric pulse wave sensor 62 can contact a skin of the back of a neck, and can measure a pulse wave.

Moreover, the main part 63 of the apparatus which incorporated this pulse wave detection part is integrated in the main body 63 which has a hollow part. The main body 63 is a case having a broach shape, and a front surface thereof is provided with a graphic display unit or a button, for example. In addition, the functions of these display sections 64 and buttons 65, 66 differ for each device into which the pulse wave detection section enters.

In addition, the photoelectric pulse wave sensor 62 and the main body 63 are each attached to the necklace 67, and are electrically connected through the lead wire (not shown) which entered into this necklace 67. As shown in FIG.

<Variation example>

① Accessories may be other than necklaces.

(2) In the case of using this form for dispensing the drug as described later, as shown in Fig. 27, the injection holes 68 and 69 of the drug are provided in the front of the main body 63. Alternatively, the injection holes 68 and 69 of the drug may be provided on the entire surface of the main body 63 to discharge the drug directly to the skin.

③ As will be described later, in the case of using this form for administration, as shown in Fig. 28, the injection needle (71, 71) through the tubes (70T, 70T) for drug administration on the front of the main body 63 Install.

(4) The injection holes 68 and 69, the tube 70T, and various buttons may be provided anywhere in the main body 63.

(5) In the various devices described below, an acceleration sensor is used to measure a user's physical condition. Thus, the acceleration sensor may be provided adjacent to the photoelectric pulse wave sensor 62.

(2) pulse wave detection unit of spectacle type

Here, the case where the photoelectric pulse wave sensor is combined with glasses is demonstrated. Moreover, in the form of this spectacles, the display device as a notification means to a user is also assembled together. Therefore, the function as a pulse wave detection part is also demonstrated in parallel.

It is a perspective view which shows the mode which attached the apparatus with the pulse wave detection part to glasses. As shown in the figure, the apparatus main body is separated into a main body 75a and a main body 75b, and are separately provided on the spectacles leg 76, and these main bodies are electrically connected to each other through a lead wire that enters the spectacles leg 76. It is.

The main body 75a incorporates a display control circuit. A liquid crystal panel 78 is provided on the front surface of the main body 75a on the lens 77 side, and a mirror 79 is provided on one end of the main body 75a. It is fixed at a predetermined angle. In the main body 75a, a driving circuit of the liquid crystal panel 78 including a light source (not shown) and a circuit for creating display data are assembled. Light emitted from this light source is reflected as a mirror 79 through the liquid crystal panel 78 and is projected onto the lens 77 of the spectacles. Moreover, the main part of the apparatus is incorporated in the main body 75b, and various buttons are provided in the upper surface. In addition, the functions of these buttons 80 and 81 differ from device to device.

On the other hand, the infrared light emitting diode and the optical sensor (see Fig. 21) constituting the photoelectric pulse wave sensor are incorporated in the pads 82 and 83, and the pads 82 and 83 are fixed to the earballs. These pads 82 and 83 are electrically connected to each other by lead wires 84 and 84 from the main body 75b.

<Variation example>

(1) The lead wire connecting the main body 75a and the main body 75b may extend along the spectacles leg 76.

(2) The main body portion was divided into two, the main body 75a and the main body 75b, but these may be integrated.

(3) When this form is used for drug discharge, as shown in Fig. 30, the injection holes 86 and 87 of the drug may be provided on the upper surface of the main body 75b.

(4) When this form is applied to the perfume discharge device, the injection holes 86 and 87 are provided on the side of the head side of the main body 75b, and the perfume is discharged to the skin.

⑤ If this form can be used for dosing, as shown in FIG. 31, the injection needles 89 and 90 are provided in front of the upper surface of the main body 75b through the tubes 88T and 88T for drug administration. .

(6) The injection holes 86, 87, the tube 88T, the various buttons, and the like may be provided anywhere in the main body 75b.

The mirror 79 may be movable so that the user can adjust the angle between the liquid crystal panel 78 and the mirror 79.

The wrist watch type pulse wave detection unit having a sensor installed at the bottom of the finger

In the case where the pulse wave detection unit is combined with a wrist watch, the configuration in which the pulse wave sensor itself is attached to the bottom of the finger will be described with reference to FIGS. 32 to 34.

First, the detailed structural example of the wrist watch put into practical use by this inventor is demonstrated. As shown in Fig. 32, the device connected to the pulse wave detecting unit includes a device main body 100 having a wrist watch structure, a cable 101 connected to the device main body 100, and a tip side of the cable 101. It consists of the sensor unit 102 provided.

The apparatus main body 100 is provided with a wrist band 103 wound around the user's arm at 12 o'clock of the wrist watch and fixed at the 6 o'clock direction of the wrist watch. The apparatus main body 100 is detachable from the user's arm by the wrist band 103.

In addition, the sensor unit 102 is shielded by the sensor fixing band 104, and is mounted between the bottom of the user's index finger and the second finger joint. When the sensor unit 102 is attached to the bottom of the finger in this way, the cable 101 ends shortly and, for example, the cable 101 does not disturb the user even during exercise. In addition, when the distribution of the body temperature from the palm to the fingertip is measured, when the ambient temperature is low, the temperature of the fingertip is remarkably decreased, whereas the temperature at the bottom of the finger does not relatively decrease. Therefore, when the sensor unit 102 is attached to the bottom of the finger, accurate measurement is possible even when exercising outdoors on a cold day.

On the other hand, the connector part 105 is provided in the surface side of the wristwatch at 6 o'clock. The connector piece 106 is detachably attached to the connector portion 105 at the end of the cable 101, and the device is removed by removing the connector piece 106 from the connector portion 105. I can use it as a watch and a stopwatch. Moreover, in order to protect the connector part 105, the predetermined connector cover is attached in the state which peeled off the cable 101 and the sensor unit 102 from the connector part 105. As shown in FIG. This connector cover is used in a component configured like the connector piece 106 except for the electrode portion.

According to the connector structure comprised in this way, operation becomes easy when the connector part 105 is regarded as a user. In addition, since the connector portion 105 does not extend out from the device body 100 in the direction of 3 o'clock of the wrist watch, the user can freely move his wrist even during exercise, and the back of the hand is connected to the connector portion 105 even if the user changes during the exercise. Don't bump into

Next, other components in FIG. 32 will be described with reference to FIG. 33. FIG. 33: shows the detail of the apparatus main body 100 in this form as a state which peeled the cable 101 and the wrist band 103. As shown in FIG. Here, the same components as those in Fig. 32 are denoted by the same reference numerals and description thereof will be omitted.

In FIG. 33, the apparatus main body 100 includes a watch case 107 made of resin. On the surface of the watch case 107, a liquid crystal display 108 for digitally displaying pulse wave information such as a pulse value in addition to the current time or date is provided. The liquid crystal display device 108 includes a first segment display region 108-1 positioned at the upper left of the display surface, a second segment display region 108-2 positioned at the upper right, and a first positioned lower right. It consists of a three segment display area 108-3 and a display area 108-D located at the lower left.

Here, the date, day of the week, current time, and the like are displayed in the first segment area 108-1. In the second segment region 108-2, the process time and the like are displayed in performing various types of time measurement. In the third segment region 108-3, various measured values measured in the pulse wave measurement are displayed. In the dot display area 108-D, various types of information can be displayed graphically, and various displays such as mode display indicating which mode the device is in at what time, pulse wave display, bar graph display, etc. Is possible.

In addition, the mode mentioned here includes a mode for operating as a diagnosis device, a mode pulse wave analyzing device for use as a mode for setting a time, a date, and the like. Since these modes and the contents displayed in the above-described display areas are different depending on the use, they will be described as necessary.

On the other hand, inside the watch case 107, a control unit 109 for performing signal processing or the like for displaying on the liquid crystal display device 108 is incorporated. The control unit 109 may be a general microprocessor or one-chip microcomputer composed of a CPU (central processing unit), a RAM (random access memory), a ROM (read only memory), or the like. In addition, the control unit 109 includes a clock circuit for displaying the time. The liquid crystal display device 108 can display the time of operation, and as a mode for operating as a stopwatch, live time and split are shown. It is possible to display a split time or the like.

On the other hand, button switches 111 to 117 are provided on the outer peripheral portion and the surface portion of the watch case 107. Although an example of the function of these button switches is shown below, about the mechanism, the function differs with respect to each apparatus combined with a wristwatch.

First, when the button switch 111 in the 2 o'clock direction of the wrist watch is pressed, an alarm sounds when 1 hour has elapsed from the time when the button is pressed.

The button switch 112 at 4 o'clock of the wrist watch is for instructing the switching of various modes of the device.

When the button switch 113 at the 11 o'clock position of the wrist watch is pressed, the EL (Electro Luminescence) backlight of the liquid crystal display device 108 turns on, for example, for 3 seconds, and then automatically turns off.

The button switch 114 at the eight o'clock position of the wrist watch is for changing the type of graphic display to be displayed in the dot display area 108 -D.

By pressing the button switch 115 at the 7 o'clock position of the wrist watch, it is possible to switch which of the hour, minute, month, date, and 12/24 hour display switching is set as the mode for correcting the time and date.

The button switch 116 located below the liquid crystal display device 108 is used to correct the set value one by one in correcting the time and date. In the case of measurement, it is used also as a switch for teaching each lap to the control part 109.

The button switch 117 located above the liquid crystal display device 108 is used to give an instruction to start / stop an operation as a pulse wave analyzer or a diagnostic device. In addition, this button switch is used to snap the set value back one by one in the time and date correction mode, and is also used to instruct the start / stop of various elapsed time measurements.

Also provided as a power source for the wrist watch is a button-type battery 118 incorporated in the watch case 107. The cable 101 shown in FIG. 32 is connected to the sensor unit 102 from the battery 118. It is responsible for supplying electric power and sending the detection result of the sensor unit 102 to the control unit 109.

In addition, as the wristwatch increases its function, it is necessary to enlarge the apparatus main body 100. However, there is a restriction that the arm is mounted on the arm, so that the apparatus main body 100 cannot be expanded to the 6 o'clock or 12 o'clock direction of the wrist watch. Thus, in this embodiment, the watch case 107 having a longer length than the length size in the 3 o'clock and 9 o'clock directions of the wristwatch is longer than that in the 6 o'clock and 12 o'clock directions.

In this embodiment, the wrist band 103 is connected to the watch case 107 which is biased toward the 3 o'clock direction. In addition, when viewed from the wrist band 103, it has a large stretched portion 119 in the 9 o'clock direction of the wrist watch, but this large stretched portion does not exist in the 3 o'clock direction of the wrist watch. Therefore, by using the watch case 107 which is horizontally long, it is possible for the user to bend the wrist and do not cause the back of the hand to hit the watch case 107 even if the user changes.

In addition, inside the watch case 107, a flat piezoelectric element 120 used as a buzzer is disposed in the direction of 9 o'clock with respect to the battery 118. The battery 118 is heavier than the element 120, and the center position of the device main body 100 is at a position biased in the 3 o'clock direction. By the way, since the wrist band 103 is connected to the surface which centered, the apparatus main body 100 can be attached to an arm in a stable state. Often, since the battery 118 and the piezoelectric element 120 are disposed in the surface direction, the device main body 100 can be thinned, and the battery cover is easily provided by the user by installing a battery cover on the back of the wrist watch. Can be exchanged.

In addition, a part of the above-described embodiments is modified, and as shown in FIG. 34, the sensor unit 102 and the sensor fixing band 104 are provided at the tip of the finger, and the pulse wave at the tip of the finger is measured. Consider.

8. The pulse wave detection unit using the elastic rubber

The pulse wave detection part described below is a "pressure sensor" which detects a pressure vibration using elastic rubber and performs pulse wave detection.

<< first form >>

(1) the structure of the pressure sensor

The pressure sensor 130 calculates the pressure vibration generated by the pressure on the elastic rubber 131 by the operator and the generated coordinates. 35A and 35B are perspective and perspective views, respectively, illustrating the configuration of the pressure sensor, and FIG. 35A shows a partial cross section for explanation. As shown in these figures, the pressure sensor 130 is composed of pressure-sensitive elements S ₁ to S ₄ and hemispherical elastic rubber. In addition, the shape of the elastic rubber 131 is demonstrated as an ideal hemispherical surface here.

Each of the pressure reduction elements S ₁ to S ₄ is provided on the bottom (plane: L) of the elastic rubber 131, and outputs voltages V ₁ to V ₄ proportional to the detection pressure as detection signals, respectively. An example of a structure is mentioned later. Coordinates (x, y) of the detection positions (Q ₁ to Q ₄ ) by these pressure-sensitive elements (S ₁ to S ₄ ), the radius of the elastic rubber 131 is r, the center of the bottom surface (L) of the origin (0, 0), respectively

(a, 0), (0, a), (-a, 0), (0, -a)

Where r> a> 0.

That is, the coordinates at which pressure is to be detected by the pressure-sensitive elements S ₁ to S ₄ are on the x and y axes of the bottom surface L, and are separated from each other by an equidistance a from the origin.

Next, the junction between the pressure-sensitive element and elastic rubber 131 will now be described, for pressure-sensitive element (S ₁₎ as an example. 36 is a sectional view showing the principal parts of the structure of the pressure reduction element S ₁ .

The bottom face (L) of the elastic rubber 131, the pressure-sensitive element for detecting a pressure of the semiconductor substrate 132, is bonded by an adhesive 133 having elasticity, the semiconductor substrate 132, the detection position (Q ₁₎ S ₁ is formed at the same time as the hollow chamber 134-1 opening at the detection position. This pressure-sensitive element S ₁ is composed of a thin portion (about several tens of micrometers, 135-1) used as a diagram and a strain gauge 136-1 formed on the surface of the thin portion 135-1.

The pressure reduction element S ₁ is formed as a well-known semiconductor etching technique, and in particular, the strain gauge 136-1 is formed using a selective diffusion technique of impurities (for example, boron). Layer). When such strain gauge 136-1 is deformed, its resistance value changes according to the deformation.

Similarly, the pressure reduction elements S ₂ to S ₄ are formed on the semiconductor substrate 132, and the resistance values thereof change in proportion to the pressure at the detection positions Q ₂ to Q ₄ .

In the pressure sensor 130 having such a configuration, when pressure vibration occurs on the hemispherical surface of the elastic rubber 131, the pressure vibration propagates within the elastic rubber 131 as an elastic wave and is detected at the detection positions Q ₁ to Q ₄ . Each is vibrated and the respective pressures in the hollow chambers 134-1 to 134-4 are varied. At this time, each of the strain gauges 136-1 to 136-4 is the pressure between the respective internal pressures of the hollow chambers 134-1 to 134-4 and the external pressure passing through the atmospheric pressure release ports 137-1 to 137-4. Since each is deformed by the difference, each resistance value changes according to the corresponding pressure vibration.

On both ends of the strain gauges 136-1 to 136-4, aluminum electrodes (not shown) for guiding to an external circuit are deposited, and resistance / voltage conversion is performed by circuits described later, respectively, and the corresponding voltages are detected at the detection position ( as a detection voltage (V ₁₎ proportional to the pressure in Q ₁ to Q ₄₎ it is to be output.

Here, if necessary, each of the hollow chambers 134-1 to 134-4 is not simply empty, but filled with a low thermal expansion coefficient liquid (eg water, alcohol) or a liquid substance (eg gelatin). It is good also as a structure. Thereby, the micro-vibrations generated at the detection positions Q ₁ to Q ₄ , respectively, can be converted into detection signals by the strain gauges 136-1 to 136-4 more accurately as a low loss rate.

Next, the electrical connection of the pressure-sensitive elements S ₁ to S ₄ in the pressure sensor 130 and the bias method thereof will be described with reference to FIGS. 37 and 38. 37, each of the strain gauges 136-1 to 136-4 is equivalently shown as a variable resistor.

As shown in FIG. 37, each of the strain gauges 136-1 to 136-4 corresponding to the pressure-sensitive elements S ₁ to S ₄ are connected in series with each other, and the output terminals 138, ... 138 are provided.

Then, both ends of the series of strain gauges 136-1 to 136-4 are connected to the bias circuit 139. The bias circuit 139 includes a constant current circuit 140, a switch 141 for turning on / off the output signal of the constant current circuit 140, and a switch (when the control signal T is in the "H" state). 141 is configured as a switching circuit 142 to turn on. That is, while the control signal T is in the "H" state, the output signal of the constant current circuit 140 is applied to the strain gauges 136-1 and 136-4.

As described above, since the resistance value of the strain gauge changes with deformation, when the strain gauges 136-1 and 136-4 flow the same constant current, the voltage between the respective output terminals 138,... V ₁ to V ₄ ) are proportional to the respective pressures at the detection positions Q ₁ to Q ₄ , respectively, and relatively represent the magnitudes of the pressures.

By the way, the waveform pattern of a control signal is considered various by the magnitude | size of a device which processes the detection signal of the pressure sensor 130, a specification, etc .. For example, the control signal T is a signal that always becomes " H " regardless of the measurement time and the non-measurement time (TS1: see FIG. 38A), and the " H " Pulse signal (TS1: see FIG. 38B) to be in the state (having a predetermined duty ratio), " H " state only at the time of measurement (TS2: to FIG. 38C), " H " The pulse signal TS4 (see Fig. 38D) is selected (having a predetermined duty ratio). In addition, the measurement time here refers to the period in which pressure vibration is detected.

In the apparatus for processing the detection signal of the pressure sensor 130, if the detection accuracy is required, the signal TS1 is suitable for the control signal T. On the other hand, if it is desired to reduce the power consumption, the pulse signal TS4 is suitable for the control signal T. Further, in this processing apparatus, if the positioning of an intermediate characteristic between detection accuracy and low power consumption is made, a pulse signal TS2 or a pulse signal TS3 is suitable. These are based on the following reasons.

Since constant current flows through the strain gauges 136-1 to 136-4, some heat generation is followed. For this reason, a temperature difference arises at the time of bias application, and when it does not, and since a resistance value subtly differs by this temperature difference, it becomes a cause of an error at the time of pressure detection. When the signal TS1 is used as the control signal T, a constant current is applied to the strain gauges 136-1 to 136-4 even at the time of non-detection, and the pressure is detected when the heat generation saturates after a certain time. This is because the measurement error due to the temperature difference can be made very small after that.

On the other hand, when the pulse signal TS is used as the control signal T, since a constant current is intermittently applied to the strain gauges 136-1 and 136-4 only at the time of detection, heat generation by the current is suppressed and low power consumption. Because it can contribute to. At this time, if each part (A / D analog / digital conversion, amplifier, etc.) of the detection signal processing apparatus of the pressure sensor 130 is operated in synchronization with the pulse signal TS4, the power consumption can be further reduced. . In the extreme, the energization of each of these parts may be performed only when the pulse signal TS4 is in the "H" state.

As the constant current bias, the constant current circuit 140 may output a constant current pulse (see FIG. 38E) having a sufficiently shorter interval than the pulse signal TS2 or the pulse signal TS4. In this case, it goes without saying that the signals TS1 to TS4 may be combined as the control signal T. In particular, when the pulse signal TS4 is used, the bias is applied to the strain gauges 136-1 to 136-4, as shown in Fig. 38F, so that the period of application of the bias is very short, so that the power consumption can be very small. In this case as well, by operating each part of the detection signal processing apparatus of the pressure sensor 130 in synchronization with the constant current pulse, the power consumption can be made smaller. In addition, if the energization of each of these parts is performed only when bias is applied, the power consumption can be made very small.

In addition, the bias application interval is required to be short (satisfying the sampling theorem) to sufficiently cope with the change in the pressure vibration, and the output device must be within a range that can be coped with.

In addition, the pressure reduction elements S ₁ to S ₄ are preferably formed on the same semiconductor substrate 132. It is because it is easy to form and arrange | position integrally, if it has a semiconductor manufacturing technique, and it is advantageous more precisely and processly than forming and arrange | positioning a pressure reduction element individually. In addition, by using the semiconductor manufacturing technology, it becomes possible to manufacture the pulse wave detector with a very small size and high accuracy.

(2) principle of pulse wave detection and coordinate calculation

Next, the principle of pulse wave detection and coordinate detection by the pressure sensor 130 of such a structure is demonstrated. Moreover, as an artery made into object in this invention, it is supposed to pass through the skin superficial layer. FIG. 39 is a perspective view for explaining the principle of pulse wave detection and coordinate calculation, which is simplified for explaining the pressure sensor 130 shown in FIGS. 35A and 35B.

As shown in FIG. 40, it is assumed that the vicinity of the artery on the hemispherical side of the elastic rubber 131 (here, referred to as the finger joint artery 143 for explanation) is pressed. In this case, the point P on the hemispherical surface of the elastic rubber 131 generates vibration by the pressure vibration wave (that is, the pulse wave) generated in the artery 143 of the finger node. Here, the point P _a is the center of gravity of vibration (center). These vibrations propagate the elastic rubber 131 and are output as electric signals indicating pulse waves by the pressure-sensitive elements S ₁ to S ₄ , that is, detection signals having voltages V ₁ to V ₄ , respectively.

Therefore, the principle of the coordinate calculation of a pressure vibration point is demonstrated below.

If the hemispherical side of the elastic rubber 131 is pressed near the artery such that the artery 143 of the knuckle is projected on the bottom face L, the point on the hemispherical surface of the elastic rubber 131 at time t = n. (P _a), the vibration is generated by the pulse wave generated in the artery 143 of the knuckle. This vibration propagates the elastic rubber 131, attenuates in proportion to the square of the propagation distance, and is a detection signal representing the pulse wave with the voltages V ₁ to V ₄ by the pressure-sensitive elements S ₁ to S ₄ . Each is detected.

By the way, the equation showing the spherical surface of the elastic rubber 131 is as follows.

x ² + y ² + z ² = r ²

(Where z> 0)

Therefore, if the coordinates (x, y, z) of any point P _a on the spherical surface of the elastic rubber 131 are x _a , y _a , respectively, Same as

Each distance between the point P _a and the detection positions Q ₁ to Q ₄ of the pressure-sensitive elements S ₁ to S ₄ is represented by the following equation in equation c and equation a representing the coordinates of the respective detection positions described above. Same as the equation.

Next, since the vibration generated at the point P _a is attenuated in proportion to the square of the propagation distance of the elastic rubber 131, the values of the voltages V ₁ to V ₄ detected by the elements are mutually point P _It is inversely proportional to the square of the distance of the detection position of the element corresponding to _a ). Therefore, the following equation holds.

In addition, x, y coordinate values (x _a , y _a ) of the point (P _a ) in the equation (e) is as follows.

As described above, when a pressure vibration due to the pressure generated by the pulse wave occurs at the point P _a on the hemispherical surface of the elastic rubber 131, the detection voltage V ₁ to V _{4 of the} decompression elements S ₁ to S ₄ occurs. The coordinate values (x _a , y _a ) of the point P _a can be found. This point (P _a) a pressure-sensitive element (S ₁ to S ₄₎ plane of the detection position (xy plane), i.e., points a vertical projection on the lower surface (L) of the elastic rubber (131) (P _'a) the coordinates of the It is clear that (see FIG. 39) is obtained.

In the equation (f), the pressure value V ₁ , V _{3 of} the pressure-sensitive elements S ₁ , S ₃ provided with the coordinate value x _a on the x axis, and the pressure value y _{a with the} coordinate value y _a provided on the y axis Since the voltages V ₂ and V ₄ of the elements S ₂ and S ₄ can be obtained independently, mutual influences can be excluded in calculating the coordinates.

This can be seen by examining Equation e in detail, and the voltages required to obtain the coordinate values (x _a , y _a ) are three of the decompression elements S ₁ to S ₄ . In the above case, the calculation of one coordinate value affects the other coordinate value. For example, the pressure-sensitive element (S ₁ to S ₃₎ coordinates by only (x _a, y _a) the order to calculate first coordinates value (x _a) calculating the in the voltage (V _1, V _3), and next Substituting this coordinate value (x _a ) into the equation f, the coordinate value (y _a ) can be calculated from the voltage (V ₂ ), but the coordinate value (y _a ) is the voltage (V ₁ to V ₂ ) This is because the coordinates cannot be calculated accurately when there is a difference in output characteristics of the pressure-sensitive element.

On the other hand, when four pressure reduction elements are provided, the position where a pressure is detected will be arranged symmetrically with respect to the bottom center of the elastic rubber 131. For this reason, even when the pressure-vibration generation point on the exposed surface moves, the damping property of the elastic rubber 131 can be equivalent to each pressure-sensitive element. In addition, if the direction of movement of the pressure vibration point passes through the apex of the elastic rubber 131 and coincides with one of the set axes of the detection position, the propagation distance of the elastic waves can be minimized, and the pressure can be detected with higher accuracy. have.

(3) Operation of the pulse wave detector

① Measurement form

The form of the measurement in the case where detection of the pressure vibration is performed by the artery of the finger joint of the subject will be briefly described.

FIG. 41 is a perspective view showing an appearance configuration when the pressure sensor 130 is combined with a wrist watch. As shown in this figure, the elastic rubber 131 of the pressure sensor 130 protrudes and is installed on the clamping side of the fastener 145 provided on one side of the pair of bands 144 and 144. The band 144 having the 145 has a structure (not shown in detail) in which a flexible printed circuit (FPC) substrate is covered with a flexible plastic so as to supply a detection signal by the pressure sensor 130.

② Operation

In the wristwatch 146 having the pulse wave detecting unit incorporated therein, as shown in FIGS. 42A and 42B, the elastic rubber 131 provided at the fastener 145 is located near the artery 143 of the finger node. To be positioned, the wrist watch 146 is wound around the subject's left wrist 147, so that it is possible to always detect a pulse wave. This winding is no different from the normal state of use of the watch.

When the rubber 131 is pressed near the artery 143 of the finger joint of the subject, the point P _a is generated on the hemispherical surface of the rubber 131 due to the blood flow fluctuation (ie, pulse wave) of the artery. Vibration occurs. This vibration propagates in the elastic rubber 131 at the point P _a to the detection positions Q ₁ to Q ₄ , becomes a pressure wave in the hollow chambers 134-1 to 134-4, and the pressure reducing element ( S ₁ to S ₄ are detected as voltages V ₁ to V ₄ .

On the numerical side to which the pulse wave detector is connected, various analysis processes are performed after converting the detected voltage into a digital value. However, when the pulse wave detector is used only for the purpose of detecting the pulse wave waveform, the voltage (V ₁ to V ₄ ) is used. It is not necessary to convert all of to a digital value, and all of them may be converted to any one (or more), such as the largest one.

<Modification example of the structure>

① In this description, equations b to f used to find the coordinate values (x _a , y _a ) of the point P ' _a indicate that the rubber 131 is an ideal hemispherical shape, that is, the sphere is centered. It assumes the shape obtained when cut | disconnected by the surface to include. However, in the case of taking into consideration the feeling of the operator, the subject, or the feeling of wearing the device in which the pressure sensor 130 is installed, the shape of the elastic rubber 131 is more convex than that of the hemispherical shape as shown in Fig. 43A. It is preferable. In addition, even in industrial considerations, it is difficult for the pressure sensor 130 to satisfy an ideal hemispherical shape and be manufactured. Rather, as shown in FIG. 43A or 43B (although extreme examples are shown in these drawings), Many are produced shifting from the center of a sphere. Even in such a case, if the deviation amount is within the allowable range in the measurement accuracy, the equation f is used as an approximation equation, and the coordinate values (x _a , y _a ) can be obtained.

This approximation is then described. Now, a case is considered in which the shape of the elastic rubber 131 is a pseudo-spherical body that is cut off by? Z from the center of the ideal sphere. In the above case, the coordinates (x, y, z) of the detection positions Q ₁ to Q ₄ by the pressure-sensitive elements S ₁ to S ₄ represent the radius of the elastic rubber 131 as r, the center to the origin 0, 0, 0), respectively

Q ₁ (a, 0, Δz)

Q ₂ (0, a, Δz)

Q ₃ (-a, 0, Δz)

Q ₄ (0, -a, Δz).

Therefore, the square of each distance between the point P _a and the detection positions Q ₁ to Q ₄ can be obtained by the following equation (d), respectively, as shown in the following equation.

However, in these equations,

It is.

Also in the above case, since the vibration generated at the point P _a is attenuated in proportion to the square of the propagation distance of the elastic rubber 131, it is detected by each sensor. Value of the voltage (V ₁ to V ₄₎ is a distance between the detection position of the sensor corresponding to a cross point (P _a), it is in inverse proportion to the square. That is, since the squares of the distances in the equation (g) and the detection voltages V ₁ to V ₄ are equal to each other, the values of the x and y coordinates of the point P _a (x _a , y _a) ) Becomes

In equation (i), (Δz) ² can be ignored if (Δz) is sufficiently small with respect to the z axis direction. In addition, as can be seen from equation (i), for (z _a .Δz), the distance of the sensor at the origin can be ignored by making it as large as possible within the range of the radius r. By this, equation (i) is substantially equal to equation (f).

(2) In order to find the coordinate values (x _a , y _a ) of the point P ' _a , the voltage V ₁ to V ₄ of each detection signal was obtained by substituting the equation (g), but may be obtained by the following method. .

That is, a constant vibration is experimentally generated on the exposed surface of the elastic rubber 131, and the relationship between the vibration-coordinate and the ratio of the voltages V ₁ to V ₄ is measured in advance, and a table showing the relationship is prepared. . And in fact, in order to obtain the coordinate values x _a , y _a of the point P ' _a , it is possible to read the coordinates corresponding to the ratio of the voltages V ₁ to V ₄ from this table.

Thus, the elastic rubber 131 does not need to have a hemispherical surface shape, but may be a convex shape so as to be pressed against the surface to be measured.

<< second form >>

Next, structural examples other than the pressure sensor will be described. FIG. 44A is a schematic plan view for explaining the configuration of this example, and FIG. 44B is a sectional view of the substantial part of the x-axis direction in FIG. 44A. In these drawings, the same reference numerals are attached to the same parts as in FIG. 35 or 36, and the description thereof is omitted.

As shown in these figures, the pressure sensor 130 is provided with a hollow chamber 134-1 which is opened at the detection position Q ₁ , and also has a hollow chamber that opens to the side wall of the hollow chamber 134-1. 148-1 extends in the center direction of the plane L and is connected to the semiconductor substrate 132. Similarly, the hollow chambers 134-2 to 134-4 are provided at the detection positions Q ₁ to Q ₄ , respectively, and the hollow tubes 148-2 and 148-4 are positioned in the center direction of the plane L. FIG. Each is extended. Pressure reduction elements S ₁ to S ₄ are provided in the semiconductor substrate 132, respectively, and are connected to the hollow tubes 148-1 and 148-4 extending in the four directions, respectively.

In this case, the hollow chambers 134-1 to 134-4 and the hollow tubes 148-1 to 148-4 are preferably different from the semiconductor substrate 132, for example, hard plastic or metal. It is better to form from the rigid body 149 of the back. Since this method can form the pressure-sensitive elements S ₁ to S ₄ intensively on the semiconductor substrate 132 without considering the detection positions Q ₁ to Q ₄ , the number of pressure-reduced elements in the same area can be obtained. There is an advantage that can increase, the cost by that much.

Moreover, also in this structure, you may make it the structure which filled the hollow chamber 134-1-134-4 and the hollow tube 148-1-148-4 with the liquid or liquid substance with low thermal expansion coefficient.

As the pressure sensor 130, a configuration in which a well-known strain gauge is directly attached to the detection positions Q ₁ to Q ₄ of the bottom surface L, and the vibration at the position is detected as deformation is also possible. Deformation due to micro deformation when pressing 131) appears as a direct output. Therefore, as shown in FIG. 36, the structure which detects as an acoustic wave (pressure wave) through the adhesive layer 133 and the hollow chamber 134-1 is preferable. In this way, the micro displacement of the elastic rubber 131 can be prevented from being directly applied to the pressure-sensitive elements S ₁ to S ₄ , and the detection accuracy can be further improved.

In addition, although the number of pressure reduction elements is four in the above-mentioned example, three may be sufficient as mentioned above. Importantly, the bottom surface of the hemispherical surface may be sufficient as each detection position of a pressure reduction element so that the distance of each detection position of a pressure reduction element and the point on the hemispherical surface of the elastic rubber 131 can be specified.

<< third form >>

As the pressure sensor 130 according to the two examples described above, the elastic waves due to the vibration at the point P _a are not only toward the detection positions Q ₁ to Q ₄ but also toward all directions of the elastic rubber 131. Spread evenly. Therefore, the point (P _a) tends to each value of the pressure generated in the detection position (Q ₁ to Q ₄₎ with respect to the magnitude of the vibration becomes smaller, the voltage (V ₁ to V ₄₎ generated in Fig become small according to this There is this. Therefore, this example has the disadvantage that the S / N ratio is likely to deteriorate. Thus, an example in which the S / N ratio is improved in the present embodiment and the next embodiment will be described.

When the present inventor coats the member 150 (eg, hard plastic or metal) having a higher modulus than the elastic rubber 131 on the hemispherical surface of the elastic rubber 131, as shown in FIG. It has been experimentally confirmed that the output voltages V ₁ to V ₄ by S ₁ to S ₄ become larger as compared with the absence of coating of the member 150. This is because the surface acoustic waves propagating along the surface of the hemispherical surface become difficult to propagate due to the presence of the member 150 and are directed toward the center direction of the elastic rubber 131, and accordingly, the respective detection positions Q ₁ to Q ₄ . It is thought that it contributes to the pressure increase in, and the output voltage of a pressure reduction element is made larger. In other words, it is considered that the transfer function indicating the propagation of the acoustic wave from the hemisphere to the detection position is improved.

In addition, in this example, since the elastic rubber 131 is not in direct contact with the operator or the subject by the coating of the member 150, there is an advantage that the deterioration of the elastic rubber 131 due to sebum is prevented.

<< fourth form >>

As shown in FIG. 46, you may be set as the structure which discretely installs many small pieces 151 of the member 150 on the hemispherical surface of the elastic rubber 131. As shown in FIG. The small piece 151 may be embedded or adhered to the hemisphere (the figure shows the bonded example).

At this time, in the transfer function of the elastic wave described above, since the direction toward the detection position in the small piece 151 is improved than that toward the detection position on the exposed surface of the elastic rubber 131, the vibration point P on the hemispherical surface P _a ) is optionally limited (prone) to the installation site of the small piece 151. Because of this point (P _a), the coordinate value, but a problem that the value of a discrete projection of the installation place of the bit 151 on the lower surface (L), the output voltage (V ₁ of the pressure-sensitive element (S ₁ to S ₄₎ of the To V ₄ ), it is effective when the resolution is relatively rough as in the detection of pulse waves. In addition, this problem can be solved by efficiently installing a large number of small pieces (151).

<< modification >>

( ₁ ) The difference in output characteristics of the pressure-sensitive elements S ₁ to S ₄ can be ignored by the following method. The method might use the technique of calculating coordinate values of a point (P _'a) of the three pressure-sensitive elements described in the "(2) The principle of pulse wave detection and coordinate detection."

First, three of four pressure reduction elements are selected, and the coordinate values (x _a , y _a ) are calculated only by these pressure reduction elements. Next, a combination of other decompression elements is selected to calculate coordinate values (x _a , y _a ) similarly. Since there are about four combinations (= ₄ C ₂ ) for selecting three among the other four, the coordinate values (x _a , y _a ) are similarly calculated by the other two combinations. The coordinate values x _a , y _a calculated independently by these four combinations coincide with each other if the output characteristics of the pressure-sensitive elements S ₁ to S ₄ are all the same. For example, if it doesn't match. It can be said that the output characteristics are different, and if the detected voltage is corrected from the calculated coordinates to match the calculated coordinates, the difference in output characteristics according to the individual difference of the decompression element can be mutually ignored, and a more accurate coordinate value can be obtained. Can be.

(2) In the above description, although the pulse wave of the artery of the finger joint is detected as the wristwatch attachment device, it goes without saying that it is not necessary to be obsessed with this. That is, it is good also as a structure which detects the pulse wave of another artery, without taking the structure of a wristwatch. An example of such a configuration is shown in FIG. 47.

In this example, the pressure sensor 130 is pressed against the subject's neck artery by, for example, a tape 152, and the main body BD for analyzing the pulse wave through the cable CB is detected by the pressure sensor 130 through the cable CB. ) Is configured to supply.

Section 2 Single-stroke

(1) Meaning of single stroke

One stroke is the amount of blood flowing out of one stroke from the heart, which corresponds to the area of the blood flow waveform coming out of the heart.

(2) Measurement technique of single stroke

The single ejection amount is calculated based on the so-called systolic area method. According to this systolic area method, the area S of the pulse wave waveform of the part corresponding to the systolic period of the heart among the measured pulse wave waveforms is calculated. If this is explained as the pulse wave waveform of FIG. 48, let the area S _sv be the area of the area | region from the granular part of a pulse wave to a notch (namely, the hatched part in the figure). And when the predetermined constant is set to K _sv , the ejection amount SV once can be calculated by the following equation.

1 stroke amount SV [m1] = area (S _sv ) [mmHg · s] × integer (K _av )

In addition, what kind of form of one stroke amount is measured is described next like a pulse wave measurement form.

Section 3 Measurement form of pulse wave and single stroke

This section describes various forms for pulse wave detection and single stroke measurement.

(1) first form

As shown in FIG. 49, the pulse wave detection part 160 and the single ejection amount measuring part 161 are means provided in order to adjust the arterial waveform and the one-time extraction amount of a finger joint in a patient. That is, in the figure, the pulse wave detection unit 160 detects the arterial waveform of the finger node through a sensor mounted on the wrist of the subject, and detects the blood pressure of the subject through a cap mounted on the upper arm of the subject. Then, the arterial waveform of the finger node is corrected as blood pressure, and the resultant arterial waveform of the finger node is output as an electric signal (analog signal). On the other hand, the one-time ejection amount measuring unit 161 measures the one-time ejection amount in the subject and outputs an electric signal indicating the result.

(2) second form

In addition to the configuration using two caps shown in FIG. 49, the pulse wave detection unit 160 and the single ejection amount measurement unit 161 may be configured to share one cap S1 as shown in FIG. 50. .

By the way, the measurement place of a pulse wave and a single stroke amount is not limited to the place shown in FIG. 49 or FIG. 50, and may be any site | part of a subject's body. That is, in the above description, although the cap was attached to the upper arm of the test subject, the shape without the cap is considered to be good considering the convenience of the test subject. Thus, the thoughts are directed to the third to fourth aspects described below.

(3) third form

As another form, the form which measures both a fingertip artery waveform and a single stroke amount in a wrist is considered. As an example of this kind of structure, as shown in FIG. 51, the sensor 165 which consists of a sensor for blood pressure measurement and a sensor for single stroke amount measurement is attached to the belt 167 of the watch 166, and the sensor ( A configuration in which the component part 168 of the device other than 165 is incorporated in the body part of the watch 166 is obtained. And, as shown in the figure, the sensor 165, for example, to use the above-described pressure pulse wave sensor.

(4) fourth form

As another form, a form in which a pulse wave and a single ejection amount is measured by a finger is also conceivable, and FIG. 52 shows an example of the configuration of the device according to this form. As shown in the figure, a sensor 169 comprising a sensor for blood pressure measurement and a sensor for single stroke amount measurement is provided at the bottom of a finger (forefinger in the example of the figure), and the sensor 169 A component 170 of the device other than this is incorporated in the wristwatch 171 and connected to the sensor 169 through the lead wires 172 and 172.

In addition, by combining two measurement forms of the third and fourth forms, the pulse amount is measured by the finger at the same time as the amount of ejection is measured at the wrist, and the amount of ejection is measured by the finger at the same time. It becomes possible to realize the form of measuring the arterial wave of the node.

By having a configuration without a cap as in the third or fourth embodiment described above, the subject does not have to walk his arms, and the burden on the subject is reduced in the measurement.

(5) fifth form

A configuration shown in Fig. 53 can be considered as the form using only the cap. As shown in the figure, the sensor 173 comprising the sensor for blood pressure measurement and the sensor for single ejection volume measurement, and the component part 174 of the device other than the sensor 173 are placed on the upper side of the subject by the cap. It is fixed to the arm and has a simple configuration even in comparison with FIG. 49.

(6) 6th form

This form is slightly different from the said 5 forms. In other words, even when a single stroke amount is required, the single stroke amount can be estimated from the arterial waveform of the finger joint (see "Chapter 4, Section 1, Section 1" below for details). In such a case, the single ejection amount measuring unit 161 as shown in FIG. 49 becomes unnecessary, and the form of the measurement is as shown in FIG.

(7) Modification

(1) In performing extraction of the arterial wave of the knuckle and measurement of the amount of ejection, it is conceivable to predict by a chime before a predetermined time of the measurement time. In this case, since the patient only needs to attach the cap to the measurement when the forecast rings, the patient can take off the cap and the like freely.

(2) The patient may have a portable paging receiver and the portable paging receiver may be called when the measurement time is near.

Chapter 3 Extraction of Pulse Wave Feature Information

In analyzing the pulse wave waveform entered by the pulse wave detector described in Chapter 2, it is necessary to extract information indicating the characteristics of the pulse wave waveform. These feature information extraction techniques are common to the devices described later. Thus, in this chapter, the contents of these feature information will be described, and the realization means for extracting feature information from the pulse wave waveform will be described.

Section 1 Waveform Parameters

Section 1 Definition of Waveform Parameters

The waveform of one pulse of pulse wave has the shape as shown in FIG. 55, and the vertical axis | shaft in this figure is a blood pressure value, and the horizontal axis is time. What is explained below is defined as a waveform parameter which specifies the shape of such a pulse wave waveform.

① Time (t ₆ ) until pulse wave corresponding to next ejection starts after pulse wave about once ejection won (hereinafter this granulation time is called pulse wave start time)

② Blood pressure values y ₁ to y _{5 of the} maximum points P1, the minimum points P2, the maximum points P3, the minimum points P4 and the maximum points P5 appearing sequentially in the pulse wave.

E) the elapsed time (t ₁ to t ₅ ) from the pulse wave start time until the respective points P1 to P5 appear;

Section 2 waveform extraction memory

In order to calculate waveform parameters, information called "peak information" associated with each of these points is extracted with respect to the maximum or minimum points. The waveform extraction storage section described below extracts this peak information from the pulse wave waveform. The details of the peak information are related to the configuration and operation of the waveform extraction storage section, and therefore, the details of the peak information are referred to at the time when the configuration of the circuit is explained.

(1) Configuration of the circuit

Hereinafter, although the structure of the waveform extraction storage part 180 is demonstrated with reference to FIG. 56, it is assumed here that the waveform extraction storage part 180 is controlled as the microcomputer 181. FIG.

In this figure, reference numeral 182 denotes an A / D converter, which converts the pulse wave signals output from the various pulse wave detectors described in Chapter 2 into digital signals corresponding to a sampling clock Φ of a predetermined period.

183 is a low pass filter and performs processing for removing components of a predetermined cutoff frequency or more for digital signals sequentially output from the A / D converter 182, and outputs the results as waveform values W in sequence.

184 is a waveform memory configured as a RAM, and sequentially stores the waveform value W supplied through the low pass filter 183.

191 is a waveform value address counter, and counts the sampling clock Φ during the period when the waveform extraction instruction START is output from the microcomputer 181, and the waveform value at which the waveform value W is to be recorded. It outputs as the address ADR1. This waveform value address ADR1 is monitored by the microcomputer 181.

192 is a selector, and when the selector signal S1 is not output from the microcomputer 181, the waveform value address ADR1 output from the waveform value address counter 191 is selected and the address input terminal of the waveform memory 184 is selected. To supply. On the other hand, when the select signal S1 is output from the microcomputer 181, the read address ADR4 output from the microcomputer 181 is selected and supplied to the address input terminal of the waveform memory 184.

201 is a differential circuit, which calculates and outputs a time derivative of the waveform value W sequentially output from the low pass filter 183.

202 is a zero cross detection circuit, and outputs a zero cross detection pulse Z when the time derivative of the waveform value W becomes zero because the waveform value W becomes a minimum value. In addition, the zero cross detection circuit 202 is a circuit provided to detect peak points P1, P2, ... from the waveform of the pulse wave illustrated in FIG. 57, and the waveform value W corresponding to these peak points is When input, the zero cross detection pulse Z is output.

203 is a peak address counter, and counts the zero cross detection pulse Z during the period during which the waveform extraction instruction START is output from the microcomputer 181, and outputs the count result as the peak address ADR2.

204 is a moving average calculation circuit, calculates an average value of time derivatives of waveform values W for the past predetermined number output from the integrating circuit 201 up to the present time, and pulse wave until the result reaches the present time. It is output as slope information (SLP) indicating the slope of.

205 is a peak information memory provided for storing the peak information described below. Here, the detail of peak information is demonstrated below. That is, the detail of the content of the peak information shown in FIG. 58 is as follows, The detail of peak information is enumerated below.

① Waveform value address (ADR1)

It is a write address output from the waveform value address counter 191 when the waveform value W output from the low pass filter 183 becomes the maximum value or the minimum value. In other words, it is a write address in the waveform memory 184 of the waveform value W corresponding to the local maximum or local minimum.

② Peak type (B / T)

Information indicating whether the waveform value W recorded at the waveform value address ADR1 is the maximum value T (Top) or the minimum value B (Bottom).

③ Waveform value (W)

It is a waveform value corresponding to the maximum value or the minimum value.

④ stroke information (STRK)

The change in waveform value from the previous peak value to the peak value.

⑤ Slope Information (SLP)

It is an average value of time derivatives of waveform values for a predetermined number of past until the peak value is reached.

(2) circuit operation

The operation of the waveform extraction storage unit 180 will be described below under the control of the microcomputer 181.

(a) Extraction of waveforms and their peak information

When the waveform extraction instruction START is output by the microcomputer 181, the reset of the waveform value address counter 191 and the peak address counter 203 is released.

As a result, the count of the sampling clock ? Is started by the waveform value address counter 191, and the count value is supplied to the waveform memory 184 via the selector 192 as the waveform value address ADR1. The pulse wave signal detected by the human body is input to the A / D converter 182, sequentially converted into a digital signal according to the sampling clock Φ , and sequentially output as the waveform value W through the low pass filter 183. do. The waveform value W output in this manner is sequentially supplied to the waveform memory 184, and is recorded in the storage area designated by the waveform value address ADR1 at that time. By the above operation, a series of waveform values W corresponding to the arterial waveforms of the finger nodes illustrated in FIG. 57 are stored in the waveform memory 184.

On the other hand, in parallel with the above operation, detection of peak information Z and writing to the peak information memory 205 are performed as described below.

First, the time derivative of the waveform value W output from the low pass filter 183 is calculated by the differential circuit 201, and this time derivative is applied to the zero cross detection circuit 202 and the moving average calculation circuit 204. Is entered. In this way, the moving average calculation circuit 204 calculates an average value (ie, a moving average value) of a predetermined number of time derivatives in the past each time the time differential value of the waveform value W is supplied, and inclines the calculation result to the slope information (SLP). Output as Here, when the waveform value W is in the minimum state during the rising or ending the rising, the positive value is output as the slope information SLP, and when the waveform value W reaches the minimum value during the falling or falling, the gradient information ( A negative value is output as SLP).

For example, when the waveform value W corresponding to the maximum point P1 shown in FIG. 57 is output from the low pass filter 183, 0 is output from the differential circuit 201 as a time derivative, and zero cross is obtained. The zero cross detection pulse Z is output from the detection circuit 202.

As a result, the microcomputer 181 determines, by the microcomputer 181, the waveform address ADR1 that is the counter value of the waveform value address counter 191, the waveform value W, and the peak address ADR2 that is the count value of the peak address counter. In the case of ADR2 = 0) and the slope information (SLP). In addition, the count value ADR2 of the peak address counter 203 is set to 1 by the zero cross detection pulse Z being output.

On the other hand, the microcomputer 181 creates the peak type B / T based on the sign of the entered slope information SLP. When the waveform value W of the maximum value P1 is output as in the above case, since the positive slope information is output at that time, the microcomputer 181 changes the value of the peak information B / T to the maximum value. We assume correspondence. The microcomputer 181 designates the peak address ADR2 (ADR2 = 0 in this case), which is accepted by the peak address counter 203, as the write address ADR3 as it is, and the waveform value W and the waveform value W ), The waveform address ADR1, the peak type B / T, and the slope information SLP are recorded in the peak information memory 205 as the first peak information. In the case of recording the first peak information, since there is no previous peak information, the stroke information STRK is not created and recorded.

Thereafter, when the waveform value W corresponding to the minimum point P2 shown in FIG. 57 is output from the low pass filter 183, the zero cross detection pulse 2 is output as described above, and the write address ( The ADR1, the waveform value W, the peak address ADR2 (= 1), and the slope information SLP <0 are entered by the microcomputer 181.

Thus, the peak type (B / T, in this case "B") is determined by the microcomputer 181 on the basis of the inclination information SLP as described above. The microcomputer 181 supplies an address smaller than the peak address ADR2 by one from the peak information memory 205 as the read address ADR3, and reads the waveform value W recorded at the first time. Then, the microcomputer 181 calculates the difference between the waveform value W currently taken out of the low pass filter 183 and the first waveform value W read out from the peak information memory 205, and the stroke information. (STRK) is obtained. The peak information B / T and stroke information STRK obtained in this way are different from each other, that is, the peak information as the second peak information simultaneously with the waveform value address ADR1, the waveform value W, and the slope information SLP. The memory 205 writes to the storage area corresponding to the peak address (ADR3 = 1). The same operation is then performed when the peak points P3, P4, ... are detected.

When the predetermined time elapses, the microcomputer 181 stops the output of the waveform extraction instruction START, and the extraction of the waveform value W and the peak information ends.

(b) Division process of pulse wave waveform

Of the various information stored in the peak information memory 205, the microcomputer 181 performs a process for specifying the information corresponding to the waveform of one stroke for extracting the waveform parameter.

First, in the peak information memory 205, the slope information SLP and the stroke information STRK corresponding to each peak point P1, P2, ... are sequentially read. Subsequently, stroke information corresponding to a positive slope (that is, the corresponding slope information SLP becomes a positive value) is selected from the respective stroke information STRK, and among the stroke information, the upper predetermined value having the largest value is selected. The number is selected. Then, if the one corresponding to the median value is selected from the selected stroke information STRK, the stroke of the standing part of the pulse wave for one stroke for extracting the waveform parameter (for example, the standing part indicated by the symbol STRKM in Fig. 57) is extracted. Information is obtained. Then, the peak address one earlier than the peak address of the stroke information (that is, the peak address of the start point P6 of the pulse wave for extracting the waveform parameter) is obtained.

(c) Extraction of Waveform Parameters

The microcomputer 181 calculates each waveform parameter with reference to each peak information corresponding to said one stroke pulse wave stored in the peak information memory 205. This process is obtained as follows, for example.

① blood pressure value (y ₁ to y ₅ )

The waveform values corresponding to the peak points P7 to P11 are y ₁ to y ₅ , respectively.

② time (t ₁ )

The waveform address corresponding to the peak point P ₆ is subtracted from the waveform address corresponding to the peak point P ₇ , and the result is multiplied by the period of the sampling clock Φ to calculate t ₁ .

③ time (t ₂ to t ₅ )

As with the t _1, it is calculated on the basis of the difference between the waveform address corresponding to each peak point. Each waveform parameter obtained as described above is stored in a buffer memory inside the microcomputer 181.

(3) Modification

The information stored in the waveform memory 184 and the peak information memory 205 can be applied in various ways other than the extraction of waveform parameters.

In this case, after the above-described circuit operation of (a) and (b) is made, the microcomputer 181 takes out this information and performs various kinds of analysis and diagnosis.

(2) Various examples of the waveform parameters of the pulse wave other than the above are conceivable. Therefore, when this circuit is used for the diagnosis of a human body, it may be modified so as to obtain an optimal waveform parameter in the diagnosis.

Section 2 pulse wave spectrum

Meaning of pulse wave spectrum

It has been found that the frequency spectrum obtained by frequency analysis of the pulse wave waveform can be information indicating the characteristics of the original pulse wave waveform. More specifically, the amplitude and phase of the frequency spectrum are useful as characteristic information of pulse waves.

Section 2 frequency analyzer

Typical frequency analysis methods of waveforms include FFT (Fast Fourier Transform) and the like. First, it is conceivable to perform frequency analysis of pulse waves using this kind of frequency analysis technique. However, the individual one wave and one wave constituting the waveform of the pulse wave are not the same shape but change every time, and the wavelength of each wave is not constant. Thus, in the case of using the FFT, a method of performing the FFT is regarded as a waveform having a very long period of time as the pulse wave having such chaotic behavior is used.

By the way, when the FFT is used, the spectrum of the pulse wave is obtained in detail, but the calculation amount tends to be large. Thus, the present inventor has developed a frequency analysis section to be described below for the purpose of quickly obtaining the spectrum of pulse waves generated every time. This frequency analyzer is a spectrum detection circuit for frequency analysis of the pulse wave waveform and extracts the amplitude and phase of the obtained spectrum. The frequency analyzer is operated in conjunction with the above-described waveform extraction storage unit 180 under the control of the microcomputer 181 described above. Detect the spectrum of pulse waves at high speed. Thereby, the waveform parameter which shows the characteristic of the 1 wave 1 wave which comprises a pulse wave can be calculated continuously.

(1) circuit configuration

59 is a block diagram showing details of the frequency analyzer 210. The frequency analyzer 210 receives the pulse wave waveform value WD in pulse units through the microcomputer 181, and repeatedly reproduces the received waveform wave value WD at high speed, and performs frequency analysis for each stroke. To calculate the spectrum constituting the pulse wave. In addition, the frequency analyzer 210 calculates the fundamental spectrum of the first pulse wave, followed by the second harmonic spectrum, and each spectrum constituting the pulse wave in a situation such as time division.

When the microcomputer 181 outputs the first waveform value WD of the pulse wave for one night to the frequency analyzer 210, the number of waveform values WD included in the synchronization signal SYNC and its extraction N ), And at the same time, the select signal S2 is changed. In addition, while the microcomputer 181 outputs the waveform value WD for one night, the microcomputer 181 sequentially outputs the write address ADR5 varying from 0 to N-1 in synchronization with the handing of each waveform value WD. .

The buffer memories 211 and 212 are thus installed in order to store the waveform value WD output from the microcomputer 181.

The distributor 213 outputs the waveform value WD of the pulse wave supplied through the microcomputer 181 toward the side designated by the select signal S2 in the buffer memory 211 or 212.

The selector 214 selects the buffer memory designated by the select signal S2 among the buffer memory 211 or the buffer memory 212, selects the buffer memory, and selects the waveform value WH read from the buffer memory. Output to the fast playback unit 220 to be described later.

The selectors 215 and 216 select the write address ADR5 or the read address ADR6 (described later) generated by the fast reproducing section 220 in accordance with the select signal S2, respectively, to the buffer memories 211 and 212, respectively. Supply.

The switch 213 and the selectors 214 to 216 described above are controlled to be switched based on the select signal S2, so that data is read from the buffer memory 212 while data is being written to the buffer memory 211. The data is read from the buffer memory 211 and supplied to the fast playback unit 220 while data is being written to the buffer memory 212.

The fast reproducing unit 220 is a means for reading the waveform value corresponding to each stroke in the buffer memory 211 and the buffer memory 212, and the read address ADR6 is 0 to N-1 (where N must be read). The number of waveforms to be changed). In addition, in detail, the high speed reproducing section 220 generates the read address ADR6 during the period in which each waveform value WD corresponding to a certain stroke is being recorded in one buffer memory, and the preceding stroke is ejected. The entire waveform value WD corresponding to is repeatedly read out from the other buffer memory a plurality of times. At that time, the generation of the read address ADR6 is controlled so that all waveform values WD corresponding to one stroke are always read within a certain period of time. The period for reading all waveform values corresponding to one stroke is changed corresponding to the order of the spectrum to be detected, and the second harmonic is detected when the fundamental spectrum is detected, 2T for the spectrum, 3T for the third harmonic spectrum,... Is replaced by. In addition, the fast reproducing unit 220 has a built-in interpolator, and the buffer memory 211 or 217 interpolates the waveform value WH read from the memory 212, and the predetermined sampling frequencies m / T and m are Outputted as a waveform value of a predetermined integer).

The sine wave generator 221 is a waveform generator of a variable frequency, and under the control of the microcomputer 181, the sine wave generator 221 corresponds to the order of the spectrum to be detected, and the sine waves of T, 2T, 3T, 4T, 5T, and 6T are sequentially Output

The band pass filter 222 is a band pass filter whose center frequency of the pass band is a predetermined value 1 / T.

The spectrum detector 223 detects the amplitude H ₁ to H ₆ of each spectrum of the pulse wave based on the output signal level of the band pass filter 222, and simultaneously outputs a phase and a sine wave generator of the output signal of the band pass filter 222. The phases θ ₁ to θ ₆ of each spectrum are detected based on the difference in the phases of the sine waves output by 221.

(2) circuit operation

As described above, the frequency analyzer 210 detects the spectrum of the pulse wave at high speed in conjunction with the waveform extraction storage unit 180. Therefore, the operation of the microcomputer 181 and the waveform extraction storage unit 180 will be described below.

(a) Waveform Segmentation

As described above in the operation section of the waveform extraction storage unit 180, when the waveform extraction instruction START is output by the microcomputer 181, the waveform and its peak information Z are extracted, and the waveform extraction storage unit It is stored in the internal waveform memory 184 and the peak information memory 205, respectively.

When the stroke information (STRK) in the peak information (Z) is equal to or greater than a predetermined value at the time when the stroke information is created corresponding to the minimum point P2, specifically, the standing part of the pulse wave (for example, in FIG. 57). When the stroke is large enough to be regarded as equivalent to the STRKM, the microcomputer 181 also selects the waveform address (i.e., the point P6 of the STRKM in FIG. 57) which is the starting point of the stroke. 205, and writes to the shift register built in the microcomputer 181. Then, the same operation is performed even when the peak points P3, P4, ... are detected.

(b) Waveform Crossing

In parallel with the above operation, the microcomputer 181 sequentially reads the waveform values from the waveform memory 184 in the waveform extraction storage unit 180 and passes them to the frequency analyzer 210 as waveform data WD. On the other hand, as shown in Fig. 61, the select signal S1 is switched in synchronization with the clock Φ , and the waveform memory 184 switches the mode of the write mode / read mode in synchronization with this.

By the way, in FIG. 60, when the waveform value of the pulse wave Wn corresponding to a certain stroke is input into the waveform memory 184, first, when the first minimum value of the pulse wave corresponding to the stroke is inputted, A zero cross detection pulse Z is generated, and the waveform value address ADR1 = As is recorded in the peak information memory 205 (see Fig. 61). Thereafter, when the maximum value (address A ₁ ) is input into the waveform extraction storage unit 180, a zero cross detection pulse Z is generated again (see FIG. 61), and the maximum value and the immediately preceding minimum value (address As) are generated. When the stroke between them is equal to or greater than the predetermined value, the minimum address As is recorded in the shift resist A ₅ in the microcomputer 181. The waveform address recorded in this way is then outputted from the shift register with a delay of two strokes, and enters the microcomputer 181 as the start address of the waveform value WD for one stroke to be passed to the frequency analyzer 210. . That is, in Fig. 60, when the maximum address Wn-1 of the pulse wave Wn corresponding to a certain ejection is recorded in the shift register, the pulse wave Wn-2 before the two ejections previously recorded in the shift register is recorded. The start address (the first minimum address) is output from the shift register and detected by the microcomputer 181.

At this point, the microcomputer 181 refers to the contents of the shift register and reaches the first minimum waveform address of the pulse wave Wn-2 to the next minimum waveform address of the pulse wave Wn-1. The number N of waveform values included in the pulse wave Wn-1 corresponding to the difference, i.e., one stroke, is obtained and output to the frequency analyzer 210 simultaneously with the synchronization signal SYNC. In addition, the selector signal S2 is switched in synchronization with the synchronizing signal SYNC, and the internal connection state of the divider 213 and the selectors 214 and 216 becomes, for example, a state indicated by a solid line in FIG. 59.

Then, the microcomputer 181 sequentially increases the read address ADR4 at the first waveform address of the pulse wave W-2 and supplies it to the waveform memory 184 through the selector 192. Here, the read address ADR4 changes faster than the write address ADR1 (for example, at twice the speed). This is because all waveforms corresponding to the pulse wave Wn-2 before the pulse wave Wn-1 before the maximum value of the pulse wave Wn + 1 of the pulsation of the pulse wave Wn difference are input to the waveform extraction storage unit 180. This is to ensure that the value is read. In this manner, the waveform value WD of the pulse wave Wn-2 before the two extractions is read out from the waveform memory 184 by the microcomputer 181 in parallel with the storage of the pulse wave Wn in the waveform memory 184. Guided to the analyzer 210, and sequentially supplied to the buffer memory 211 through the distributor 213. In synchronization with the waveform value WD being sequentially supplied to the buffer memory 211 as described above, the write address ADR 5 is sequentially increased from 0 to N-1, and the write address ADR 5 is selected by the selector ( 215 is supplied to the buffer memory 211. As a result, each waveform value WD corresponding to the pulse wave Wn-2 is stored in each memory area of the address of the buffer memory 211 of 0 to N-1.

(c) fast playback

In parallel with the above operation, the read address 6: ADR is output by the fast reproducing unit 220 and supplied to the buffer memory 211 through the selector 216. As a result, each waveform value WD corresponding to the pulse wave Wn-3 before the one pulse of the pulse wave Wn-2 is read out from the buffer memory 211, and the high-speed reproducing unit 220 is provided through the selector 214. Enter

Here, each waveform value WD corresponding to the pulse wave Wn-3 in the buffer memory 211 has a higher speed than that of each waveform value corresponding to the pulse wave Wn-2 in the buffer memory 211. It is read repeatedly over times. At that time, the increase rate of the read address 6: ADR is controlled so that all of the waveform values WD corresponding to the pulse wave Wn-3 are read within a predetermined period T. That is, the fast reproducing unit 220 increases the highway read address 6: ADR when the number of waveform values WD read from the buffer memory 211 is a large value N1 as shown in FIG. On the contrary, in the case of the small value N2 as shown in FIG. 63, the data is read at a low speed, the address 6: ADR is increased, and the read address 6: ADR is 0 to Nn within a predetermined period T. The interval between -1 or 0 to N2-1 is changed. The waveform values WD sequentially read as described above are interpolated in the fast reproducing section 220, and are supplied to the band pass filter 222 as waveform values having a constant sampling frequency m / T. .

(d) spectral detection

The band pass filter 222 selects and passes a signal having a frequency of 1 / T among time series data based on the received waveform value and is supplied to the spectrum detector 223. Meanwhile, as shown in FIG. 64, the sine wave generator 221 generates a sine wave having a period T and supplies the sine wave to the spectrum detector 223. The spectrum detector 223 detects the output signal level of the band pass filter 222 over aberrations, outputs a representative value thereof as the amplitude H of the fundamental wave spectrum of the pulse wave Wn-3, and simultaneously outputs a band pass filter ( The phase difference between the phase of the output signal of 222 and the phase of the sine wave output from the sine wave generator 221 is detected over aberration, and the representative value is output as the phase θ ₁ of the fundamental wave spectrum of the pulse wave Wn-3. do. Each representative value calculates, for example, a moving average value of an output signal level and a phase difference corresponding to each wave immediately before outputting the fundamental wave spectrum.

Next, the fast reproducing section 220 sets the rate of increase of the read address 6: ADR so as to read all the waveform values of the pulse wave Wn-3 within a predetermined period 2T in the case of detecting the fundamental wave spectrum. 2, the waveform value WH corresponding to the pulse wave Wn-3 is repeatedly read and supplied to the band pass filter 222 (see FIG. 64). In addition, a signal having a frequency of 1 / T, that is, a signal corresponding to the second harmonic of the pulse wave Wn-3, of the time series data having the waveform value WH passes through the band pass filter 222, and the spectrum detector 223 Is supplied. As a result, the spectrum detector 223 detects and outputs the amplitude H ₂ of the second harmonic spectrum of the pulse wave Wn-3. On the other hand, the sinusoidal wave generator 221 generates a sinusoidal wave having a period of 2T and supplies it to the spectrum detector 223 (see Fig. 64). As a result, the spectrum detector 223 outputs the phase θ ₂ of the fundamental wave spectrum of the pulse wave Wn-3.

Subsequently, the increase speed of the read address 6: ADR is sequentially switched to 1/3, 1/4, 1/5, and 1/6 in the case of the fundamental wave spectrum, and the sine wave generator 221 is adapted accordingly. The period of the generated sine wave is sequentially switched to 3T, 4T, 5T, and 6T, and the amplitude (H ₃ to H ₆ ) and phase (θ ₃ to θ) of the harmonic spectrum from 3rd to 6th order by the same operation as described above. ₆ ) is output from the spectrum detector 223. Each spectrum of the obtained pulse wave Wn-3 enters the microcomputer 181. Then, the microcomputer 181 uses the number N of waveform values WD corresponding to the pulse wave Wn-3 and the period τ of the clock Ψ, so that the frequency f of the fundamental wave is f = 1 / ( Nτ) is calculated and output simultaneously with the spectrum.

Thereafter, when the pulse wave Wn + 1 after one extraction rises from the pulse wave Wn, and the first maximum value is input into the waveform extraction storage unit 180, the synchronization signal SYNC is generated by the microcomputer 181. At the same time, the number N of waveform values WD included in the pulse wave Wn-2 is output. In addition, the select signal S2 is inverted, and the internal connection state of the divider 213 and the selectors 214 to 216 is shown along the dotted line in FIG. 59. In parallel with the storage of the pulse wave Wn + 1 in the waveform memory 184, the waveform value WD of the pulse wave Wn-1 before its two extractions is made to the waveform memory 184 by the microcomputer 181. It is read and guided to the frequency analyzer 210 and sequentially supplied to the buffer memory 212 through the distributor 213.

In parallel with the above operation, each waveform value WD corresponding to the pulse wave Wn-2 before the one pulse of the pulse wave Wn-1 is read from the buffer memory 211 by the high speed reproducing unit 220, It is interpolated by the fast reproducing section 220 and output as a waveform value WH. The same processing as that of the pulse wave Wn-3 is performed on the waveform value WH corresponding to the pulse wave Wn-2, and the spectrum thereof is obtained.

Subsequently, the above-described processing is performed on each pulse wave which appears in sequence, and the spectrum of each pulse wave is obtained continuously, and output as a parameter corresponding to each extraction.

(3) Modification

( ₁ ) Without detecting both the amplitudes (H ₁ to H ₆ ) and the phases (θ ₁ to θ ₆ ), for example, only the phase (θ ₄ ) in which the change in the body is particularly good may be detected.

(2) In the circuit described above, the waveform parameters corresponding to the respective strokes are output in real time at the time when the waveform parameters can be obtained. However, the output method of the waveform parameter is not limited to this, and for example, the microcomputer 181 may calculate and output the addition average value (ie, the moving average value of the waveform parameter) of the waveform parameter for the predetermined stroke number. .

Chapter 4 Pulse Waveform Analysis

Section 1 Calculation of Circulation Dynamic Parameters

As described above, the circulation dynamics parameter may be cited as a factor for determining the behavior of the circulatory system of the human body. Therefore, the following describes various methods for deriving cyclic dynamic parameters by analyzing the pulse wave waveform.

Clause 1 calculation method based on electric model (four element concentrated constant model)

The present inventors found a method of calculating the circulating dynamic parameters by replacing the circulatory system of the human body with an electrical model and obtaining the value of each device constituting the electrical model. Using the electrical model as described above, the cyclic dynamics parameter can be calculated by a simple calculation process.

(1) Overview

First, the present inventors adopted a four element concentrated constant model as the electrical model of the arterial system. Four factor concentrated constant model is in inertia by blood in central part of arterial system, vascular resistance (viscosity resistance) by blood characteristic in arterial system center part among factors which determine the behavior of circulatory system of human body, arterial system center part Attention is paid to the four circulating dynamic parameters of vascular compliance (adhesiveness) and vascular resistance (viscosity resistance) at the end of the arterial line, and these are modeled as electrical circuits. In addition, compliance is the quantity which shows the softening degree of a blood vessel, and is viscoelastic.

FIG. 65 shows a circuit diagram of the four element concentrated constant model, and shows the correspondence relationship between each element constituting the four element concentrated constant model and the above parameters.

Inductance (L): Inertia of blood at the center of arterial system [dyn · s ² / cm ⁵ ]

Capacitance (C): Compliance of blood vessels in the central part of the arterial system [cm ⁵ / dyn]

Electrical resistance (R _c ): vascular resistance due to blood viscosity in the central part of the arterial system [dyn · s / cm ⁵ ]

Electrical resistance (R _p ): blood vessel resistance due to blood viscosity in the central part of the arterial system [dyn · s ² / cm ⁵ ]

I, i _p , i _c flowing through each part in the electric circuit correspond to blood flow [cm ³ / s] flowing through each corresponding part, respectively, and the input voltage e applied to the electric circuit is the pressure [dyn] / cm ² ]. In addition, the terminal voltage v _p of the capacitance C corresponds to the pressure [dyn / cm ² ] in the peripheral part of the arterial system such as the arterial part of the finger joint.

(2) Parameter calculation procedure

(a) Approximate Equation of Response Characteristics of Four Element Concentrated Integer Model

Next, a theoretical explanation regarding the behavior of the four element concentrated constant model shown in FIG. 65 will be described. First, in the four element concentrated constant model shown in the figure, the following differential equation holds.

Here, the current i is

Since it can be represented by, Equation 1 can be expressed as Equation 3 below.

As is well known, the general solution of the quadratic constant differential equation as shown by Equation 3 above is the sum of the special solution satisfying Equation 3 (normal solution) and the transient solution satisfying the following differential equation: Given by

Here, the solution of differential equation 4 is obtained as follows. First, the damped vibration waveform represented by the following equation (5) is assumed as a solution of the differential equation 4.

Substituting Equation 5 into Equation 4, Equation 4 is as follows.

And, when solving Equation 6 with respect to s,

It becomes

In Equation 7,

In the case of, the radical in claim 2 becomes negative, and in the above case, s is represented as follows.

From here,

In Equation 10, Equations 10 and 11 may be expressed as follows.

As above, the value of s is confirmed, and a solution satisfying the differential equation 4 is obtained.

Based on the above, this inventor uses the said Formula (5) as an approximation of the damping vibration component contained in the response waveform of a 4-element lumped constant model.

Next, the pressure waveform of the aortic starting portion is modeled. In general, the pressure waveform of the aortic starting portion is a waveform as shown in FIG. 66. Thus, here, the pressure waveform of the aortic starting portion is approximated by the triangular wave shown in FIG. In Fig. 67, when the amplitude and time of the approximate waveform are E _o , E _m , t _p , and t _p1 , the aortic pressure e at an arbitrary time t is represented by the following equation.

In the interval 0≤ t ≤ t _p1 :

In the interval t _p1 ≤ t ≤ t _p :

As described above, if the pressure wave of the aortic starting portion is modeled by a simple triangular wave, the cyclic dynamics parameter can be calculated by a simple calculation process. In addition, E _o is the lowest blood pressure (dilator blood pressure), E _o + E _m is the highest blood pressure (constrictor blood pressure), t _p is 1 ejection time, t _p1 is the rise in the aortic pressure when the pressure becomes the lowest blood pressure value It's time to

The response waveform (corresponding to the arterial wave of the finger node) when the electric signal e represented by the above expressions (17) and (18) is input to the equivalent circuit of FIG. 65 is approximated as follows.

In the interval 0≤ t≤ t _p1 :

In the interval t _p1 ≤ t≤ t _p :

Here, E _min is the lowest blood pressure value (see FIG. 72 which follows) in the arterial waveform of the finger joint.

The right side third term in the above equation (19) and the right side second term in the above equation (20) are the damping vibration components (corresponding to the above equation (5)), and α and ω in these terms are Given by Equations 15 and 16 above.

In _{addition, B, t p, D m1} , D m2 is an integer value that is calculated in accordance with the sequence which will be described later.

(b) Relationship between each parameter of the 4-element focused model and the arterial waveform of the knuckle

Hereinafter, the things other than (alpha) and (omega) already determined among each constant in the said Formula (19) and (20) are examined.

First, by substituting Equations 17 and 19 into the differential equation 3, the following Equation 21 is obtained.

The following conditions are necessary for the above expression (21) to hold.

In addition, although the above equations (24) and (25) constrain α and ω, the α and ω already obtained in the equations (15) and (16) are natural, but satisfy these equations.

On the other hand, by substituting Equation 18 and Equation 20 into the differential equation 3, Equation 26 is obtained.

In order to hold the above equation (26), the following equation (27) must be established in addition to the above equations (24) and (25).

Based on conditional expressions 22 to 25 and equation 27 for the differential equation 3 obtained as described above, the constants in equations (19) and (20) are calculated.

First, E _min is represented by Equation 27

Next, in Equation 23, B

It becomes

Next, by substituting Equation 29 into Equation 22 and solving for t _b ,

It becomes

The remaining constants D _m1 and D _m2, and θ ₁ and θ ₂ are values such that the arterial waveform v _p of the knuckle can maintain continuity at t = 0, t _p1 , t _p , that is, the following conditions ( Values satisfying 1) to (4) are selected.

(One). Of the equation (19) of v _p (t _p1) in Equation 20 v _p (t _p1) is to match.

(2). V _p (t _p ) in (20) and v _p (0) in (19) coincide.

(3). The differential coefficients in t = t _p1 in the equations (19) and (20) coincide.

(4). The differential coefficient at t = 0 in equation (19) and the differential coefficient at t = t _p in equation (20).

That is, D _m1 and θ ₁ are

The value to be selected is selected. However, in the above formula,

And v ₀₁ and v ₀₂ are initial values of v _p and i _c at t = 0.

Further, D _m2 and θ ₂ are

The value to be selected is selected. However, in the above equations,

V _o2 and i _o2 are the initial values of v _p and i _c at t = t _p1 . In this way, the integers of Equations 19 and 20 are obtained.

However, by inverting at the angular frequency (ω) in Equation 16, the vascular resistance R _c at the central portion is

It becomes Here, the condition that R _c is real and positive

to be. In general, the order of R _p is about 10 ³ (dyn · s / cm ⁵ ), C is about 10 ⁻⁴ (cm ⁵ / dyn), and ω is the angular frequency of the vibration component superimposed on the pulse wave. It can be seen above (rad / s). For this reason, it can be considered that the lower limit of the expression (40) is almost 1 / (ω ² C). Thus, for simplicity, L is approximated,

R _c ,

It becomes

Further, in the relationship between equations (41) and (42), the attenuation coefficient α of equation (15) is

It becomes Using the relationship of equations (41) to (43), the remaining parameters are represented using any one of α and ω and 4 integers, for example blood inertia L,

It becomes It is clear from the equations (44) to (46) that the parameters of the model are determined by obtaining α, ω and L. Here, α and ω can be obtained from the measured waveform of the arterial wave of the finger joint. In addition, L can be computed based on one stroke amount SV.

Hereinafter, the calculation procedure of L is demonstrated based on one stroke amount SV. First, the average value of the pressure waves in the aortic starting portion is given by the following equation (47).

On the other hand, the following formula (48) holds between R _c , R _p , α, ω, and L.

In addition, since the average current flowing through the 4-element concentrated constant model, that is, E ₀₁ divided by R _c + R _p corresponds to the average value (SV / t _p ) of blood flow through the artery by pulsation, Equation 49 is Is established.

In addition, 1333.22 in said formula (49) is a proportional constant for converting the unit of a pressure value from "mmHg" to "dyn / cm <^2>".

By solving Equation 49 obtained as described above with respect to L, Equation 50 for obtaining L in one stroke amount SV is obtained as follows.

(C) Calculation method of parameter in four element concentrated constant model

68 to 71 are flowcharts showing the operation of the parameter calculation process. 72 is a waveform diagram showing the arterial waveform of the finger joint. Hereinafter, referring to these drawings, the parameter calculation processing will be described as being processed by a microcomputer (not shown).

Here, it is assumed that pulse wave waveforms such as arterial pulse waves of the finger joints, one-time extraction, and SV are measured as preconditions in calculating the parameters. Detailed description for measuring these is described in "Chapter 2, Section 2 and Section 3".

When the measurement of these pulse wave waveforms and one stroke amount is completed, the parameter calculation processing routine shown in the flowcharts of Figs. 68 and 69 is executed. Further, the?,? Calculation routines showing the flow in Fig. 70 according to the execution of the routine are executed (steps S109, S117), and the? Calculation routine shown in the flowchart in Fig. 71 in accordance with the execution of the?,? Calculation routines. This is executed (step S203). The contents of these routines will be described below.

First, the microcomputer calculates the time t ₁ corresponding to the first point P1 at which the blood pressure is maximized and the blood pressure value y ₁ , and the blood pressure after the first point, with respect to the arterial waveform of the finger joint for one stroke inserted into the built-in memory. The time t ₂ and the blood pressure value y ₂ corresponding to the second point falling once are obtained, and the time t ₃ and the blood pressure value y ₃ corresponding to the third point P3 which is the second peak point. In addition, the detailed description of these processes is described in "Chapter 3 Section 1".

Furthermore, the time of one night and the hypotension value Emin (corresponding to the first items of the equations (3) and (4)) are obtained for the arterial waveform of the knuckle inserted in the memory (step S101). In addition, in the case of a gentle pulse wave in which it is difficult to distinguish the second point P2 and the third point P3, the time of the second point P2 and the third point P3 is defined as t ₂ = 2t ₁ , t ₃ = 3t ₁ , and the blood of the point Determine the value.

In order to simplify the calculation, the normalization process of y ₁ to y ₃ is performed using the blood pressure value y _{e at the} point A shown in FIG. 73 (steps S102 and S103), and the value of B is changed to (y _e 2). Is set initially to -0.1 (step S104).

Then, the optimum values of B, t _b , α, and ω are obtained in the following order.

① First, change B in the range of y _o / 2 to y _o and at the same time change t _b in the range of t _p / 2 to t _p (+0.1 interval), and for each B and t _b | v _p (t ₁ ) -y ₁ |, | v _p (t ₂ ) -y ₂ |, | v _p (t ₃ ) -y ₃ |

② Among the values of B, t _b , α, and ω obtained in ①, | v _p (t ₁ ) -y ₁ |, | v _p (t ₂ ) -y ₂ |, | v _p (t ₃ ) -y ₃ | B, t _b , α, and ω are obtained.

③ Repeat the above ① and ② in the range of B ± 0.05 and t _b ± 0.05 based on B and t _b obtained in ②.

④ In the processing of 1 to 3 above, α changes the range of 3 to 10 to 0.1 gap, and calculates the optimum ω for each α. Further, ω is obtained by using the dichotomy to obtain a point where dv _p (t ₂ ) / dt = 0 at angle α (see FIG. 71). In the above processing, the initial value v ₀₁ of the expression (33) is set to 0 when the v _p value is calculated.

_T5 , E _m , E ₀ are calculated based on the equations (28) to (30) and (44) to (46) (step S123, step S124).

(6) Using the equation (50), the value of L is calculated in one stroke amount (step S125), and the remaining parameter values are obtained by the equations (44) to (46) (step S126).

The direct (average) total peripheral vascular resistance TPR is then calculated as follows.

TPR = Rc + Rp

(3) data string

As an example of each data required for the parameter arithmetic processing, one obtained from the arterial waveform of the finger joint shown in FIG. 72 is shown below.

First point: t ₁ = 0.104 (s), y ₁ = 123.4 (mmHg)

2nd point: t ₂ = 0.264 (s), y ₂ = 93.8 (mmHg)

Third point: t _{3 =} 0.38 (s), y ₃ = 103.1 (mmHg)

Time per night: t _r = 0.784 (s)

Minimum blood pressure: E _min = 87.7 (mmHg)

1 stroke volume data: SV = 103.19 (cc / beat)

Moreover, each data is determined so as to illustrate below by the parameter calculation process.

α = 4.2 (s ^-1 ), ω = 24.325 (rad / s)

B = 27.2 (mmHg), t = 0.602 (s)

t _p1 = 0.588 (s)

E _m = 27.4 (mmHg)

E _o = 90.3 (mmHg)

As a result, the parameters illustrated below are obtained.

L = 7.021 (dyns ² / cm ⁵ )

C = 2.407 × 10 ^-4 (cm ⁵ / dyn)

R _c = 29.5 (dyns / cm ⁵ )

R _p = 958.2 (dyns / cm ⁵ )

TPR = 1018.7 (dyns / cm ⁵ )

And, for the confirmation, if the equation 40 is calculated with the calculated parameters,

6.969 ≤ L ≤ 7.021

It can be said that the approximation of Equation 41 is valid. Also, as shown in Fig. 74, it is found that the arterial waveform W2 of the finger node calculated using the calculated parameter coincides very well with the waveform obtained by the measured waveform (W1: average waveform for 1 minute). Can be.

(4) Modification

① Calculation of inductance L

By measuring the blood flow, a value corresponding to the average current (1 / t _p ) {E _o t _p + (t _p1 E _m / 2)} in Equation 49 is obtained, and the inductance L is calculated based on the result. It's okay. Here, as the apparatus for measuring the blood flow rate, those by the impedance method and those by the Doppler method are known. Moreover, the thing using an ultrasonic wave, the thing using a laser, etc. are mentioned for the blood flow measurement apparatus by a Doppler method.

② Parameter calculation method without measuring the amount of one shot

A form in which the circulating dynamics parameters are obtained without measuring the single ejection amount SV can be considered. That is, by setting the inductance L in the dynamic parameters to a fixed value, the value of the other cyclic dynamic parameters is calculated based only on the waveform of the arterial waveform of the knuckles. As described above, the one-time amount measurement unit (for example, see FIG. 50 or less) for measuring the one-time amount can be omitted.

By the way, when the value of inductance L is fixed as mentioned above, compared with the method using the measured one-shot amount, the precision of the obtained cyclic dynamics parameter falls. Thus, to compensate for this, as shown in Fig. 74, the monitor which superimposes the artery waveform (measurement waveform) W1 of the finger node obtained by the measurement and the artery waveform (calculation waveform) W2 of the finger node obtained by the calculation is superimposed. Install it. First, the calculated waveform W2 is obtained by setting the value of inductance L to the fixed value, and the waveform is displayed on the monitor to show the degree of agreement of the waveform with the measured waveform W1. Next, the true terminal is obtained with a suitable inductance L different from the above fixed value, the calculated waveform W2 is obtained again, and the degree of agreement with the measured waveform W1 is viewed on the monitor. Subsequently, the true terminal determines appropriately the value of the inductance L as described above, calculates the calculation waveform W2 for each value of the inductance L, and compares each of the calculation waveforms W2 with the measurement waveform W1 on the monitor. Then, one waveform among these calculated waveforms W2 that best matches the measurement waveform W1 is selected, and the value of inductance L at that time is determined as an optimum value.

In this connection, as described in "Chapter 2, Section 3", having the calculation method as described above, the single ejection amount measuring unit can be omitted as shown in Fig. 54, and thus there is an advantage that the cap is unnecessary. .

③ Model of the pressure waveform at the aortic starting point

As a model of the pressure waveform of the aortic starting portion, a trapezoidal wave as shown in FIG. 75 may be used instead of a triangular wave. In the above case, since it is closer to the actual pressure waveform compared with the triangular wave, the cyclic dynamics parameter can be obtained more accurately.

④ Other calculation method of cyclic dynamics parameter

Although the cyclic dynamics parameters were obtained by calculation using a formula, each response waveform of the model when each cyclic dynamics parameter was changed within a predetermined range was simulated by a circuit simulator or the like, and best matched with the arterial waveforms of the measured finger nodes. It is also possible to select and output a cyclic dynamics parameter. In this case, more practically close complexes can be used as the electrical model of the arterial system and the model of the pressure waveform of the aortic origin, and the measurement accuracy is also improved.

Claim 2 calculation method by strain of pulse wave

(1) Overview

In the above-described analysis method by the electrical model, as a general rule, each value of the circulating dynamics parameter was calculated based on the measurement results of both the arterial waveform of the fingertip and the stroke volume. According to the above method, in order to measure accurately, it is necessary to use cape for the detection of a single ejection amount, and sometimes it is troublesome when going out. Thus, there is another method of measuring only the arterial waveforms of the knuckles and calculating the respective values of the circulatory dynamics parameters from the measurement results.

(2) output method

It is known that there is a strong relationship between the strain obtained from the arterial waveform of the knuckles and each value of the cyclic dynamics parameter. Thus, the spectrum analysis of the waveform is performed, and the strain d of the pulse wave is obtained from the following equation using the result. The calculation of the spectral information of the pulse wave is as described above in Chapter 3, Section 2.

Strain d = √ (I ₂ ² + I ₃ ² +… + I _n ² ) / I ₁

Where I ₁ is the amplitude of the fundamental wave, I ₂ , I ₃ ,. Are the amplitudes of the second, third, ..., nth harmonics of the pulse wave, respectively.

Subsequently, the value of each element is obtained from the relationship between the strain d and each value of the cyclic dynamic parameter. Here, FIG. 76A to FIG. 76D are the result of having examined the said relationship with respect to the example of the test subject 120. FIG. FIG. 76A shows the relationship between central vascular resistance R and strain d, and the relationship between ^them is represented by R _c = 58.68 ^{d -0.394} , and correlation r is r = -0.807. 76B shows the relationship between the peripheral vascular resistance R and the strain d. When the relational expression of both is obtained, it is represented by R _p = 2321.3e ^-0.615d and the correlation r = ^0.418 . In addition, Fig. ^76C shows the relationship between the inertia L and the strain d. When the relational expression of both is obtained, L = 162.8e ^-2.535d , and the correlation r is r = -1.774. 76D shows the relationship between the compliance C and the strain d. When the relational expression of both is obtained, it is represented by C = (− 1.607 + 3.342d) X10 ⁻⁴ , and the correlation r = 0.764.

(3) representative pulse wave waveform and strain

FIG. 77 shows the relationship between the strain d and the representative pulse wave waveforms of flat veins, bow veins, and strings (see developed FIGS. 1 (a) to 1 (c)). The figure shows the results of analysis on the flat vein (35), the bow vein (21), the string (22). In the figure, the flat vein has a deviation of about 0.053 up and down about 0.907. The tachycardia is larger than the deformation of the flat vein, and has a deviation of 0.148 up and down around 1.013. Variation of the tachycardia is the smallest of the three characters, with an average of 0.734, up and down by 0.064 degrees. In addition, as a result of testing the magnitude relationship between flat vein tachycardia and the deformation of strings by t-test, the risk difference was recognized to be 0.05 or less.

On the other hand, Fig. 78 to Fig. 81 show the relationship between each parameter of the cyclic dynamics parameter and the bow, flat, and string. 78 shows the relationship between central vascular resistance R and three veins. As shown in the figure, the vascular resistance of the tachycardia is the smallest (47.048 ± 18.170 dyn · s / cm ⁵ , the same below), then the vascular resistance of the flat vein is small (92.037 ± 36.494), and the vascular resistance of the string is The largest (226.093 ± 61.135). 79 shows the relationship between peripheral vascular resistance R and three veins. As shown in the figure, the vascular resistance of the tachycardia is the smallest (1182.1 ± 176.7), then the vascular resistance of the flat vein is small (1386.5 ± 228.3), and the largest vascular resistance of the string (1583.0 ± 251.0). 80 shows the relationship between the inertia L of blood and the three veins. As shown in the figure, the inertia of the bow vein is the smallest (10.337 ± 2.609), then the inertia of the flat vein is small (16.414 ± 4.604), and the inertia of the string is the largest (27.550 ± 5.393). In addition, FIG. 81 illustrates the relationship between compliance C and three veins. As shown in the figure, the bow vein compliance is the largest (2.030 ± 0.554 × 10 ^-4 cm ⁵ / dyn, the same below), followed by the greater compliance of the flat vein (1.387 ± 0.311), and the least of the string vein compliance. (0.819 ± 0.207).

As described above, the order of magnitude relations is reversed with respect to compliance only. However, if the reciprocal order of compliance is inverse, the magnitude relation is in the same order for all cyclic dynamic parameters. Moreover, about the magnitude relationship between these cyclic dynamic parameters and the three waves, the t-test has recognized a risk difference of 0.05 or less.

(4) Modification

① as a definition of the strain, but may also be used for _{(I 2 + I 3 + ...} + I n) / I 1 or the like.

(2) The correlation may be stored in the memory as a table in place of the calculation by the relational expression.

(3) The strain d can also be obtained by the method using the circuit shown in FIG.

That is, the pulse wave is input to the low pass filter 240 and the high pass filter 241 to output the low frequency signal component v ₁ and the high frequency component v ₂ . Subsequently, the respective output signals v ₁ and v ₂ are rectified by the rectifier circuits 242 and 243, and smoothed by the smoothing circuits 244 and 245 to obtain direct current signals dc1 and dc2. These DC signals dc1 and dc2 are divided by the division circuit 246 to obtain a strain rate d = dc2 / dc1.

(4) The cyclic dynamics parameter is not limited to the above-described one, and the same result can be obtained even if a model similar to the other is assumed. In particular, the correlation equation for obtaining the dynamic parameters is not limited to the above, and other empirical equations may be employed.

Section 3 Calculation Method Based on Strain of Pulse Wave and Amplitude and Phase of Harmonic Wave of Spectrum

The cyclic dynamic parameters can also be obtained from the strain obtained from the pulse wave, the amplitude and phase of the harmonics in the frequency spectrum of the pulse wave.

First, by Fourier analysis of the waveform of the read pulse wave, the amplitude I ₁ , I ₂ , I ₃ ,... And phases P ₁ , P ₂ , P ₃ ,... (For this purpose, for example, the hardware described in Chapter 3, Section 2) may be used. Next, the amplitude values I ₁ , I ₂ , I ₃ ,... The strain d of the pulse wave is obtained by the following equation.

d = √ (I ₂ ² + I ₃ ² +… + I _n ² ) / I ₁

Then, the strain d, the phases P ₁ , P ₂ , P ₃ ,. Find the value of each parameter of the dynamic parameter in the regression equation with each value of the cyclic dynamic parameter. Thus, the above regression equation is shown below.

From here,

In these equations, R ² is a coefficient of determination, P is a risk, and n is the number of samples.

These regression equations measure the arterial waves of the knuckles of a large number of subjects, and Fourier interpretation of the measured pulse waves to obtain the amplitude and phase of the fundamental and harmonics, while the one-off volume and arterial waveform of the knuckles for each subject. It can be obtained by calculating the cyclic dynamics parameter at and calculating the correlation of the amplitude, phase, and parameters obtained for each subject.

Section 2 Analysis of Living State Based on Pulse Waves

(LF, HF, `` LF / HF '', calculation of RR50)

Clause 1 indicative of the pulse wave

The four of LF, HF, "LF / HF", and RR50 are, as it were, information about the "wave" of the pulse wave (an indicator of living state). Hereinafter, the meaning of these indicators is demonstrated.

In the electrocardiogram, the time gap between the R wave of a certain heartbeat and the R wave of the next heartbeat is called the RR gap. The RR interval is a numerical value that is an index of autonomic nerve function in the human body. FIG. 83 shows the heart rate in an electrocardiogram and the RR gap obtained from the waveforms of these heart rates. As can be seen from the figure, according to the analysis of the electrocardiogram measurement results, it is known that the RR gap fluctuates with time.

On the other hand, the fluctuation of the blood pressure measured at the artery part of the finger joint is defined as the fluctuation of the systolic blood pressure and the diastolic blood pressure per night, and corresponds to the RR gap variation in the electrocardiogram. Fig. 84 shows the relationship between the electrocardiogram and blood pressure. As can be seen from the figure, the blood pressure of the systolic and diastolic devices is measured as the maximum value of arterial pressure in each RR gap and the minimum value immediately before the maximum value.

By performing the spectral analysis of these heart rate fluctuations or blood pressure fluctuations, it can be seen that these fluctuations consist of waves of a plurality of frequencies. These are divided into three kinds of variable components shown below.

① HF (High Frequency) component that is a change consistent with breathing

② LF (Low Frequency) component that fluctuates around 10 seconds

③ The trend to fluctuate below the measurement limit

For each of the measured pulse waves, the RR gap between adjacent pulse waves and pulse waves is obtained, and the discrete values of the obtained RR gaps are interpolated by a suitable method (for example, 3rd order spline interpolation) (Fig. 83). See). Then, by performing an FFT process on the curve after interpolation and performing spectral analysis, it is possible to extract the above-mentioned variation component as a peak on the frequency axis. FIG. 85A shows the waveform of the variation in the measured RR gap of the pulse wave and the waveform of each variation in the case where the variation waveform is interpreted as the three frequency components. FIG. 85B is a result of spectral analysis of the fluctuation waveform of the RR gap shown in FIG. 85A.

As can be seen from the figure, for example, in the case of resting, peaks can be seen at two frequencies around 0.07 Hz and around 0.25 Hz, the former being an LF component and the latter being an HF component. In addition, since the component of a drain is below a measurement result, it cannot read in a figure.

The LF component indicates the degree of tension of the sympathetic nerve, and the greater the amplitude of the component, the more the tension increases (or is in a calm state). On the other hand, the HF component indicates the degree of tension of the parasympathetic nerve, and means that the amplitude of the present component is relaxed (or calmed) as the amplitude of the component is large.

Since there are individual differences in the amplitude values of the LF component and the HF component, when this is taken into account, "LF / HF", which is an amplitude ratio of the LF component and the HF component, is useful for estimating the subject's tension. In the characteristics of the above-described LF component and HF component, the larger the value of "LF / HF", the higher the degree of tension, and the smaller the value of "LF / HF", the lower the degree of tension.

On the other hand, RR50 is defined as the number by which the absolute value of the clearance of the pulse wave corresponding to the continuous RR clearance of 2 heartbeats fluctuated more than 50 milliseconds in the measurement of the pulse wave of predetermined time. It is clarified that the larger the value of RR50 is in the calm state, and the smaller the value of the RR50 is in the excited state.

Incidentally, when calculating RR50, only the RR gap (pulse wave gap) is required, and the pulse wave frequency analysis is not necessarily required.

Clause 2 exposure method of each indicator

These indices are calculated from the pulse wave waveform in the following order.

(1) calculation of pulse wave gap

First, the waveform of the pulse wave for a predetermined time (for example, 30 seconds or one minute) is put in, and the waveforms of all the pulse waves that have entered within the measurement period by the extraction process of the peak information described in Chapter 3, Section 1, and the like. The peak detection process is performed. And based on the time of the peak of two adjacent pulse waves, both time gap (it is called RR gap hereafter since it corresponds to RR gap) is computed.

(2) LF. Calculation of HF and `` LF / HF ''

Since the RR gap values obtained above are discrete on the time axis, interpolation between adjacent RR gaps is interpolated by a suitable interpolation method to obtain the curve shown in Fig. 85 (a). Next, performing an FFT process on the curve after interpolation yields a spectrum as shown in FIG. 85 (b). therefore. As in the case of the pulse wave waveform, a process for extracting peak information is applied to obtain a maximum value in the spectrum and a frequency corresponding to the maximum value, and the maximum value obtained in the low frequency region is obtained in the LF component and the high frequency region. Is taken as the HF component. The amplitudes of these components are also calculated to calculate the amplitude ratio "LF / HF" of both.

(3) calculation of RR50

Based on the RR gap obtained above, time difference of adjacent RR gap is calculated | required sequentially, it is examined whether the said time difference about each exceeded 50 millisecond, and counts the number corresponding to this and makes RR50.

Section 3 Correction of living state based on body measurements

In each of the above sections, various ecological states obtained from pulse waves and pulse wave analysis methods for obtaining them have been discussed.

However, the living state is found to change due to the intense activity of the subject. For example, the value of "LF / HF" is larger when the test subject is moving compared to the resting time when the test subject is not moving. Thus, it is conceivable to correct the living state obtained from the pulse wave in accordance with the body motion of the subject. This is specifically as follows.

First, as a first method, the subject is equipped with an acceleration sensor or an acceleration sensor is installed in the apparatus, and the value of the acceleration sensor is measured simultaneously with the pulse wave measurement. And when it is recognized by the measurement result of an acceleration sensor that a subject is moving, the biological state measurement value is appropriately correct | amended by the measurement value of an acceleration sensor, and it converts into the value of normal time (stable time).

As a second method, the biometric state obtained from the pulse wave and the values of the acceleration sensor are measured at all times, and these measured values are stored in a memory in comparison. When measuring the living state at the present time, the measured value closest to the value measured by the acceleration sensor at the present time is found in the memory, and the living state stored in pairs with the value of the found acceleration sensor is stored at the present time. It is set as the living body state.

As described above, even when the subject is influenced by the biological state for the reason of exercising, the biological state consistent with the subject activity can be obtained based on the similar activity state in the past.

In addition, the steady state here means that the movement near the pulse wave sensor measured by an acceleration sensor is below a predetermined threshold (for example, 0.1 G). Specifically, for example, when the arm is shaken, the pulse wave cannot be measured. Therefore, not only can it be measured during exercise, but it can also be said that it is not suitable also in the walk or the walk of a room.

So, for example, if the user is indoors, move to a room with a desk and chair, sit on a chair as shown in FIG. 86A, place the hand on which the wristwatch 320 is mounted on the desk, Be careful not to move it. First, ideally, it is ideal to do the above, but, for example, when the user is outdoors, the exercise is stopped first to clear the breathing, and if walking, stop walking once. Subsequently, for example, a posture as shown in FIG. 86B is carried out, and a necessary operation such as pressing a button of the wristwatch 320 with the hand on the opposite side while keeping the wrist worn on the wristwatch 320 is not moved. Do it.

Incidentally, in the state where the pulse wave sensor 305 of the necklace or the glasses is attached, it is possible to sit in a chair or to stand up, so that the body can be moved as much as possible. Importantly, there is no problem if the pulse wave sensor 305 is not vibrated.

<Variation example>

As the frequency analysis method applicable to this chapter, various frequency analysis methods such as DFT (discrete Fourier transform), MEM (maximum entropy method), wave rate conversion, and the like can be considered.

Chapter 5 Interface Means

In the various devices described in the following chapters, the human device gives instructions or inputs data to the device, while the device can notify the human being in various forms. Although such a means for inputting information or a means for notification may be required depending on the purpose of the apparatus or the like, in most cases, the means is not considered to be a problem when the purpose is reached. For example, when a warning is given to a human, a buzzer may be sounded and a message may be displayed on a display. Furthermore, it may be notified by voice. This is sufficient if the purpose of warning is met.

Thus, this chapter lists specific examples of these means. In principle, the apparatus described in the next chapter can be realized by using one of the following listed as input means or notification means, and therefore, various changes are made.

Section 1 input means

In the case where an instruction is given to a device by a human, or when inputting information, a device as shown below can be used.

① keyboard

Pointing devices: mouse, touch screen, tablet, trackball, etc.

③ various storage media

Most of the various numerical values provided for the storage of information can be used as input means. Examples of these include floppy disks, magnetic disks, and magneto-optical disks. In addition, various media such as magnetic drums, magnetic tapes, cassette tapes, and CD-ROMs (compact disks) may be mentioned.

④ In addition, a microphone, a scanner, or the like can also be considered in consideration of input by voice or image.

Section 2 input means (notification means to human being)

Examples of the means for notifying the human in the apparatus include those described below. It is thought that these means would be appropriate to classify based on the five senses. In addition, these means may not only be used independently but may combine several means.

As described below, for example, the use of a means for appealing out of time may allow the visually impaired to understand the contents of the notification. In the same configuration, if the means for appealing out of hearing are used, a notification for the hearing impaired may be made. It is possible to configure an excellent device even for a user with a disability. In addition, the use of the device for appealing to the hearing and the sense of touch improves the use of the device by providing the advantage that the user does not need to look specifically at the liquid crystal display of the wrist watch even during exercise.

Section 1 means of appealing to hearing

As the notification means for appealing to the hearing, it is for notifying the pulse wave analysis result, the diagnosis result, etc., or for the purpose of giving a warning to the human, and the following can be considered. In addition, these means are often embedded in a portable device such as a wrist watch, and in such a case, an element assembled as part of a watch may be useful.

① buzzer

② voltage device

③ speaker

(4) As a special example, it may be considered to have a portable radio call receiver in a human being to be notified, and to call the portable radio call receiver on the device side when making a notification.

In addition, there are many cases in which notifications are to be delivered using not only the notification but also some information. In such a case, the level of information such as sound or the like described below may be changed in accordance with the contents of the information to be conveyed.

① pitch

② volume

③ tone

④ voice

⑤ Types of music (songs, etc.)

Clause 2 Means of appeal

Means for visual appeal are used for the purpose of informing the device of various message measurement results or for warning. As a means therefor, the following apparatus can be considered.

① Display device

CRT (cathode ray tube display device), LCD (liquid crystal display display), etc. are mentioned. As a special display device, there is a spectacle type projector (see Fig. 29) described in "Chapter 2, Section 6".

② printer

③ X-Y projector

④ lamp

In addition, the following changes can be considered in the notification.

① Digital display, analog display according to notice of numerical value

② Display by graph

③ Add color to the display color

④ Bar graph display in case of notifying by number or rating

⑤ pie graph

⑥ Face chart

In the case of notifying by rating, the face chart as shown in FIG. 87 is displayed according to the grade. In the figure, six grades are assumed.

SECTION 3 Means for appealing to the sense of touch

Means of appealing to the sense of touch may be considered to be used for warning purposes. Means for that are as follows.

① electrical stimulation

Electrical current is supplied to the shape memory alloy which protrudes from the back of the portable device such as a wrist watch.

② mechanical stimulation

A projection (for example, a needle that is not so pointed out) on the back of a portable device such as a wrist watch is stimulated by the projection as a structure that allows entry and exit.

On the other hand, if the contents of the notification are simple, the user can be notified in the following form using mechanical vibration. First, a vibration alarm for transmitting vibration by rotating an eccentric load is known, but this may be provided integrally or separately from the main body of the portable device. In addition, as shown in FIG. 88, a recessed part having a thickness of about 70 µm may be formed in a part of the lower surface of the main body of the portable device, and the piezoelectric element PZT may be provided therein. When an AC voltage of an appropriate frequency is applied to the piezoelectric element PZT, the piezoelectric element PZT vibrates and is transmitted to the user equipped with the portable device. The thickness of the piezoelectric element PZT is 100 µm, and the diameter thereof may be about 80% of the diameter of the recess. If the diameter of the piezoelectric element PZT is about 80% as described above, the sound pressure of the notification sound can be increased.

By using the above mechanism, if the vibration intensity, vibration time, vibration frequency, and the like are changed in accordance with the contents of the notification, various notifications can be made to the class.

Section 4 means for appealing to the sense of smell

As a means for appealing to the sense of smell, a discharging mechanism such as a perfume may be provided in the apparatus so that the contents to be notified correspond to the aroma, and the perfume according to the contents may be discharged. Incidentally, the micro pump or the like described in "Chapter 6 Section 2 Clause 1" is optimal for a discharge mechanism such as perfume.

Section 3 communication means

In various apparatuses described in Chapter 6 below, I / O (input and output) interface means for communicating with an external device such as a personal computer can be provided, whereby Information may be transmitted to an external device, or instructions or settings transmitted from the external device may be received into the device.

Thus, a description is given below with reference to FIG. 89 of the communication means for performing communication with an external device. As shown in the figure, it is composed of a personal computer apparatus main body 380, a display 331, a keyboard 332, a printer 333, and the like, and is constituted of an ordinary personal computer except for the following points. Therefore, explanation of the internal structure is omitted.

That is, the apparatus main body 330 has a transmission control unit and a reception control unit (not shown) for transmitting and receiving data by an optical signal, and each of the transmission control unit and the reception control unit has an LED 334 and an optical unit for receiving an optical signal, respectively. And a phototransistor 335 for receiving the signal. These LEDs 334 and phototransistors 335 are all used for near infrared rays (for example, those having a center wavelength of 940 nm), and the main body of the device 330 through the visible light cut filter 336 for blocking visible light. In the communication window 337, optical communication provided on the front surface of the optical device is performed.

On the other hand, the device side connected with a personal computer has the following structures. Although the wrist watch shown in FIG. 32 etc. is demonstrated here as an example, even if it is various portable devices, such as a necklace and glasses, there is no problem. As described above, the connector portion 105 is detachably configured in the apparatus main body 100 of the wrist watch. Therefore, as shown in FIG. 89, the communication connector 338 may be provided in place of the connector cover for the connector portion from which the connector portion 105 is removed. The communication connector 338 contains an LED, a phototransistor, and an optical communication interface as in the personal computer side. In addition, an optical interface unit (not shown) for optical communication is provided inside the apparatus main body 100 of the wrist watch.

The transfer command is input from the keyboard 332, for example, to transfer various kinds of information stored in the RAM or the hard disk of the personal computer side to the wrist side from the personal computer side. As a result, the information on the personal computer side is output as near-infrared light via the LED 334 and the communication window 337. On the other hand, the near-infrared light is transmitted to the optical interface of the wrist watch through the communication connector 338 on the wrist watch side.

On the other hand, when various types of information such as measurement of a living state are transmitted from the wristwatch to the personal computer, the communication direction is reversed from the above. That is, the user of the mobile device sets the mobile device to the mode for data transmission by operating a button switch installed on the wrist watch. As a result, the processor or the like embedded in the apparatus reads out information to be transferred from the RAM or the like and sends it to the optical interface unit. As a result, the measured value is converted into an optical signal, sent out from the communication connector 338, and transmitted to the personal computer through the communication window 337 and the phototransistor 335.

However, in the case of performing the above optical signal, if it is not possible to distinguish which device sent the information, it is possible to incorrectly receive information that the other device should accept. Thus, the I / O interface means according to the present invention uses identification information indicating which device sent the information in transmitting or receiving information.

Hereinafter, a configuration for preventing contention when there are a plurality of devices that transmit optical signals will be described with reference to FIG. 90. The transmitter 340 shown in the figure is embedded in the I / O interface means. In the figure, information on a processor or the like embedded in a portable device or a personal computer is described on the bus.

The A / D converter 341 cycles various information signals transmitted from the bus at predetermined time intervals and converts them into digital signals.

The identification number storage unit 342 stores an identification number for identifying which device the empty signal is sent from, and the identification number is used together with the corresponding information when the information is sent out of the delivery device 340. Place it in the signal. The identification numbers stored in the identification number storage unit 342 in each transmission device 340 are given different numbers according to the settings at the time of shipment. Therefore, a setting is made such that all devices, including portable devices, personal computers, and other devices, are assigned a unique number.

The control unit 343 is a circuit for controlling each unit in the transmitting device 340. In addition, the transmitter 344 has a built-in drive circuit for driving the LED 345 for transmitting the optical signal, and by driving the LED 345, by converting the transmission data generated by the control unit 343 into an optical signal Send out.

By enabling communication with the external device as described above, it is possible to transmit the information on the portable device side to the external device side, and at the same time, it is possible to give various settings or instructions to the portable device side from the external device.

Finally, one specific example of information transmission between the portable device and the external device will be described. Now, it is assumed that the waveform of the pulse wave measured on the portable device side is displayed on the display 331 (see FIG. 89) provided on the external device side. In addition, the kind of pulse wave waveform displayed on the display 331 shall be any of the above-mentioned flat vein, bow vein, and string. Then, the type of the measured pulse wave waveform is compressed on the portable device side and then transmitted from the portable device side to the external device.

In order to realize the above, first, the portable device side analyzes the pulse wave waveform measured by the living body and determines which of the flat vein, the bow vein, and the string of veins. As a method for performing the determination, the correlation between pulse strain (or cyclic dynamics parameter) and flat veins, bow veins and string waves is investigated in advance, and the strain (or cyclic dynamic parameter) of pulse waves is calculated from the measured pulse waves. The method of determining the type of the like is considered.

Subsequently, this is encoded by, for example, a character code in correspondence with the determined pulse wave. Then, the encoded information is transmitted to the external device side by optical communication through I / O interface means provided in the portable device and the external device, respectively. Then, on the basis of the encoded information transferred from the external device side, the pulse wave type is identified as either flat, live or string, and the pulse wave waveform for the identified pulse wave is read from a ROM or the like stored in the external device. Shown on display 331.

In addition to the image of the pulse wave waveform as described above, the display 331 may display a name corresponding to a classified waveform such as flat vein or bow vein as a character, or may display a symbol, an icon, or the like representing the waveform. It's okay.

As described above, when the portable device and the external device are configured to realize communication using compressed information, the amount of information to be transmitted can be reduced. The communication using the compressed information as described above is the same in the case of transmitting information from the external device side to the portable device side.

<< modification >>

① In addition, the actual place and the communication connector 338 may be connected by wire with an external device, and may be comprised so that it may communicate wirelessly by wireless or optical communication mentioned above.

Chapter 6 Diagnosis and Control of Biological Status

Various means by which the apparatus described in this chapter is used are only an example, and various deformation | transformation are possible for it. For example, a device using a wrist watch type as a pulse wave detection unit can also be replaced with a necklace type or eyeglass type pulse wave detection unit. In addition, when a device using a cyclic dynamics parameter is used as a biological state, for example, the cyclic dynamics parameter may be obtained based on an electrical model, or may be obtained based on strain.

Section 1 Diagnosis of Biological Status

The apparatus in this section performs various diagnostics based on the living state obtained from the pulse wave analysis, and notifies the resulted terminal, the subject, or the like.

Claim 1 diagnostic device using the periodic fluctuation of the biological state

The device diagnoses the patient's condition by accurately detecting the change in the living state, taking into account the periodic change in the state of the living body (in-day variation, annual variation, etc.).

<< First Example >>

As described above, the human circulation dynamics fluctuate within a day, and there are individual differences in the fluctuation forms. The apparatus according to the present embodiment is capable of capturing a change in the health state of the patient by fully considering the variation of the circulation dynamics during the day and letting the terminal know. That is, in the present embodiment, the circulating dynamics parameter is extracted from the patient at a plurality of times every day, and each time the extraction is performed, the cyclic dynamics parameter extracted at the present time is determined by the cyclic dynamics parameter at the same time within the past fixed period. It is determined whether or not it is within the fluctuation range, and if not, the notification is performed.

<Configuration of the device>

91 is a block diagram showing the configuration of the apparatus according to the present embodiment. In the figure, the pulse wave detection unit 381 is a means provided for measuring the arterial waveform of the knuckles in the patient, and the single stroke amount measuring unit 382 measures the single stroke amount and outputs an electrical signal indicating the result. do. In addition, the detailed description of the structure, operation | movement, and a measurement form of these pulse wave detection part 381 and the one time ejection amount measurement part 382 is as having described in "Chapter 2".

Next, each part which comprises the control part 380 is demonstrated. The memory 383 is a nonvolatile memory composed of a battery backed-up RAM and the like, and is used as temporary storage of control data when the microcomputer 387 controls each part of the control unit 380. In addition, in the predetermined storage area of the memory 383, cyclic dynamic parameters measured at a plurality of different times are stored for each patient.

The input unit 384 is input means provided for inputting commands to the microcomputer 387, and is configured by, for example, a keyboard.

The output unit 385 is an output means composed of a printer display device or the like, and these devices perform recording and display of information such as circulating dynamic parameters obtained from a patient under the control of the microcomputer 387.

The waveform extraction storage unit 386 receives the pulse wave signal output from the pulse wave detection unit 381 under the control of the microcomputer 387, extracts and stores the pulse wave for one night from the received signal. In addition, the detailed description of the waveform extraction storage part 386 is described in "Chapter 3 Section 1 Clause 2."

The microcomputer 387 controls each unit in the control unit 380 in accordance with a command input through the input unit 384. The microcomputer 387 has a built-in clock circuit, and when any one of a plurality of preset times comes, the following processing is performed each time.

① Measurement of arterial wave and single stroke of finger joint

② Calculation of Circulation Dynamic Parameters

(3) Determination of whether or not the present cyclic dynamics parameter is contained within the variation range of the cyclic dynamics parameter at the same time in the past fixed period.

④ Alarm output when a negative result is obtained for the above determination

The body motion detecting unit 391 is a body motion detecting means for grasping the body motion of the user of the apparatus, and converts the measured body motion value into a digital signal and sends it to the microcomputer 387.

<Operation of the device>

Hereinafter, the operation of the present embodiment will be described with reference to the flowchart shown in FIG. 92.

As described above, the microcomputer 387 of the present embodiment includes a clock circuit, and a plurality of times (for example, six, eight, ten, twelve o'clock) in which the current time specified by the clock circuit is preset. , ...), the processing shown in FIG. 92 is performed.

First, the process proceeds to step S501, and the microcomputer 387 uses the pulse wave detection unit 381 and the waveform extraction storage unit 386, as described in Chapter 3, Section 1, to arteries of the knuckles. Processing for extracting the waveform is performed to extract peak information of the pulse wave.

Here, in the measurement of the pulse wave, the microcomputer 387 reads the output of the body motion detector 391 and stores it in the memory 383. Then, it is determined whether or not the output value of the body motion detecting unit 391 shows that the user is in a stable state. If it is not in a stable state, the measurement of the pulse wave may be inaccurate. Therefore, the microcomputer 387 uses the output unit 885 to notify the user of the above effect. Then, after confirming that the user is in a stable state suitable for the pulse wave measurement, the pulse wave is measured.

Next, when proceeding to step S502, the microcomputer 387 controls the one-time ejection amount measuring unit 382 to measure the one-time ejection amount of the patient.

Next, the process proceeds to step S503, where the microcomputer 387 executes the calculation process of the cyclic dynamics parameter. That is, the microcomputer 387 obtains one start point of the pulse wave for one night to extract the waveform parameter, and the waveform value of the pulse wave for one night starting at the peak address of the start point is determined by the waveform extraction unit 368. Is read from Then, based on the pulse wave for one night read as described above and the extraction amount measured in step S502, the values of the elements of the four-element concentrated constant model are calculated, and the memory ( 383).

In the calculation of the cyclic dynamic parameters, since the method described in Section 4, Section 1 Section 1 is adopted here, the amount of ejection is measured once. The method described in paragraph 3 ”may be used.

The microcomputer 387 then proceeds to step S504, and the microcomputer 387 changes the cyclic dynamics parameter at the same time within the past fixed period in which the cyclic dynamics parameter at the current time obtained in the step S503 is stored in the memory 383. Determine if it is in range. The above process will also be described in detail as follows.

That is, if the current time is 8:00 am, the microcomputer 387 refers to, for example, the cyclic dynamic parameters at 8:00 am one day, two days ago, and three days ago, and the average value of these cyclic dynamic parameters ( In other words, the moving average value E and the standard deviation σ are calculated. Then, it is determined whether or not the cyclic dynamics parameter at the present time is in the range of E ± 3σ.

In the above judgment, when one of the cyclic dynamic parameters is out of the range of E ± 3σ of the parameter in the past fixed period, the process proceeds to step S505, and the output unit 385 outputs an alarm to perform processing. Quit. On the other hand, when all kinds of cyclic dynamic parameters fall within the range of E ± 3σ of the parameter in the past fixed period, the processing is terminated without performing an alarm output.

According to the present embodiment, when the patient's condition changes and a sudden change in the circulating dynamics parameter that is unacceptable as the variation in the day occurs, this can be detected quickly. In other words, if there is a change between the physical condition of the day and the physical condition of recent days, the patient can know the effect.

In addition, in the above description, the alarm is outputted when the current cyclic dynamics parameter does not exist in a predetermined range from the average value of the parameters in the past fixed period. However, when there is an abnormality, a notification may be made without notification if the rhythm of the body is good. In the above embodiment, if the circulatory dynamics parameter at the present time is within the E ± σ range, for example, the current rhythm of the current body can be said to be smooth without changing from the latest, so It is possible to notify that the state of is good.

As described above, when the state of good body is notified, the user who is notified can also be mentally afforded, which also contributes to the improvement of the QOL.

<< Second Embodiment >>

In the first embodiment described above, the abnormality of the physical state is detected based on the change of the circulatory dynamics parameter. However, the abnormality of the physical state can also be detected based on the variation of the pulse wave spectrum during the day. For this reason, in this embodiment, the spectrum of the current pulse wave is detected, and the abnormality of the physical state is detected by comparing with the spectrum of the past at the same time.

<Configuration of the device>

93 is a block diagram showing the construction of the apparatus according to the present embodiment. The difference between the apparatus shown in the drawing and the apparatus shown in FIG. 91 is that the single ejection amount measuring unit 382 in FIG. 91 is not provided and the frequency analyzer 388 is newly provided.

The frequency analyzer 388 receives the waveform value of the pulse wave in units of beats through a microcomputer, repeats the received waveform value at high speed, and performs frequency analysis for each beat to calculate the spectrum constituting the pulse wave. In addition, the detailed structure and operation | movement of the said frequency analysis part 388 are described in "Chapter 3 Section 2 Clause 2".

<Operation of the device>

In the following, the operation of the apparatus will be described only with respect to the parts different from the first embodiment. The microcomputer 387 controls the waveform extraction storage 386 and the frequency analyzer 388 so that the amplitudes H ₁ to H ₆ and the phases θ ₁ to θ ₆ of each spectrum of the pulse wave in the frequency analyzer 388 are determined. To be detected. Subsequently, these detected values are stored in the memory 383, and based on these stored data, basic data of abnormality detection of the body is created as in the first embodiment. And abnormality of a body is detected by comparing present detection data with the said basic data.

In addition, as described above, rather than detecting all of amplitudes H1 to H6 and phases θ ₁ to θ _6, for example, it is especially safe to change the physical condition to only a well-appearing phase θ ₄ is detected. In addition, as in the first embodiment, notification may be made when the physical condition is good.

<< Third Example >>

In each of the above embodiments, the measurement of the biological state has been made at a predetermined time. On the other hand, in the present Example, the measurement at the time out of the on-time is enabled. That is, in order to perform an accurate diagnosis, it is desirable to measure arterial waves of a knuckle, etc. by keeping a predetermined time every day. However, because it may be difficult, measurement can be performed even at a time out of the on-time. For example:

① When it is time to make a measurement, the diagnostic device notifies you of the effect by a chime.

(2) The patient responds to this as soon as possible, attaches a cap, etc., and inputs, by the input unit 384, a command to instruct the device to measure arterial waves of the fingertips.

(3) The apparatus executes the process shown in FIG. 92 as in the respective embodiments above. In the above case, however, in step S503, the time when the measurement is actually made is written to the memory 383 together with the cyclic dynamics parameter. By doing so, the extraction time of the cyclic dynamics parameter in the memory 383 becomes irregular with the day. Therefore, in step S504, a determination process is performed as follows.

For example, suppose that the measurement was performed at 8:20 am now. In this case, several parameters before and after each of the extracted circulating dynamic parameters stored in the memory 383 at the time before and after 8:20 am are read out. Then, interpolation curves (e.g., quadratic curves) between the floats when the cyclic dynamics parameters are plotted on two-dimensional coordinates whose horizontal axis is the time and the vertical axis are the cyclic dynamics parameters are obtained. Then, the value at 8:20 am of the interpolation curve is obtained. In addition, the same processing was performed two days ago, three days ago,. The cyclic dynamics parameter of is performed, and each cyclic dynamics parameter in 8:20 am in the past fixed period is calculated | required by interpolation calculation. Then, the average value and the standard deviation sigma of each cyclic dynamic parameter obtained by the interpolation operation as described above are obtained, and the same determination as in the above embodiments is performed.

As described above, in the present embodiment, even when a parameter corresponding to the current time is not stored in the storage means in the parameter within the past fixed period, the parameter corresponding to the current time can be obtained by interpolation calculation. Therefore, it can handle even in the situation where it is difficult to measure a living body state on time.

In addition, as in the first embodiment, notification may be made when the body is in good condition.

<< Fourth Example >>

In this embodiment, diagnosis is made based on the type of change in the cyclic dynamics parameter. In other words, it is determined that the change in the cyclic dynamics parameter is not based on the change in the cyclic dynamics parameter at the same time in the past.

Also in this embodiment, the processing proceeds in accordance with the flowchart of FIG. 92 described above. In the present embodiment, however, in the late-night time zone in which the arterial waves of the fingertips are not measured, the microcomputer 387 reads the cyclic dynamic parameters at each time recorded on the day in the memory 388. Then, it is determined which state each cyclic dynamics parameter corresponds to, and the result of the determination is added to the cyclic dynamics parameter and recorded in the memory 383.

B: It is a local minimum

U; On the rise

T: The maximum value

D: descending

And in the determination of step S504 of FIG. 92, it is first determined whether the change from the cyclic dynamic parameter obtained last time to the cyclic dynamic parameter obtained this time is rising or falling, and the said determination result is the same time within the past fixed period. It is determined whether or not the change in the cyclic dynamics parameter in accordance with the trend is followed.

That is, for example, when paying attention to the trend of change with respect to 8:00 am, it is assumed that the circulating dynamics parameter has an upward trend (U) in almost one day in the past 10 days. In the above case, when the cyclic dynamics parameter obtained at 8:00 am of the day is rising compared to the cyclic dynamics parameter obtained at 6 am of the previous day, the method of changing the cyclic dynamics parameter depends on the variation method in the past 10 days. It can be said to be normal. On the contrary, when the cyclic dynamics parameter obtained at 8:00 am of the day is lower than the cyclic dynamics parameter obtained at 6 am of the previous day, the variation of the cyclic dynamics parameter is inversely reversed to the variation method in the past 10 days. It can be said to be strange. In this case, therefore, the flow advances to step S505 in FIG. 92 to output an alarm.

As described above, according to the present embodiment, it is possible to capture a change in the biological state unnaturally.

In addition, in the above description, a notification is made when the state of change of the cyclic dynamics parameter at this time is in violation of the change of the cyclic dynamics parameter described above. By the way, according to the case of the first embodiment, when the state of variation at the present time is the same as the state of variation in the past, it means that the physical condition is good, so the user may be notified of this effect.

<< Fifth Embodiment >>

In this embodiment, the diagnosis is performed based on the maximum value generation time and the minimum value generation time of the parameter. That is, the current parameter based on the maximum value generation time and the minimum value generation time of the past parameter is to capture the unnatural movement.

In the above-mentioned fourth embodiment, the state of change such as rising or falling is obtained for each parameter obtained on the day, but in this embodiment, the time at which the value becomes the maximum and the time at which the value becomes the minimum To be written into the memory 383. Then, for example, each range of the minimum value and the minimum value generation time in the past 5 days is obtained, and a section between them is obtained.

For each of these ranges we can say

① The section between the range of the minimum value generating time and the immediately adjacent maximum value generating time is a section in which the parameter rises. If the parameter is rising in the section, it is normal, and if it is falling, it is abnormal.

② It is the section in which the parameter falls between the range of the maximum value generating time and the immediately adjacent minimum value generating time. In this section, it is normal if the parameter is falling, and is abnormal if it is rising.

In the present embodiment, when the current time corresponds to the above section, judgments 1 and 2 are made regarding the parameters at that time.

In addition, the generation time of the maximum value and the minimum value employ | adopts the maximum value of the actual parameter and the extraction time of the minimum value, and obtains the daily fluctuation curve of a parameter by state analysis, and generate | occur | produces the maximum value and minimum value in the said daily fluctuation curve. Time may be employed.

As described above, according to the present embodiment, it is possible to capture unnatural changes in the biological state.

In addition, in the above description, when the current time corresponds to a minimum value generation interval or a maximum value generation interval, a notification is made if the change state of the cyclic dynamics parameter at this time is in violation of the change of the cyclic dynamics parameter in the past. To do so. By the way, according to the case of the first embodiment, when the change state at the present time is the same as the change state in the past, the user may be notified that the physical condition is good.

<< Sixth Example >>

This embodiment applies the device to the diagnosis of internal detuning.

Living in a time containment laboratory with no clues of time, the human cleansing function runs freely in a cycle of about 25 hours, but in long time segregation, sleep awakening and rectal temperature rhythms are unclear, It is often seen that the former changes state about 30 hours and the latter about 25 hours. This phenomenon is called internal decoupling.

In recent years, situations such as being put in a state of time segregation also increase in daily life, and internal decoupling often occurs in daily life even without time segregation experiments. For example, mobile work, such as night shifts, when people fly to remote locations around the world with different world views (so-called time lags), and other irregular lives.

In the case of internal desynchronization, it leads to patients with autonomic ataxia. Therefore, when internal detuning occurs, it is necessary to find this early.

However, rectal temperature conditions are generally synchronized with cyclic dynamics parameters. According to the first embodiment, since the fluctuation rhythm of the circulatory dynamics parameter reflecting the rectal temperature condition can be detected during the day, the symptom of the internal fluctuation can be diagnosed by detecting the dizziness of the fluctuation state during the day.

In this case, there is an advantage that the diagnosis can be performed without using a deep thermometer.

In addition, according to each of the embodiments described above, it is possible to make a diagnosis in consideration of the periodic change of the original state of the living body, and to accurately detect the unnatural change of the living state. In addition, changes in circulation dynamics before and after exercise, before and after bathing, and the effects of training mental stability can be seen.

<< modification >>

① The metronome sound source may be installed in the device, and the metronome sound of 0.25Hz may be generated before the measurement is made, and the patient may have normal breathing.

(2) In the memory 383, parameters obtained every day up to the present are recorded. Thus, an X-Y plotter is used as the output device, and the control unit 380 (or the control unit 389) controls the X-Y plotter to plot the fluctuation curve of the parameter throughout the day. In addition, it is possible to visually capture the change of the patient's condition by plotting the fluctuation curve of the parameter on the plurality of days in accordance with the designation of the user.

③ According to the user's designation, the correlation between the fluctuation curves of the day on a plurality of days is calculated and outputted. By doing as mentioned above, the change of a biological state can be caught.

④ Every day, whenever the extraction of parameters for one day is finished and the variation curve of the parameter of the day is confirmed, the correlation between the variation curves of the day of the day may be calculated. By doing so, it is possible to detect the collapse of the living body state by detecting that the mutual relationship is broken.

(5) In the first embodiment, correction may be made in consideration of the annual variation of the cyclic dynamic parameters obtained by the measurement. For example, if compliance C, the correction is to reduce the measurement result at a constant rate in summer, and the correction is to increase in winter. By doing the above, the degree of diagnosis can be improved.

(6) In the above first and second embodiments, an alarm sounds when a measured value such as a current cyclic dynamic parameter is separated from the average of past measured values by a certain amount or more. Digital display).

FIG. 94 shows the control unit 389 of FIG. 93 in the liquid crystal display 390, a pulse wave detection unit 381 (not shown) is provided on the back side of the band, and a display unit 391 is provided in the dial. Here, the display portion 391 displays the difference between the average value of the present measured values of the cyclic dynamic parameters R _c , R _p , L, C and past measured values by a bar graph. Also, the dashed lines show the levels of interest. In addition, the display may be ± display as shown in the figure, or may be an absolute value display.

According to such a structure, it becomes possible to measure a cyclic dynamics parameter for every fixed time (for example, 15 minutes), and to display the measurement result, and a user can always check his or her physical condition. Conventionally, there was only a body temperature measurement method for easily knowing the state of one's body, but by attaching the device to a wrist, the body state can be accurately known at any time beyond the body temperature, which is extremely useful for busy business and the like.

In addition, as shown in FIG. 95, the indication by a guide may be substituted instead of the bar graph display. That is, the hour hand 392, the minute hand 393, and the second hand 394 shown in the same drawing are used. For example, the hour hand 392 replaces the current measurement value of the cyclic dynamics parameter, and the minute hand 393 is used. ) Is assigned the average of past measurements. The hour hand 392 and the minute hand 393 may be moved and displayed according to the values of the present measured value and the past measured value. In the illustrated case, for example, when the needle is at the point of 12 o'clock, the value becomes 0, and as the value of the cyclic dynamics parameter increases, the needle is driven clockwise. In the illustrated case, since the hour hand 392 is located at the six o'clock side of the minute hand 393, the present value of the cyclic dynamics parameter is slightly larger than the past average value. Reference numeral 395 in the figure denotes a mode setting button for switching between a mode using a normal wrist watch and a mode displaying the present measured value and the average value of the cyclic dynamic parameters described above.

In addition, other instructions may be provided in addition to the hour hand 391, the minute hand 392, and the second hand 393.

Moreover, the form similar to FIG. 96 using only one needle may be sufficient. In the figure, the same components as in FIG. 95 are assigned the same reference numerals, and the description thereof is omitted. As said aspect, the difference of the present value based on the past average value of a cyclic dynamics parameter is displayed. Therefore, the display surface 396 which is smaller than the display portion 891 is provided on the display portion 391, and the small needle 397 is provided on the display surface 396. The 12 o'clock position of the display surface 396 corresponds to the average value of the cyclic dynamics parameter in the past fixed period, and the subtractive 397 shows the current value of the cyclic dynamics parameter. By the position of the subtractive 397, the present value of the cyclic dynamics parameter based on the average value in the past is shown. That is, if the present value is above the average value in the past, the minute hand 397 rotates clockwise, and if the present value is less than the mean value in the past, the minute needle 397 rotates counterclockwise. Done.

Moreover, needless to say, even if the rotation direction of the small needle 397 is opposite to this, there is no problem. In addition, about what consists of several indexes, such as a cyclic dynamics parameter, may be provided with several lines of roughening as many as the number of indicators to display, and a display surface is provided by these indicators, and one roughening is applied to each display surface one by one. You may install it. In addition, when using it as a general wrist watch, the display surface 396 may be used for showing a date or the day of the week like a commercial wrist watch. In such a case, it is good to use the mode setting button 395 to switch between the mode of the normal watch and the mode displaying the cyclic dynamics parameter.

⑦ in place of the display of the above-mentioned circulation dynamic parameters, even with respect to the phase or amplitude of the pulse wave show the difference between the past average value, and also, the parameters R _c, R _p, a difference between the total value of the L past average value You may display it. In the above case, the smaller the values of the parameters R _c , R _p , and L, the better the physical condition, but the larger the values of the parameters C, the better the condition of the body. It is desirable to.

By doing so, the physical condition of the day can be known accurately.

(8) In each of the above-described embodiments, the physical condition judgment reference data may be the average data of the past three days, the average data of the past one week may be used, and the data on the day of good physical condition may be used as the reference data. It's okay.

In this case, it is necessary to correct the data according to the season in consideration of the above-described annual variation. In addition, since it is thought that temperature is the cause of a large annual variation, you may make it correct | amend the reference data according to temperature.

In the above-described embodiment, the four element concentrated constant model has been described, but other electrical models may be used. In addition, in a living state other than the cyclic dynamics parameter, for example, the so-called index of the pulse wave described in "Chapter 4, Section 2" and the like can also be considered.

⑩ For pulse wave measurement, after confirming that the user has stabilized himself, the input unit 384 may be used to inform the device of this effect. In this case, it is helpful to determine whether or not the user is in a stable state by notifying whether the pulse wave measurement measured at the output value of the body motion detection unit 391 is appropriate.

In addition, the microcomputer 387 may always perform the detection of the stable state using the body motion detection part 391, and may detect the pulse wave only when a predetermined period is in a stable state.

Furthermore, the pulse wave and the body motion are measured over a predetermined period without waiting for a stable state, and these measured values are stored together in the memory 383. Based on the stored body motion measurement results, the user may select only the pulse wave measurement results at a point in time when the user is in a stable state for a predetermined period so as to obtain pulse wave information.

Section 2 diagnostic device using the pulse wave

<< First Example >>

The apparatus according to the present embodiment extracts the indicators indicated by the living body every regular time, and displays the moving average of the measured amount in the past few days, the measured value at the present time, and the like on a portable device such as a wrist watch. As a result, the user can grasp his or her health state from the display result and display the time course of these measurements, so that the user can also know the recent change in the health state. In addition, in the Example, LF, HF, "LF / HF", RR50, and pulse rate which were described in "Chapter 4 Section 2" are used as an index indicating a living state.

<Configuration of the device>

97 is a block diagram showing the configuration of the apparatus according to the present embodiment. In the present embodiment, the user of the device wears the wristwatch 450 shown in FIG. 98, and the device is incorporated in the wristwatch 450. In addition, the said aspect which incorporated the pressure type pulse wave detection part was demonstrated in "Chapter 2 Section 1 Clause 4."

Next, in FIG. 97, the central part which controls each circuit in the CPU 440 apparatus WHEREIN: The function is demonstrated as the term of the operation mentioned later. The ROM 441 stores control programs, control data, and the like for the CPU 440. The temporary storage memory 442 is a kind of RAM and is used as a work area when the CPU 440 performs an operation. The pulse wave detection unit 443 always measures the pulse wave in the sinus part of the user's fingertip, and outputs the measurement result as an analog signal. The A / D converter 444 quantizes the analog signal, converts it into a digital signal, and outputs the digital signal. The data memory 445 is a nonvolatile memory composed of battery-backed RAM and the like. The data of the pulse wave inserted in the A / D converter 444 by the CPU 440 or the LF, HF, and LF / HF '', RR50, and pulse rate are stored. The clock circuit 446 has a mechanism for intervening the CPU 440 in addition to generating a time for display by the wristwatch 450. That is, according to the designation of the CPU 440, an intervention signal is sent to the CPU 440 when a specific time is detected or when a predetermined time has elapsed. The operation unit 447 is composed of buttons provided on the wristwatch 450, and detects that these buttons are pressed and outputs the types of the buttons. The display 448 is a display device corresponding to various display units attached to the wrist watch. The display control circuit 449 accepts the generated display information by the CPU 440 and assembles display data for sending from the display information to the display 448.

The I / O interface 500 is described in "Chapter 5, Section 3" as a means for communicating between devices installed outside the apparatus. By using the I / O interface 500, for example, information of a living state such as LF, HF, &quot; LF / HF &quot;, RR50, and pulse rate of the past predetermined number of days stored in the data memory 445 can be transferred to an external device. Can transmit

The acceleration sensor 501 is an example of body motion detecting means capable of capturing the body motion of the user of this apparatus. The A / D converter 502 has the same configuration as the A / D converter 444, and converts the output of the acceleration sensor 501 into a digital signal and sends it to the bus.

The apparatus of this embodiment is equipped with two modes, "normal use mode" normally used as a clock, and "interpretation mode" which displays the pulse wave analysis result.

In FIG. 98, reference numeral 451 denotes a main body of a wrist watch, and a time display section 452 and a figure display section 453 are provided on an upper surface portion. In addition, the time alignment button 24, the mode switch button 25, and the display switch button 26 are attached to the right side part. The time display unit 452 always displays the current time sent from the CPU 440. In the normal use mode, the figure display section 453 displays the date and the like, and the analysis result of the pulse wave is graphically displayed in the analysis mode. The time alignment button 454 is used for time adjustment, alarm setting, and so on in the so-called crown. The mode switching button 455 is a button for switching between the normal use mode and the analysis mode, and the normal use mode and the analysis mode are alternately switched each time the button is pressed. In addition, it is initialized to a normal use mode at the time of power supply. The display switching button 456 is used to switch the display contents on the figure display section 453 in the analysis mode.

And the figure display part 453 can graph and display any one of the pulse wave analysis results shown below.

① Moving average and present value of `` LF / HF ''

② Moving average and present value of LF and HF

③ Moving average and present value of RR50

④ Moving average and present value of pulse rate

⑤ Change of "LF / HF" in past predetermined period

⑥ LF and HF in the past

⑦ Change of RR50 in the past predetermined period

⑧ Change of pulse rate in the past predetermined period

Each time the display switching button 456 is pressed, the analysis results 1 to 8 are sequentially displayed on the figure display section 453. When the graph of (8) is displayed, the graph of (1) is displayed again by pressing the display switching button 456 only once.

In addition, in this embodiment, the moving average value is calculated based on the measured amount for one week in the past, and the "predetermined period" of 4 to 8 is also one week.

<Operation of the device>

(1) pretreatment

In order to measure the pulse wave at intervals of a predetermined time (for example, two hours), the CPU 440 clocks to generate an intervention signal, for example, "at two o'clock in the morning at two o'clock" when the power is turned on. Instruct the circuit 446.

(2) Pulse wave measurement and analysis

For example, when the clock circuit 446 generates an intervention signal to the CPU 440 at 2 pm, the CPU 440 first reads the output of the acceleration sensor 501 through the A / D converter 502. It is stored in the temporary storage memory 442. Then, it is determined whether the output value of the acceleration sensor 501 indicates that the user is in a stable state. In the unlikely event that the pulse wave measurement is inaccurate unless it is in a stable state, the CPU 440 displays this effect on the display 448 and notifies the user. After that, when the user recognizes that the user is in a stable state suitable for measuring the pulse wave, the CPU 440 performs the pulse wave blowing processing for only a predetermined time (for example, 30 seconds). Therefore, the CPU 440 first instructs the clock circuit 446 to monitor time for 30 seconds.

By the way, the pulse wave detection part 443 is measuring the pulse wave of the artery part of a user's finger joint at all times, and the said measurement result is converted into a digital signal by the A / D converter 444, and is output. Thus, the CPU 440 reads the digital signal and stores it in the data memory 445 together with the current time (2 pm) read by the clock circuit 446. The CPU 440 repeats the blow-in process, after which, if 30 seconds elapse, and the intervention signal is sent from the clock circuit 446, the process stops. By the abnormal processing, the waveform of the pulse wave over 30 seconds is stored in the data memory 445.

Next, the CPU 440 analyzes the waveform of the pulse wave stored in the data memory 446 to calculate LF, HF, "LF / LH", and RR50. In addition, the detailed description of the calculation method of these indicators was demonstrated in "Chapter 4 Section 2". In addition, the CPU 440 converts the number of peaks of the pulse wave observed within one measurement period into one minute to set the pulse rate. Finally, these values are stored in the data memory 445 together with the pulse wave measurement time (2 pm).

(3) display of measurement results

When the user presses the mode switch button 455, the mode is switched from the normal use mode to the analysis mode.

The operation unit 447 receives a notification that the mode switching button 455 has been pressed, and the CPU 440 instructs the display control unit circuit 449 to erase the figure display unit 453. This displays the day of the week on the figure display section 453.

① Extraction of present value of living body

Subsequently, the CPU 440 performs pulse wave measurement and biometric analysis in the same procedure as the processing of "(2) Measurement and Analysis of Pulse Wave" described above. 445), and analyzes the waveform of the pulse wave taken in, and calculates the values of LF, HF, LF / HF, RR50, and pulse rate at the "current time point." These values are stored in the temporary storage memory 442.

② Interpolation

Next, the CPU 440 obtains the current time from the clock circuit 446 to obtain pulse wave measurement time before and after the current time. As described above, since the pulse wave measurement time is set to be 2 hours from 0 am, for example, when the current time is 1:30 pm, the pulse wave measurement times before and after become at noon and 2:00 pm.

Next, for example, the values of LF, HF, "LF / HF", RR50, and pulse rate measured at noon and 2:00 pm are read in the data memory 445 for each day of the past one week. And LF, HF,

The values at the present time are estimated by interpolating the values at noon and 2:00 pm for each of "LF / HF", RR50, and pulse rate. The CPU 440 calculates the average value for one week for each of the LF, HF, "LF / HF", RR50, and pulse rate.

In addition, depending on the interpolation method, a wider range of information is required than immediately before and after, but in such a case, necessary information is read from the appropriate data memory 445 and interpolated.

③ Graph display

First, a graph as shown in FIG. 99 is created from the moving average value of "LF / HF" and the present value of "LF / HF" at the present time (1:30 pm). When the display information of the graph is sent to the display control circuit 449, the average value and the present value of "LF / HF" in the past week are displayed on the figure display section 453 of the display 448 (the first screen). ).

Thereafter, each time the user presses the display switching button 456, the CPU 440 creates display information for the graph described below, and displays it in the figure display section 453 in order.

(a) First press (second screen).

As shown in FIG. 100, the average and present values of the past one week of the LF and the average and present values between the past values of the HF are displayed in a bar graph.

(b) The second pressurization (the third screen)

As shown in FIG. 101, the average value and the present value of the past one week of the RR50 are displayed in a bar graph.

(c) The third pressurization (the fourth screen)

As shown in Fig. 102, the average value and the present value of the past one week of the pulse rate are displayed in a bar graph.

(d) The fourth pressurization (the fifth screen)

Based on the value of "LF / HF" for the past week, the tangential graph shown in FIG. 103 is displayed.

(e) The fifth pressurization (the sixth screen)

Based on the values of LF and HF for the past week, two tangential graphs shown in FIG. 104 are displayed.

(f) 6th press (the 7th screen)

Based on the value of RR50 for the past one week, a broken line graph similar to that of FIG. 103 is displayed. In addition, "RR50" is displayed instead of "LF / HF" in the same figure.

(g) Press (the eighth screen)

Based on the pulse rate values for the past week, a broken line graph similar to that of FIG. 103 is displayed. In addition, it becomes "pulse rate" instead of "LF / HF".

(h) The eighth pressurization (the ninth screen)

The first bar graph shown in FIG. 99 is displayed again. Thereafter, when the display switching button 456 is pressed, the same graph is displayed every eight screens.

After that, when the user presses the mode switching button 455 again, the mode is switched to the normal use mode. Then, the CPU 440 instructs the display control circuit 449 to erase the figure display portion 453, and then obtains and corrects the date and the day of the week, and displays them on the figure display 453. FIG. When the mode switch button 455 is pressed in the analysis mode, the graph display is interrupted, and the mode is shifted to the normal use mode, and the date and day are displayed.

As described above, according to the present embodiment, since the device is incorporated in the wrist watch attached to the daily body, the subject can always easily check the state of health. In other words, by displaying the indicator at the present time and the average value of the present time and the same time point in the past predetermined period, the state at the present time is remarkable in the state of the past predetermined period after taking into account the periodic fluctuations of the biological state. You can see at a glance whether you are deviating or not. In addition, it is possible to check the recent change in the state of health at a glance by displaying the trend of the indicator in the past for a predetermined period.

Therefore, when a subject confirms regularly or irregularly and the state changes, a habit of consulting with a specialized institution such as a doctor is put on the body, and efficient health management can be performed.

<< Second Embodiment >>

In the present embodiment, an embodiment in which the pulse wave at the fingertip is used instead of the pulse wave in the artery of the finger joint will be described.

<Configuration of the device>

The functional part of the apparatus according to the present embodiment is exactly the same as that of the first embodiment. However, the structures of the pulse wave detecting means and the wrist watch in this embodiment are different from those in the first embodiment. That is, in the first embodiment and the present embodiment, the configuration and structure of the pulse wave detection unit 443 in FIG. 97 are different.

In this embodiment, the pressurized pulse wave detection unit described in "Chapter 2, Section 5" is used, and FIG. 105 shows the mechanical configuration of the wristwatch according to the present embodiment. In the figure, reference numeral 460 denotes a main body of a wrist watch, and an LCD display portion 461, a finger contact portion 51, a time alignment button 462, an analysis button 463, and a display switching button 464 are provided. .

The LCD display portion 461 corresponds to the display 448 in FIG. 97 and includes a visual display portion 461a and a figure display portion 461b. The time display portion 461a displays the current time in both the normal use mode and the analysis mode. That is, the time display continues in the analysis mode, and the user can know the current time even during the analysis. On the other hand, the figure display part 461b displays the date and the day of the week in the normal use mode, and the message and the information for measurement and analysis in the analysis mode.

The time alignment button 462 is a button used for the time of the watch and other setting operations, and the analysis mode button 463 is used for setting / starting the operation of the pulse wave analysis function. In addition, the display switching button 464 plays the same role as the display switching button 456 in the first embodiment, and can switch the display contents on the figure display section 461b in the analysis mode.

In this embodiment, the pressing force to be applied to the finger contact 51 is set to any one of <67, 83, 100, 117, 133> g / cm ² in advance, and in the following description, the pressing force is optimal for detecting the pulse wave. It is set to the phosphorus pressure, and shall be set to the pressure at 83 g / cm <^2> below. In addition, since the adjustment of the pressing force is caused by the pressurization of the user's finger, the measurement becomes difficult unless the corresponding allowable range is set for each pressing force. Therefore, an allowable range of "± 2 g / cm <^2>" is set with respect to each said pressing force.

In addition, the above-described CPU 440 controls message display for guiding the analysis procedure to the user, guide graphic data for allowing the user to press the finger contact 51 with an appropriate pressing force, and the like. The display control circuit 449 creates display data from the display information from these display information and outputs it to the figure display unit 461b.

On the other hand, as shown in FIG. 106, the pressure signal P, which is the output of the strain gauge 57, is converted into a digital signal by the A / D converter 465 and sent to the CPU 440.

<Operation of the device>

(1) pretreatment

In order to perform pulse wave measurement every day at a predetermined time, the clock circuit is configured to generate an intervention signal at, for example, "two hours from 8 am to 10 pm" by turning on the power. Indicated by (446). In this embodiment, in order to measure the pulse wave by pressing the user's finger, the night time zone is not set as the measurement time.

(2) pulse wave measurement

In order to perform pulse wave measurement at predetermined time intervals (for example, 2 hours), the clock circuit is configured to generate an intervention signal at an interval of, for example, "two hours at 0 AM" at the time of turning on the power. 446 is indicated.

① Intake of waveform of pulse wave

For example, when the clock circuit 446 generates an intervention signal to the CPU 440 at 2 pm, the CPU 440 performs the pulse wave intake processing only for a predetermined time as in the first embodiment.

First, the CPU 440 notifies the user that the pulse wave measurement time has come. Then, the CPU 440 causes the figure display portion 461b to display a message such as "measuring a mac". When the user who saw this presses the analysis mode button 463, the apparatus becomes operable. In addition, when the analysis mode button 463 is pressed again, the watch returns to the normal operation, and when the analysis mode button 463 is pressed again during the analysis, the analysis operation is interrupted and returns to the normal operation again. .

Next, when notification of pressurization of the analysis mode button 463 is made by the operation unit 447, the CPU 440 causes the figure display unit 461b to display the message "Pressing to 2". When the user who saw this puts a finger on the finger contact part 51, the resistance value of the strain gauge 57 incorporated in the wrist watch changes. The CPU 440 detects the pressure change at the output of the A / D converter 465, and changes the figure display portion 461b to a graph display as shown in Fig. 107 (a). Here, the marks ml to m5 of the inverted triangle in the same figure mean measurement points corresponding to pressing forces <67, 83, 100, 117, 133> g / cm ² (described above) in order from the left.

Then, when the user presses the finger gradually by increasing the pressure contact force, the CPU 440 based on the read pressure, and based on the actual pressure, the code PM (Fig. 107A) as many as the number corresponding to the magnitude of the actual pressing force. The bar-shaped mark as shown in () is displayed from the left side sequentially. The user presses the second finger on the finger contact 51 so that the mark PM is displayed to the position of the mark m2 indicating the second measurement point while referring to the rod-shaped mark (state of FIG. 107B).

In the state where mark PM is displayed to the position of mark m2, it shows that the present pressing force exists in the measurement range (83 +/- 2g / cm <^2> ) of a 2nd measuring point. On the other hand, when the pressing force slightly exceeds the measurement allowable range, the mark PM before and after the mark PM flickers and blinks.

If it is detected that the pressing force is within the measurement allowable range for a short time, the CPU 440 terminates the graph display of the figure display section 461b, and instead displays the message "Stop as is".

In addition, the user moves the finger during the short period. When the pressing force is out of the measurement allowable range, a message "Please try again" is displayed on the figure display part 461b. Next, since the display of the figure display section 461b is switched back to the above graph display, the user adjusts the pressing force so that the mark PM is displayed again at the position of the mark m2.

In this way, when the pressing force becomes substantially constant, pulse wave measurement is performed one after another. Since the operation of the pulse wave measurement is the same as that of the first embodiment, the CPU 440 sets a predetermined time in the clock circuit 446, and only during this period, the A / D converter 444 receives the pulse wave signal from the data memory ( 445).

(3) Analysis of pulse wave waveform

Next, as in the first embodiment, the CPU 440 sequentially calculates LF, HF, "LF / HF", RR50, and pulse rate, and stores them in the data memory 445 together with the measurement time.

In this way, the biological state is periodically measured.

(4) display of measurement results

Then, when the user presses the analysis mode button 463 to know the current state, the CPU 440 controls the figure display unit 461b. In this case, since the timing of the button press does not correspond to the time of the periodic measurement of the pulse wave, the CPU 440 may confirm that the press of the button is at the user's will.

① Extraction of present value of living body

The CPU 440 executes the above-described "(2) pulse wave measurement" and "(3) pulse wave waveform analysis" processing. That is, the pulse wave of the fingertip for a predetermined time is put into the data memory 445, and the values of LF, HF, "LF / HF", RR50, and pulse rate at the present time are calculated by the waveform analysis of the pulse wave.

② Interpolation

Subsequently, as in the first embodiment, the CPU 440 calculates a living state at the same time as the current time point by interpolating past biometric values, and calculates a moving average for each living state.

③ Graph display

By the same procedure as in the first embodiment, as the user presses the display switching button 464, the graphs of the living states shown in FIGS. 99 to 104 are displayed on the figure display section 461b.

As described above, according to each of the above embodiments, it is possible to display and inspect the analysis result of one's health state from time to time at the will of the user. In addition, since the moving average of the state between the present state and the past measured value is displayed, it is possible to periodically grasp how the state of health at the present time is compared with the usual. In addition, since the state of the living body can be displayed, the user can also know how the recent state of health of the person has changed.

<< modification >>

(1) In the first embodiment, the apparatus may be combined with an accessory or glasses.

(2) The graph display shown in Figs. 99 to 104 may also be performed at the regular measurement time of the pulse wave.

(3) In each of the above embodiments, the analysis results are displayed graphically from the viewpoint of directly appealing to the time, but for example, numerical display may be used.

(4) The maximum and minimum values of the living state of the past one week may be respectively detected, and an alarm by a buzzer or the like may be issued when the current value is larger or smaller than their values, or an abnormal display may be performed. In this way, attention can be drawn when the user's state of health deviates significantly from the recent state of health.

In addition, in accordance with the diagnostic apparatus of claim 1, the present state of the living body is in a state where the physical state is in a good state when the present value of the biological state is smaller than or equal to the maximum value or greater than or equal to the minimum value in the past one week. In that case, the effect may be notified. In this way, when the state of good physical condition is notified, the user notified can be mentally afforded in the same manner as described above, so that there is an effect that contributes to the improvement of the QOL.

⑤ day and night living in the living state tea. Thus, the maximum value, the minimum value in the day time zone, the maximum value and the minimum value in the night time zone may be obtained separately, and the current value may be compared with the value in each time zone depending on whether the present time zone is the day time zone or the night time zone. In this way, it is possible to grasp the state of health more accurately.

(6) In the above embodiment, after the mode switching button 455 is pressed, the pulse wave is measured to calculate the "current" living state. As a method of replacing this, a pulse wave waveform is always put in the data memory 445, and a waveform of a predetermined time (for example, 30 seconds) is always stored in the data memory 445. When the mode switching button 455 is pressed, the living body state is calculated from the waveform of the stored pulse wave without measuring the pulse wave next time. In this way, the time from when a user presses a button until the result is displayed can be significantly shortened.

⑦ If the user perceives an abnormality, the result of spectrum analysis of RR interval variation may be displayed in a graph so that a doctor or the like can diagnose from various points of view.

In each of the above embodiments, the user switches the information displayed on the figure display section 453 by pressing the display switching button 456. However, this may be automated and displayed in order after a predetermined time (for example, 5 seconds). In this way, it is possible to eliminate the trouble of manipulating the buttons every time the separate information is viewed.

(9) The pulse wave may be measured by the user after confirming that the user is in a stable state by using the operation unit 447. In this case, the pulse wave determined by the output value of the acceleration sensor 501 may be used. Displaying the appropriateness of the measurement on the display 448 is useful for determining whether the user is in a stable state.

In addition, the CPU 440 may always detect the stable state using the acceleration sensor 501, and may detect the pulse wave only when the predetermined state is stable.

In addition, the pulse wave measurement and the physical condition are measured over a predetermined period without waiting for a stable state, and these measured values are stored together in the data memory 445. Based on the stored body motion measurement results, the user may select only the pulse wave measurement results at the point in time when the user is in a stable state for only a predetermined period of time to obtain pulse wave information.

As described in the above-described apparatus, for FIGS. 99 to 102 (ie, LF / HF, LF, HF, RR50, and pulse rate indicators), the notification using the clock hand as shown in FIG. 95 instead of the bar graph display is also used. You can do

Section 2 control of living state

In the above section, various apparatuses for controlling the living state by drug administration, perfume discharge, and the like will be described. These devices diagnose the living state from the pulse wave analysis result, advance it further, and control the living state based on the obtained diagnosis result.

By the way, in the medication control apparatus and chemical | medical agent discharge apparatus demonstrated below, the micro pump is used as a common drive means in drug administration or discharge of a fragrance | flavor. Thus, prior to the description of these devices, a description will first be given of the microphone pump and the driving unit for driving the same.

Claim 1 micro pump

(1) structure of micro pump

108 is a cross-sectional view of the micro pump 501. The micro pump 501 has a sandwich structure of the substrate 502, the thin film plate 503, and the surface plate 504.

The substrate 502 is made of, for example, a glass substrate having a thickness of about 1 mm, and an input port 505 and an output port 506 are provided. These tubes 505T and 506T are joined by an adhesive so that the liquid is not counted.

The thin film plate 503 is made of, for example, a Si substrate having a thickness of about 0.3 mm, and an inlet valve 507 and an outlet valve 508 are formed by an etching method, and a diaphragm between these valves ( 509 is formed. In addition, a pump chamber 522 below the diaphragm 509 and a pump flow path system connected thereto are formed. On the upper part of the diaphragm 509, the voltage element 526 of the piezo disk is bonded as a driving means.

The inlet valve 507 is formed to cover the substrate 502, and a valve body 516 protrudes downward to surround the through hole 518 while a through hole 518 is formed in the center of the flat portion. ) Is formed. The valve body 516 has a tip portion extending to the substrate 502, and a chamber 517 is formed by the side surface of the inlet valve 507 and the valve body 516. The seal 517 is through the input port 505 through a flow path not shown. On the other hand, the outlet valve 508 is composed of a cap-shaped valve body 525 so as to cover the inlet of the output port 506.

The surface plate 504 which consists of the glass substrate similar to the board | substrate 502 on the thin film plate 503 is bonded by the anodic bonding method, and the surface plate 504 upper wall of the some flow path of the said pump flow path system is carried out. This is composed. A window 528 is formed at a place corresponding to the diaphragm 509 of the surface plate 504. The piezoelectric element 526 is bonded to the surface of the diaphragm 509 exposed through the window 528. The thickness of the surface plate 504 is about 1 mm.

Next, the operation detection switch 550 will be described. The operation detection switch 550 is installed to detect the behavior of the partition wall of the outlet valve 508, and includes a protrusion 551 protruding from the upper portion of the partition wall and an electrode adhered to the surface of the protrusion 551. A plate 552 and a back electrode plate 553 bonded to the lower portion of the surface plate 504 so as to face the electrode plate 552.

In addition, as will be described later, the output valves of the oscillation circuit 564 are applied to the electrode plates 552, 553 through the capacitor C and the resistor R shown in FIG. 109. As the electrode plates 552, 553, for example, Pt-Ir, W, Ta, Ni, Pt, Pd, Mo, Ti uses contact materials such as polycrystalline Si, WSi, CP1, CP2, and the like.

(2) drive unit structure

109 shows the configuration of a drive unit for driving the above-described micro pump 501. In the same figure, the whole circuit shown with the code | symbol 500 (600) comprises the dosage part or fragrance discharge part in the apparatus mentioned later.

In the figure, 501 is the micropump described above, the input pump 505 is press-fitted to the tank 561 via the tuner 505T, and the output port 506 is connected to the tuner 506T.

Tuner 506T is connected to medication needle 562 as shown when the device is used for medication. In addition, when the apparatus is used for perfume discharge, the injection needle 562 is not attached, and the tip of the tuner 506T is disposed close to the injection hole for perfume discharge (described later).

The drive circuit 563 generates a fluctuation pulse of a predetermined level (about 100 V) by being given a drive command from an external device such as a microcomputer, and supplies it to the piezoelectric element 526 which is a driving means of the micropump 501.

The oscillation circuit 564 generates a plurality of pulses whose period is shorter than the pulse width of the drive circuit, and applies them to the operation detection switch 550 of the micropump 501 through the capacitor C and the resistor R. Here, the operation detection switch 550 is configured to be turned on by a predetermined time interval each time the liquid is discharged from the output port 506 of the micropump 501. Therefore, when the micropump 501 is operating normally, the drive pulse is applied to the micropump 501, and the voltage across the operation detection switch 550 is increased whenever the liquid is discharged. Will be lowered.

The abnormality detection circuit 565 rectifies the voltages at both ends of the operation detection switch 550, and outputs an abnormality detection signal when the level of the voltage obtained by the rectification does not change in time corresponding to the fluctuation pulse. The abnormality detection signal is sent to a microcomputer or the like which controls the micropump.

(3) the operation of the micro pump 501 and the driving unit

First, the drive circuit 563 generates a drive pulse of a predetermined level (about 100V) by giving a drive command to a microcomputer or the like installed outside the micropump, and supplies it to the piezoelectric element 526 of the micropump 501. . When the driving pulse is applied, the piezoelectric element 526 is deformed as shown in FIG. 110, and the diaphragm 509 is depressed. As a result, the pressure in the pump chamber 522 rises, the partition of the output valve 508 lifts, and the valve main body 525 falls from the board | substrate 502. As shown in FIG. Then, the liquid in the pump chamber 522 (a potion in case of medicine, a perfume in case of chemical ejection) flows out to the output port 506 through a gap between the valve body 525 and the substrate 502, and the tuner 506T (if it is a dose, it is also ejected through the injection needle 562).

When the driving pulse falls, as shown in FIG. 111, since the diaphragm 509 tries to return to the original state in which the diaphragm 509 is recessed inward, negative pressure is generated in the pump chamber 522. For this reason, when the valve main body 525 of the outlet valve 508 is pressed against the board | substrate 502, the output port 506 is clogged, On the contrary, as for an input valve, a partition wall is lifted upwards and accordingly, a valve main body ( 516 falls off the substrate 502. As a result, liquid flows from the input port 505 and is absorbed into the pump chamber 522 through the gap between the valve body 516 and the substrate 502 and the through hole 518, after which the drive valve is applied. Each time, the discharge and suction of the same liquid as above are repeated.

By the way, while the micropump 501 is operating, the voltage across the operation detection switch 550 is monitored by the abnormality detection circuit 565. If the liquid is not discharged smoothly due to blockage of the tuner, blockage of the needle, or the like, the relationship between the timing of generating the drive pulse and the timing at which the operation detection switch 550 is turned on is shifted from the normal one. The abnormality detection circuit 565 outputs an abnormality detection signal to the microcomputer or the like when the misalignment is detected.

Section 2 dosing control device

Patients with hypertension, heart failure, and diseases of the circulatory system often have unstable circulatory behavior. Therefore, it is necessary to monitor their condition at all times so as not to enter a dangerous state. As factors that influence the behavior of the circulatory system, α receptors, β receptors, calcium receptors, ACE receptors, and the like are known. Is controlled to stabilize the behavior of the patient's circulatory dynamics.

However, since the administration of the circulatory agonist as described above must be performed in a timely manner when the solution of the patient is released from the normal state, the doctor or the like must constantly monitor the solution of the patient, which requires a great effort. . In addition, patients with severe symptoms have to administer circulatory agonists to the extent that they are not always excessive, so they should not lie in the hospital bed just for receiving the administration.

This apparatus was developed on the background of the above, and aims to stabilize the circulating dynamics of the patient's blood pressure by monitoring the circulating dynamics of the patient and taking necessary medications based on the results. Therefore, it is judged whether or not the patient is in a state of needing medication, and the circulating agonist required among the α blocker and the β blocker is administered to the patient in accordance with the determination result. In addition, the circulatory agonists referred to herein include drugs or hormonal systems that directly or indirectly affect the circulatory system.

<< First Example >>

<Overview of the device>

The dosage control device according to the present embodiment uses the above-described LF, HF, "LF / HF", and RR50 as a living body state for viewing the pulse wave change, and administers the excitement and calm state of the living bodies obtained from these doses. It is used for control.

That is, the pulse wave of the patient is periodically measured to calculate LF, HF, "LF / HF", and RR50. If the patient is in a calm state in these living states, α blocker is administered to the patient to determine the excited state of the α receptor. On the contrary, when in an excited state, β blocker is administered to calm the excited state of the β receptor to stabilize circulatory dynamics such as blood pressure of the patient.

<Configuration of the device>

112 is a block diagram showing the configuration of the dosage control device 700 according to the present embodiment. The memory 701 is a nonvolatile memory constituted by a battery-backed RAM or the like, and is used for temporary storage of control data when the microcomputer 705 controls each part in the medication control device 700. In the predetermined memory area 7 of the memory 701, a value that is desirable for a patient receiving medication (at a time when the patient is healthy, at least one of LF, HF, "LF / HF", and RR50) Or the average value of a plurality of subjects).

In addition, the medication control device 700 not only performs the medication control using the fixed biological state of this content, but also extracts the biological state from the pulse wave obtained from the patient, and performs the medication control using the biological state prepared as described above. It is configured to be. In the specific memory area 7 of the memory 701, the biometric state created as described above is stored.

The input unit 702 is an input means provided for inputting a command to the microcomputer 705, and is configured by, for example, a keyboard.

The output unit 703, in the output means constituted by a printer, a display device, or the like, performs control of the microcomputer 705 to store the living state obtained from the patient, record medication, display the pulse wave, and the like.

The waveform extraction storage unit 704 inserts a pulse wave signal output from the pulse wave detection unit 710 under the control of the microcomputer 705, and extracts and stores the pulse wave for one night from the input signal. In addition, the detailed description of the waveform extractor memory | storage part 704 is described in "Chapter 3 Section 1 Clause 2."

The microcomputer 705 controls each part in the apparatus 700 in accordance with a command input through the input unit 702. The microcomputer 705 has a built-in clock circuit and performs the following processing each time a predetermined time elapses in the operation mode in which medication control is performed.

In the operation mode in which the clock circuit is incorporated and the dosage control is performed, the following processing is performed each time a predetermined time elapses.

① Control of taking in the pulse wave signal by the waveform extraction storage unit 704 and the extraction process of the pulse wave for one night

Whenever the peak point of the pulse wave is detected by the waveform extraction storage unit 704, the peak information is stored in the internal memory.

② Frequency analysis of pulse wave and judgment of patient's condition

On the basis of the peak information, waveform values of pulse waves of continuous pulses are read by the waveform extraction and storage unit 704 to calculate a living state, and the obtained living state is compared with a preferable living state stored in the memory 701 in advance. In this case, it is determined whether or not the patient is in a calm state.

③ Dosing Control

On the basis of the above determination result, when the patient is in an excited state and the blood pressure value of the patient is a value requiring medication, a beta blocker is administered by supplying a driving command to the second medication unit 600. On the other hand, when the patient is in a calm state and the blood pressure value of the patient is a value requiring a myrrh, a driving command is supplied to the first dosage unit 500 to be administered to the α blocker patient.

On the other hand, the first dosage unit 500 and the second dosage unit 600 is composed of the micro-pump described in the paragraph "1" and its drive unit, the first dosage unit 500 is for administering α blocker The second dosage unit 600 is for administering β blocker. In addition, the tank 561 shown in FIG. 109 is satisfied with the drug of (alpha) blocker or (beta) blocker.

The I / O interface 706 is described in "Chapter 5, Section 3" as a means for communicating with devices installed outside the apparatus. By using the I / O interface 706, for example, information such as a living state stored in the memory 701 may be transmitted to an external device.

The body motion detection unit 707 is an example of body motion detection means for capturing the body motion of the user of the apparatus, converts the measured body motion value into a digital signal and sends it to the microcomputer 705.

<Operation of the device>

(1) Dosing Control Using a Fixed Biometric State

In the case where the user of the present device does not particularly designate the mode, the patient's medication control is performed based on the fixed living state previously stored in the medication control device 700 and the memory 701. When the tank 561 is replaced at the time of dosing, the user inputs a command indicating the meaning from the input unit 702, and the microcomputer 705 accepts the command so that the initial value of the remaining amount of the α blocker or β blocker (tank) The equivalent of the filling capacity) is written into the memory 701.

As described above, the microcomputer 705 has a built-in clock circuit, and at this time, a timer intervention signal is generated whenever time clocking is performed by the clock circuit. By the generation of the timer intervention signal, the microcomputer 705 executes the timer intervention routine shown in FIG.

First, the flow advances to step S721, and the microcomputer 705 executes processing for extracting the waveform and its peak information. In addition, the detail was demonstrated in "Chapter 3 Section 1". Here, in the measurement of the pulse wave, the microcomputer 705 reads the output of the body motion detector 707 and stores it in the memory 701. Then, it is determined whether the output value of the body motion detecting unit 707 indicates that the user is in a stable state. Since the measurement of the pulse wave may be inaccurate unless it is in a stable state, the microcomputer 705 uses the output unit 703 to notify the user of the above effect. Then, after the user recognizes the stable state suitable for the pulse wave measurement, the pulse wave is measured.

Next, the flow advances to step S722, and the microcomputer 705 executes waveform reading processing and pulse wave analysis processing. That is, the microcomputer 705 analyzes the waveform of the pulse wave stored in the memory 701 and calculates LF, HF, "LF / HF", and RR50. In addition, the detail was demonstrated in "Chapter 3 Section 1" and "Chapter 4 Section 2".

In step S723, the microcomputer 705 stores the biometric state obtained in step S722 in the memory 701 at the same time as the information indicating the current date and time.

Next, the process proceeds to step 724, referring to the time (described later) and the output of the clock circuit that performed the previous dose stored in the memory 701, and whether or not the predetermined time has elapsed from the time of the previous dose. Determine. If the determination result is "Yes", the flow advances to step S725, and if "No", the timer intervention routine ends. This judgment is made in order to prevent the inconvenience of continuously administering the same type of blocker before the effect of the dosage is shown.

Subsequently, the flow advances to step S725 to compare the biomeasurement measured now with the biomechanism previously stored in the memory 701. As a result of the comparison, if it is in the calm state beyond the predetermined range, the flow advances to step S726. Then, the pulse wave detection unit 710 measures the blood pressure pulse wave of the patient to obtain a blood pressure value, and when the blood pressure value is a value that requires administration, the driving instruction is given over a predetermined number of times so as to administer the α blocker. Send to section 500. On the other hand, if the state of excitement exceeds a predetermined range, the flow proceeds to step S727. In step S726, when the blood pressure value of the patient is a value requiring medication, β blocker is administered to a predetermined number of times. The driving instruction is sent to the second dosage unit 600. On the other hand, if the living body state does not match any of the above and is in the normal state, the timer intervention routine ends.

When a drive command is generated by the microcomputer 705, the 1st dosage part 500 or the 2nd dosage part 600 which accepted this is respectively via the tube 506 and the injection needle 562 shown in FIG. The appropriate blocker is administered to the patient. At that time, the microcomputer 705 receives the abnormality detection signal at these dosage units, causes the output unit 703 to display an alarm, and prompts the user to replace the injection needle 562.

When the steps S726 and S727 are completed, the process proceeds to step S728 and the current dose is calculated based on the number of times the drive command is generated, and the dose and the type of the blocker administered this time (α blocker or β blocker). ) And the time of administration are recorded in the memory 701 as medication memory information. In this way, the medication storage information recorded in the memory 701 can be output from the output unit 703 by the command input from the input unit 702. The doctor can diagnose the change of the patient's solution and the like with reference to the medication memory information. In step S708, the remaining amount corresponding to the blocker which performed this administration is read out from the memory 701, and the result of having controlled this dose in the remaining amount is written into the memory 701 as the remaining amount. Here, when the remaining amount becomes less than or equal to the predetermined value, the microcomputer 705 sends a warning output command to the output unit 703. The output unit 703 prompts the user to replace the tank 561 by an alarm display or the like. In this way, the tank 561 can be replaced before the medicine disappears.

The timer intervention routine ends by the above, and after a fixed time has elapsed, the timer intervention routine is executed again.

(2) pattern memory / automatic operation mode

The user can set the pattern storage / automatic driving mode as the operation mode by the command input at the input unit 702. As the operation mode, a living body state can be created based on the pulse wave obtained from the patient, and then medication control can be performed using the living body state thus created. The operation in the above operation mode will be described below.

In initiating the dosage control in the operating mode, it is necessary to obtain a living state. The doctor inputs, to the input unit 702, an instruction to create a living body state when the patient enters a state requiring the α blocker or the β blocker. As a result, the pattern storage routine shown in FIG. 114 is executed by the microcomputer 705.

First, the flow advances to step S731 to perform each process of waveform extraction and peak detection. Next, the flow advances to step S732 to perform extraction processing of the pulse wave at the predetermined time and analysis of the waveform of the pulse wave to calculate a living state. Subsequently, the process proceeds to step S733 and the biometric state obtained in step S732 is written into the memory 701. Since the processing contents of these steps are the same as those in step S721, step S722 and step S723 in the timer intervention routine (Fig. 113), detailed description thereof will be omitted.

After the living body state is created in the memory 701 in this manner, the input unit 702 inputs a command for starting the medication control. As a result, the timer intervention routine is executed at regular time intervals as described above. In this case, however, the medication control is performed based on the living body state obtained in the patient as described above, instead of the living state of the fixed value previously stored in the memory 701.

<< Second Embodiment >>

The apparatus according to the present embodiment is configured to divide the dosage control device into a portable portion and a fixed portion, and is intended to organize a portable device.

<Configuration of the device>

115 shows the configuration of the dosage control device according to the present embodiment. In the figure, 720 denotes a fixed dosage control device used to be fixed to the side of a hospital bed, etc., 730 is a portable dosage control device used while being carried to a patient, and each of these devices is the dosage shown in FIG. 112. It has a configuration similar to the control device 700. Therefore, in each of these apparatuses 720 and 730, the parts corresponding to the respective parts of the dosage control device 700 are denoted by the same reference numerals, and the description thereof is omitted, hereinafter, only portions different from the dosage control device 700 will be omitted. Explain.

The fixed dosage control device 720 and the portable dosage control device 730 are provided with an I / O interface 706 (described above) for the respective microcomputers 705 to communicate with each other. As described above, the I / O interface is provided with a mechanism for assigning identification numbers to various types of communication information. Therefore, according to this embodiment, when the communication is performed wirelessly, the fixed dosage control device 720 can communicate with the plurality of portable dosage control devices 730 in time division.

Next, the external devices referred to as the pulse wave detection unit 710, the first dosage unit 500, and the second dosage unit 600 are fixed to the fixed dosage control device 720 by the cables 710C, 500C, and 600C, respectively. A portable medication control device 730 can be connected. In each cable 710C, 500C, and 600C, a signal line and an electric supply line are received, and a signal transmission and reception between the dosage control device and each external device is performed through the signal line, and power is supplied through the electric supply line. .

The portable dosage control device 730 has a battery (not shown) that is charged through the charging terminal 708d to supply power from the battery to each part of the device, and to each external device through each electric supply line of each cable. It has an electricity supply control part 708b which supplies to. Since the portable medication control device 730 operates the battery as a power source, the electricity supply control by the electricity supply control unit 708b is controlled by the microcomputer 705 so as to save power consumption. That is, under the control by the microcomputer 705, the electricity supply control unit 708b performs the electricity supply to each part of the apparatus only during the necessary period, such as when the timer intervention routine described above is executed, and the other period is the microcomputer ( 705 is supplied with electricity only. In addition, the electrical supply of the pulse wave detection part 710 is performed by waveform extraction only when the A / D converter in the waveform extraction storage part 704 samples a waveform value, and the 1st dosage part 500 and the 2nd dosage | use are carried out. The electricity supply to the unit 600 is performed only in the step of performing medication during the timer intervention routine. In addition, the electric supply control part 708b is provided with the voltage monitoring circuit (not shown) which outputs an alarm signal, when the output voltage of a battery becomes below a predetermined voltage value. The alarm signal is supplied to the microcomputer 705, and the microcomputer 705 which receives the alarm signal drives an alarm by driving an alarm means called a light emitting element or an alarm sound generating device (not shown at the same time).

The fixed medication control device 720 has a power source 708a, which supplies electric power to a pulse wave detection unit inside the device and outside the device based on a commercial power source. The output voltage of the power supply 708a is output to the voltage output terminal 708c, and the portable dosage control device 730 is connected to the terminal 708c by connecting the charging terminal 708d in the portable dosage control device 730 to the terminal 708c. Can charge the battery.

Each of the medication control devices 720 and 730 omits their description because the operation in the case of using each of them individually is the same as in the first embodiment.

<Operation of the device>

Since the medication control devices 720 and 730 related to the present embodiment can transmit and receive information through the I / O interface 706, the following usages are possible.

① The pulse dosage detector 710, the first dosage unit 500, the second dosage unit 600, and the portable dosage control device 730 are connected to the fixed dosage control device 720 to provide a portable dosage control device 730. While charging the battery, the fixed dosage control device 720 extracts the patient's living state and stores it in the memory 701.

(2) The microcomputer 705 reads the biometric state stored in the memory 701 of the fixed medication control device 720 and sends it to the portable medication control device 730 through the I / O interface 706. FIG. These information are written into the memory 701 via the I / O interface 706 and the microcomputer 705 in the portable medication control device 730.

(3) The pulse wave detection unit 710, the first dosage unit 500, and the second dosage unit 600 are connected to the portable dosage control device 730 to input a command for starting the dosage control, and in the first embodiment, The timer intervention routine described is periodically executed and the medication control based on the living state received by the fixed medication control device 720 is performed. In the meantime, the patient can move away from the bed of the hospital. In the meantime, when the output voltage of the battery in the portable medication control device 730 becomes less than or equal to the predetermined voltage value, an alarm signal is generated, and an alarm is generated by the microcomputer 705 that has received the alarm signal.

(4) The patient returns to the hospital bed by an alarm indication indicating that the tank 561 needs to be replaced or the alarm for a predetermined time. The portable medication control device 730 is connected to the fixed medication control device 720, and the battery of the portable medication control device 730 is charged while being stored in the memory 701 in the portable medication control device 730. A medication record (time of administration so far, type of blocker administered) is sent to the fixed medication control device 720. The medication record is added to the medication record up to that point stored in the memory 701 in the fixed medication control device 720.

In this way, the medication record information remains in the memory 701 of the fixed medication control device 720, and the doctor can output the medication record information from the output unit 703 for reference, and diagnose the change of the patient's solution and the like. . At this time, the doctor can also rewrite the setting value of the desired biological state by the fixed dosage control device 720 and send it to the portable dosage control device 730 as necessary. After that, if desired by the patient, the medication is controlled by the portable medication type control device 730 in the same order as in the above (2) and (3).

As described above, according to the present embodiment, since the patient can use the device while carrying the device, and the unnecessary power consumption is suppressed, the use for a long time becomes possible. In addition, since an alarm is output when the output voltage of the battery is lowered, it is possible to prevent the device from shutting down due to battery consumption. In addition, since medication record information can be exchanged with an external device, medication storage can be performed by continuously performing medication control by a plurality of medication control devices.

<< Third Example >>

In the above embodiment, for example, it is judged whether or not to administer the pulse wave wave information as a living body state. In contrast, in the present embodiment, the values of the elements of the 4-element concentrated constant model that model the circulation dynamics of the patient are calculated based on the pulse wave obtained from the patient, and the results are used as the living state.

In the present embodiment, the microcomputer 705 reads the pulse wave equivalent to one night in the waveform extraction storage unit 704 in step S722 of FIG. 113, and then determines the value of each element constituting the model. The calculation result is used as a living body state. In step S725, the state of the patient is determined by comparing the values of the elements in each of the excited state and the calm state prepared in advance as the living state with the living state.

<< Fourth Example >>

Although two types of blockers are used in the above embodiment, only one type of blocker may be used, or three or more types of blockers may be used. For example, when only the administration of the alpha blocker is necessary, the second dosage unit 600 is deleted from the configuration shown in FIG. 112, and only the first dosage unit 500 is used. In addition, when the step S725 of the timer intervention routine (FIG. 113) which the microcomputer 705 performs regularly is changed, and the determination result of step 724 becomes "Yes", the present patient's state is It is judged whether or not it is a calm state, and if the determination result is "Yes", the administration of the alpha blocker is performed and the recording thereof, and if it is "No", the timer intervention routine is terminated without the administration.

<< modification >>

(1) The medication control device 700 (portable medication control device 730 in the second embodiment) may be combined with an accessory or glasses.

(2) In the above embodiment, the alpha blocker or the beta blocker is administered when the waveform parameter of the pulse wave satisfies the predetermined condition, but the pulse wave itself in the state requiring the administration of the alpha blocker or the beta blocker is stored in the memory. The dosage control may be performed by comparing the stored pulse wave with the pulse wave obtained by the measurement.

In the above embodiment, when a patient is excited or sedated, a predetermined amount of blocker is administered at one time, but the form of the administration is not limited thereto. For example, nifedipine may be administered. In these cases, the program dose setting the control method, i.e., when an excitement or calm state is detected, the dose is given at a certain time, and the dose is also given after a predetermined time thereafter. In the state of performing the test, the medication may be divided into a plurality of circuits according to a preset program.

(4) In the above embodiment, administration was performed by an injection needle, but the means for performing administration is not limited to this. For example, various dosage methods may be applied, such as transdermal administration, intravenous administration, intraarterial administration, intraperitoneal administration, oral administration, transrectal administration, and the like.

⑤ This dosage device can be used for other applications as well as the dosage control of circulating working drugs. For example, in the case of obstructive atherosclerosis, administration of prostaglandin (arterial dilator), automatic control of the intravenous drip, control of administration of heparin during dialysis, and the like may be performed.

(6) In the above embodiment, a micropump using a silicon micromachine is used, but the present invention is not limited thereto, and various fluids such as syringe-type, rotary-type, and balloon-type are used. It is also possible to apply a pump.

(7) In the above embodiment, the necessity of the medication is detected based on the living state, and the final judgment is made as to whether the medication is administered by blood pressure measurement, but the final judge may be conducted by directly measuring the intravascular pressure. .

(8) In the above embodiment, it is determined whether to take a medicine based on the pulse wave obtained from the patient, and if necessary, the medicine is automatically taken. However, it is not limited to the thing of the range which automatically administers in this way. For example, in the above embodiment, a device for displaying or outputting each indicator of a living body state obtained from a patient may be configured except for a micropump, which is a medication means. In the above case, the doctor can make a judgment as to whether or not medication should be performed based on the display content or the output content.

9. As the living body, any of LF, HF, "LF / HF", and RR50 may be used. In addition, the excited state or the calm state may be comprehensively determined by combining two or all of these.

⑩ The display surface of the clock may display the current state of excitement and calm, that is, the values of the wave index of the current pulse wave, the cyclic dynamic parameter R _c, and the like.

In dosing, the pulse wave waveform is detected and the medication is performed from one stroke to the next in synchronism with the ejection of blood (and thus the pulse cycle) transferred from the heart (and thus between the pulse wave and the pulse wave). You may also do so. By doing this, the medicine can be injected in a state where the blood vessel pressure in the subcutaneous tissue of the living body is low.

In the pulse wave measurement, after confirming that the user has stabilized himself, the input unit 702 may be used to inform the device of the above effect. In this case, when the propriety of the pulse wave measurement determined by the output value of the body motion detection part 707 is notified, a state is good in determining whether a user is in a stable state.

In addition, the microcomputer 705 may always perform the detection of the stable state using the body motion detection part 707, and may detect the pulse wave only when a predetermined period is in a stable state.

In addition, the pulse wave and the body motion are measured over a predetermined period without waiting for a stable state, and these measured values are stored together in the memory 701. Based on the stored body motion measurement results, the user may select only the pulse wave measurement results when the user is in a stable state for only a predetermined period of time to obtain pulse wave information.

In each of the above embodiments, the effect state of the medicine may be detected and notified to the patient or the like. That is, the microcomputer 705 determines whether or not the biological state obtained by measuring the pulse wave in the subsequent patient and reaching the state that does not require the administration even after instructing the medication. And when the effect of medication is shown and it is determined that subsequent medication is not necessary, the output part 703 notifies that.

Claim 3 drug discharge device

At present, when the stress is high, society's interest in relaxation is increasing, and there is a demand for relaxation means that can be easily used in daily life. As a means for relaxation of this kind, the soothing action of perfume has been used conventionally. As an example from the example, the form of use which smokes incense and submerges a group is mentioned. Moreover, as a recent thing, the air conditioner etc. which mixed and blow | blended fragrance | flavor in air are mentioned.

By the way, in order to prevent the stress from being stored, it is desirable to relax at an appropriate frequency, but a long-awaited modern man neglects such relaxation. Since it is too early to be careful to relax yourself in the first place, there is a need for means of relaxation that do not require such an effort.

In addition, proper relaxation is necessary to prevent the storage of stress, but it is not always good to only relax. In other words, in order to achieve a truly healthy life, it is desirable to switch between a calm state and an excited state to a state of calming when resting and an appropriate state of excitement when working.

The device is intended to meet the requirements as described above, and automatically releases the perfume at an appropriate timing without bothering the user's hands, and controls and relaxes the internal state of the human body such as an excited state or a calm state.

<Preview>

MEANS TO SOLVE THE PROBLEM This inventor performs the following prior examination in designing the said apparatus. In addition, although this apparatus can use various drugs, it demonstrates, taking a fragrance as an example of a drug below.

<Confirmation of the effect of fragrance>

There is a close relationship between the human state, called the excited state and the calm state, and the circulatory dynamics parameter of the human, and as the human body changes from the calm state to the excited state or from the excited state to the calm state, the change is It is known to appear as a change. Therefore, the present inventors have determined the effect of the perfume by investigating the behavior of the circulatory dynamics parameters of the human body when in charge of the perfume.

(1) measuring method

Seven males aged 23 to 39 years were enrolled. Each subject was subjected to aroma oils of lavender and sandalwood, and the amount of one-time ejection of the subject and the arterial wave of the knuckles were measured at each time point after the ingestion, ingestion period, and ingestion period.

(2) analysis

As a circulating dynamics parameter of the human body, a four-element concentrated constant model was assumed, and it was confirmed what temporal change of each element of the four-element concentrated constant model.

(3) measurement result

By this experiment, the change of the circulating dynamics parameter by a fragrance was confirmed. 116 (a) to 116 (b) show the data of the single ejection amount SV and the blood vessel resistance R among the experimental data obtained this time. In addition, in the same figure, there is a notation which shows a measurement time point in the horizontal axis, but "before" is the time before making incense smell, "medium" the time after 6 minutes after starting incense smell, and "after" 3 minutes after the fragrance is stopped, "after" means a time after 6 minutes after the fragrance is stopped.

As shown in Figs. 116A to 116B, the significant increase in vascular resistance (R _p ) (ie, the transition to sedation) by allowing the fragrance of lavender to give the fragrance of sandalwood is a significant one-off (SV). An increase in and a decrease in vascular resistance (R _p ) (ie transition to excitability) were recognized.

As mentioned above, it was confirmed by the prior review that this time, lavender has a sedative effect and sandalwood has an excitatory effect.

<Confirmation of rhythm fluctuation of circulation dynamics>

It is known that the human state repeats the excited state and the calm state according to a regular rhythm of one cycle per day. Although this apparatus controls the human state to a desirable state by discharging the fragrance, in examining the means for achieving the above object, the original state of the human state when no operation is performed You need to know the behavior. Then, the inventors confirmed the shape of the rhythm fluctuations (variation rhythm in the day or fluctuation rhythm in the year) of the human state by examining the temporal change of the biological state such as the circulatory dynamic parameter as described above.

"theorem"

Based on the result of the above preliminary examination, the points which should be considered in designing this apparatus are summarized as follows.

① Since the action varies depending on the fragrance, it is necessary to determine the type of fragrance based on the intended action.

② The amplitude of the fluctuating rhythm is very large. Therefore, even if the human state is controlled by the fragrance, it is necessary to consider the rhythm of fluctuations throughout the day, not controlling the discharge of the fragrance based only on the current value of the circulating dynamics parameter.

③ The value of the cyclic dynamics parameter is large. Therefore, the discharge of the perfume needs to be controlled based on the fluctuation rhythm of the user's circulation dynamics parameters throughout the day.

<< First Example >>

Originally, it was confirmed that the human being repeats the excited state and the calm state in accordance with a constant rhythm. Here, for a person who has a good rhythm as a change rhythm of the excited state / calm state, there is no problem if such a rhythm is maintained over an organ. However, if the rhythm seems to be broken, it will have to be manipulated to return to the original rhythm. In addition, it is considered that an operation to avoid falling into such a state is necessary for a person who does not want to be in a state of extreme excitement or calm, so that a person who tends to be calm may transition to an appropriate state of excitement. You will need to manipulate it. In addition, a person who is always in a state of excitement will need manipulation to properly transition to a calm state.

In the apparatus according to the present embodiment, the circulation dynamics of the user is periodically measured, and perfume is discharged as needed based on the measurement result. Since the circulating dynamics are rhythmic fluctuations in one day cycle as described above, it is not possible to determine the application of perfume discharge only by the cyclic dynamics of a specific time point. Then, in consideration of the rhythm fluctuations of the circulating dynamics, the control of perfume discharge based on the respective parameter values of the current cyclic dynamics is performed. In addition, how it is desirable to manipulate the fluctuation rhythm of the excited state / calm state varies by the user. Therefore, the user can select a desired control mode also in what state the perfume should be discharged.

117 to 123 show the modes of discharge control of the perfume which can be executed in the present embodiment. In these figures, the solid line indicates the original temporal change of the user's state (excited state / calm state), and the broken line shows the temporal change of the state of the user controlled by the perfume discharge. Hereinafter, each mode of discharge control of a fragrance is demonstrated.

① Mode 1

In the time zone when the user transitions to the calm state, the smell of sandalwood having an excitatory action is suppressed (see FIG. 117). Extreme calming is very suitable for users who do not like it.

② Mode 2

In the time zone when the user enters the state of excitement, the smell of sandalwood, which has an excitatory action, is promoted (see FIG. 118). It is very suitable for users who need to make a recovery from calm state quickly.

③ Mode 3

At the time when the user enters the excited state, the smell of lavender having a calming effect is suppressed (see FIG. 119). Extreme excitement is well suited for users who do not like it.

④ mode 4

At the time when the user transitions to a calming state, the fragrance of lavender has a calming effect, promoting the transition of the calming state (see FIG. 120). It is very suitable for the user who needs to make a recovery from the excited state quickly.

⑤ mode 5

When the user transitions to the excited state, the fragrance of lavender is suppressed to suppress the transition of the excited state, and when the user transitions to the calm state, the smell of sandalwood is suppressed to suppress the transition of the calm state (see FIG. 121). It is very suitable for users who need to keep the state constant.

⑥ Mode 6

When the user transitions to the excited state, the fragrance of sandalwood is promoted, and the transition to the excited state is promoted, and when the user transitions to the calmed state, the fragrance of lavender is promoted (see FIG. 122). It is perfect for those who want to slow down and pull the rhythm of life.

⑦ Mode 7

When there is a change contrary to the fluctuation rhythm of the excited state / calm state of the past, the perfume which suppresses the change is discharged. That is, normally, when the transition of calming state is recognized in the time periods TA and TC to transition to the excited state, the smell of sandalwood is emitted to suppress the transition of calming state. In general, when the transition of the excited state is recognized in the time period (TB, TD) of transition to the calm state, the smell of lavender is emitted to suppress the transition of the excited state (see FIG. 123). It is effective in suppressing sudden excitement and calm.

<Configuration of the device>

124 is a block diagram showing the functional configuration of the apparatus according to the present embodiment.

The pulse wave detection unit 750 is a means provided to measure the arterial waveform of the finger node in the patient. In addition, the 1st fragrance discharge part 500 and the 2nd fragrance discharge part 600 are means provided in order to give a fragrance of lavender and sandalwood, respectively, and these were mentioned above in "paragraph 1".

The apparatus also has a battery 760 and an electricity supply control unit 761 for intermittent supply of electricity. The electricity supply control unit 761 includes a period during which each of the control unit 740, the pulse wave detection unit 750, the first perfume discharge unit 500, and the second perfume discharge unit 600 requires electricity supply (for example, the control unit). For 740, only the period during which arithmetic processing or the like is performed, and in the case of the perfume discharge unit, the period during which the perfume is discharged, supplies the output voltage of the battery 760 to each part. In this way, the voltage of the battery 760 is intermittently supplied to the respective parts, whereby the power consumption can be kept low, and the device can be operated for a long time. In addition, the output voltage of the battery 760 is monitored by a microcomputer (to be described later) in the control unit 740, and the notification is made when this becomes less than or equal to a predetermined voltage. This shows that it is time to replace the battery.

125A and 125B show the whole structure of the apparatus, the former is a perspective view showing the external appearance, and the latter is a sectional view taken along the line A-A 'of the former. As shown in the figure, the embodiment incorporated in the wristwatch having the pressure pulse wave sensor described in "Chapter 2 Section 1 Clause 4" is used.

The cross-sectional structure of the attachment portion of the watch band 771 in the watch main body 770 is as shown in Fig. 125B. The part includes a micropump 501, a tank 561, and the like described in claim 1, and these constitute a first perfume discharge part 500 in FIG. The microcomputer 501 pours the fragrance of lavender through the tube 505T from the tank 561 according to the driving instruction conveyed from the control part 740. The raised fragrance is sprayed to the outside at the injection hole 772 formed into the surface of the watch body 770 by passing through the tube 506.

Incidentally, the clock main body 770 also has a built-in equivalent to the second fragrance discharge unit 600 in FIG. 123, but is not shown in order to avoid trouble. The sandalwood fragrance, which is spread by the second fragrance discharge unit 600, is injected to the outside from the injection hole 773.

Next, with reference to FIG. 124, the structure of the control part 740 is demonstrated. The memory 741 is a nonvolatile memory constituted by a battery-backed RAM or the like, and is used for temporary storage of control data when the microcomputer 745 controls other parts. In the predetermined storage area of the memory 741, cyclic dynamic parameters measured at a plurality of different time points are stored.

The input unit 742 is means provided for inputting various commands to the microcomputer 745, such as a command for setting one of the modes 1 to 7, described above. For example, in FIG. It consists of a Lew's, a button, etc. provided in the clock | watch main body 770 shown.

The output part 743 is an output means comprised by the liquid crystal display device, the alarm sound generating device, etc. which were provided in the clock | watch body 770.

The waveform extraction storage unit 744 records the detection signal obtained by the pulse wave detection unit 750 under the control of the microcomputer 745, and extracts and stores the pulse wave for one night from the recorded signal. In addition, the detail was demonstrated in "Chapter 3 Section 1 Clause 2."

The microcomputer 745 controls each unit in the control unit 740 in accordance with a command input through the input unit 742. In addition, the microcomputer 745 incorporates a clock circuit, and performs the following timer intervention processing each time a predetermined time elapses.

(1) Control of recording process of pulse wave signal and extraction process of pulse wave of thin powder by waveform extraction storage unit 744

Whenever the peak point of the pulse wave is detected by the waveform extraction storage unit 744, the peak information is obtained and stored in the internal memory.

② Calculation of Circulation Dynamic Parameters

Based on the peak information obtained in (1), the waveform value of the pulse wave for one night is read by the waveform extraction storage unit 744, and the value of the user's cyclic dynamic parameter is obtained based on the pulse wave. As the present embodiment, the &quot; method of obtaining these parameters from the amplitude and phase of pulse wave strain and pulse wave spectrum &quot; described in Chapter 4, Section 1, Section 3 is employed. The obtained cyclic dynamics parameter is stored in the memory 741 together with the information indicating the measurement time of the pulse wave.

As the above processing is repeated at regular time intervals, the cyclic dynamics parameter at each time is stored in the memory 741.

The microcomputer 745 also controls the perfume discharge of the first perfume discharge unit 500 and the second perfume discharge unit 600 with reference to the circulating dynamic parameters in the past fixed period stored in the memory 741. . In addition, the said control is demonstrated also when an operation | movement is demonstrated, and the overlapping description is avoided here.

In addition, the 1st fragrance discharge part 500 and the 2nd fragrance discharge part 600 are comprised by the microcomputer and its drive part, The 1st fragrance discharge part 500 is for spraying the fragrance of lavender, The two fragrance discharge unit 600 is for spraying the fragrance of sandalwood. In addition, as a present Example, the tank 561 shown in FIG. 109 is satisfy | filled with the fragrance of lavender or sandalwood.

On the other hand, the I / O interface 755 is described in "Chapter 5, Section 3" as a means for performing communication between devices installed outside the apparatus. By using the I / O interface 755, for example, information on the biometric state or the discharge record of the perfume stored in the memory 741 can be transmitted to the external device.

The body motion detection unit 756 is an example of body motion detection means for grasping the body motion of the user of the apparatus, converts the measured body motion value into a digital signal and sends it to the microcomputer 745.

<Operation of the device>

(1) Periodic measurement of cyclic dynamic parameters

As described above, timer intervention is performed on the microcomputer 745 regularly. As a result of the above, the following processing is executed by the microcomputer 745 as a timer intervention routine.

First, a process for extracting a waveform and its peak information is executed. In addition, the detail of the said process was demonstrated in "Chapter 3 Section 1".

Here, in measuring the pulse wave, the microcomputer 745 reads the output of the body motion detector 756 and stores it in the memory 741. Then, it is determined whether the output value of the body motion detecting unit 756 indicates that the user is in a stable state. If there is a possibility that the measurement of the pulse wave may be inaccurate if it is not in the stable state, the microcomputer 745 uses the output unit 743 to notify the user of the above effect. Then, after the user recognizes the stable state suitable for the pulse wave measurement, the pulse wave is measured.

Next, the microcomputer 745 performs waveform reading processing and calculating processing of the cyclic dynamics parameter. That is, the waveform value of the pulse wave for one night is read by the waveform extraction storage unit 744 by the microcomputer 745, and the spectrum (amplitude information and phase information) of the pulse wave is obtained by FFT processing. And based on the said spectrum, the value of one parameter of the 4-element concentrated constant model, for example, the inductance L, is calculated, and the other parameter value is calculated based on the value of L and the waveform of the pulse wave for one night. . The microcomputer 745 rewrites the cyclic dynamics parameter thus obtained to the memory 741 simultaneously with the information indicating the current date and time.

(2) discharge control of perfume

The operation of the fragrance discharge control differs in the case where any of the modes 1 to 6 described above is selected and the case in which the mode 7 is selected. The operation of the apparatus will be explained below in each case.

① When one of the modes (1 to 6) is selected

When these modes are selected, the microcomputer 745 performs a process of determining when to discharge the perfume when a predetermined time is reached in the midnight time zone. That is, the cyclic dynamic parameters within a certain period of time (for a predetermined number of days) stored in the memory 741 are read, and each movement of a specific parameter (for example, the time when the resistance R _p becomes maximum and the time when the minimum becomes The average is calculated, and according to the result of the calculation, time zones (period TA and TC illustrated in FIG. 123) for transition from the calm state to the excited state and time zones (for example illustrated in FIG. 123) for transition from the excited state to the calm state. Period TB, TD), and the fragrance discharge command is set so that the fragrance corresponding to each mode is discharged at a predetermined time in the time zone thus obtained, for example, at a time in the center of the time zone. For example, when the mode 5 is set, the following four time periods of perfume discharge are set.

Driving the second fragrance discharge unit 600 at a predetermined time in the time zone TA.

Driving the first fragrance discharge unit 500 at a predetermined time in the time zone TB.

Driving the second fragrance discharge unit 600 at a predetermined time in the time zone TC.

Driving the first fragrance discharge unit 500 at a predetermined time in the time zone TD.

And when the time set as mentioned above in a day arrives, the microcomputer 745 sends a drive command to the corresponding perfume discharge part. When the drive command is generated by the microcomputer 745, the first perfume discharge unit 500 or the second perfume discharge unit 600 which receives this is via the respective injection holes 772 or the injection holes 773. While the corresponding perfume is injected to the outside, the perfume is sucked into the micro pump 501 in the tank 561. At that time, the microcomputer 745 receives the abnormality detection signal from the first perfume discharge unit 500 or the second perfume discharge unit 600, thereby causing the output unit 743 to display an alarm. Thereby, when the discharge of perfume is not normally performed, the effect is immediately known, and treatment such as adjustment of the discharge means can be promptly performed.

Next, when the discharge of the perfume is finished, the current discharge amount is calculated based on the number of times the drive command is generated, and the discharge amount and the type of the perfume discharged this time are written into the memory 741 as discharge record information. In addition, the accumulated value of the discharge amount so far is calculated for each perfume and the result is written into the memory 741. Here, when the accumulated value exceeds a predetermined value, the microcomputer 745 sends a warning output command to the output unit 743, and the output unit 743 sends a tank to the user by displaying an alarm such as lighting of a warning lamp. Prompt the exchange of (561). It turns out that it was time to replenish fragrance by this.

② When mode (7) is selected

Also in this mode, the microcomputer 745 reads the cyclic dynamic parameters stored in the memory 741 at a predetermined time in the late-night time zone and based on this, the time zone for transitioning from the calm state to the excited state (period TA, TC) and the time period (period TB, TD) of transition from the excited state to the calm state (see FIG. 123). In this mode, the time period thus obtained is monitored for the temporal change of circulation dynamics and the discharge control of the perfume based on the monitoring result.

That is, during the day, the microcomputer 745 periodically measures the cyclic dynamics parameter in any of the periods TA, TB, TC, and TD, and the cyclic dynamics parameter obtained at that time Determine whether it is increasing or decreasing. The microcomputer 745 then determines whether the temporal change of the cyclic dynamics parameter is contrary to the normal temporal change of the cyclic dynamics parameter in that time zone. And when a change contrary to the normal temporal change of a cyclic dynamics parameter is recognized, the fragrance | flavor for suppressing such a strange change is discharged.

For example, the period TA is a time period during which the resistance R _p of the cyclic dynamic parameters decreases and the user transitions from a calm state to an excited state. In the period TA, if the resistance R _p is decreasing, there is no problem since it is a normal change. However, if the resistance R _p is increased, this is contrary to the time change of the passage of the resistance R _p . Thus, the microcomputer 745 sends a drive command to the second perfume discharge unit 600 to discharge the sandalwood perfume, and suppresses the increase in resistance R _p (that is, the transition of the calm state). In the period TB, since the increase in the resistance R _p is a normal temporal change, when the resistance R _p decreases, the driving command is sent to the first perfume discharge unit 500, and the lavender Discharge the fragrance and prevent the reduction of resistance R _p .

As described above, control of the perfume discharge is performed based on the temporal change of the circulating dynamics parameter, and the perfume discharge is automatically suppressed, promoted, or suppressed and promoted at an appropriate timing. In this way, the user's state is controlled such that it changes in time according to the desired fluctuation rhythm.

<< Second Embodiment >>

While the first embodiment performs the discharge control of the perfume based on the shape of the waveform of the pulse wave, the present embodiment controls the discharge of the perfume based on LF, HF, and "LF / HF". In addition, although these indicators are represented below and demonstrated by "LF / HF", the same control is possible even if LF or HF is used, except that the kind of fragrance to discharge in HF is reversed. .

<Configuration of the device>

The configuration of this embodiment is the same as that of the first embodiment.

<Operation of the device>

(1) Periodic measurement and spectral analysis of pulse wave

As described above, for the microcomputer 745, timer intervention occurs periodically (eg, every two hours). In response to this, the microcomputer 745 executes the following processing as a timer intervention routine.

First, the waveform and the peak information of the waveform are extracted as in the first embodiment. In this embodiment, the pulse wave recording process is performed for example, 30 seconds per measurement. Next, "LF / HF" is calculated based on the recorded pulse wave waveform, and stored in the memory 741 simultaneously with the time when the pulse wave is measured.

Then, the regular measurement and spectral analysis of the pulse wave described above are repeated every other hour for 2 hours.

(2) discharge control of perfume

As in the first embodiment, the operation related to the discharge control of the perfume is different from the case in which one of the modes 1 to 6 is selected and the case in which the mode 7 is selected. The operation is outlined in each case below.

① When one of the modes (1 to 6) is selected

The microcomputer 745 determines the timing of perfume discharge at a predetermined time in the late night time zone. That is, after reading the value of "LF / HF" for a predetermined number of days (for example, the past one week) from the memory 741 and calculating the average of "LF / HF" at each time, the "LF / HF" Calculate the time at which the average value of &quot;

Next, according to the calculation result, time periods for transitioning from the calm state to the excited state and time periods for the transition from the excited state to the calm state are obtained. Then, the fragrance discharge command is set so that the fragrance corresponding to each mode is discharged at a predetermined time (for example, the central time) of the determined time zone.

Thereafter, when the time set above is reached, the microcomputer 745 drives the corresponding first perfume discharge unit 500 or the second perfume discharge unit 600 to discharge the perfume. Then, when the discharge of the perfume is finished, the discharge amount of the perfume is calculated as in the first embodiment, and stored in the memory 741 as discharge record information at the same time as the type of perfume. The cumulative value of the discharge amount for each perfume is also obtained and stored in the memory 741.

② When mode (7) is selected

As in ①, the microcomputer 745 calculates an average value for one week based on "LF / HF" in the memory 741 at a predetermined time in the late-night time zone. Next, the time at which the average value of the "LF / HF" becomes maximum or minimum is calculated | required, and the time slot which transitions from a calm state to an excited state, and the time zone which transitions from an excited state to a calm state is calculated | required based on the obtained time. Next, during the day of the next day, the discharge control of the perfume is performed based on the monitoring of the temporal change of "LF / HF" in the determined time zone and the monitoring result.

That is, when the microcomputer 745 performs regular measurement of the value of "LF / HF", it determines whether "LF / HF" at the present time is increasing or decreasing from the previous value. Subsequently, it is examined whether the temporal change is against the normal temporal change in the time zone to which the time of the periodic measurement belongs. If it is admitted against this, discharge of the fragrance which suppresses the said abnormal temporal change is performed.

For example, when "LF / HF" decreases during the time when the internal state of the subject should transition from the calm state to the excited state, this is contrary to the normal time change. Therefore, the microcomputer 745 drives the 2nd fragrance discharge part 600, discharges the sandalwood fragrance, and moves a subject to an excited state. On the other hand, if "LF / HF" is increasing during the time when the internal state of the subject is to transition from the excited state to the calm state, the first perfume discharge unit 500 is driven to discharge the perfume of lavender and the subject is calm. Leads.

Third Embodiment

This embodiment is the same as the second embodiment in that the perfume is discharged based on the wave information of the pulse wave, except that RR50 is used as the living body.

<Configuration of the device>

The configuration of this embodiment is the same as that of the first to second embodiments.

<Operation of the device>

(1) Periodic measurement of pulse wave

As described above, for the microcomputer 745, timer intervention occurs periodically (eg, every two hours). In response to this, the microcomputer 745 executes the following processing as a timer intervention routine.

First, the waveform and the peak information of the waveform are extracted and stored as in the second embodiment. When the measurement for one time is finished, the microcomputer 745 performs peak detection of each pulse wave on each pulse of the pulse wave obtained in the measurement period, and then calculates RR50 and stores it in the memo 741 at the same time as the measurement time point. .

And the regular measurement of the above-mentioned pulse wave is repeated every other time every 2 hours.

(2) discharge control of perfume

The operation of controlling the discharge of the perfume in this embodiment is the same as that of the second embodiment except that RR50 is used instead of "LF / HF". Here, "LF / HF" is in an excited state as the value is larger, and in a calm state as the value is smaller. On the other hand, RR50 is in a calm state as the value is larger, and in a excited state as the value is smaller. Therefore, in the present embodiment, the selection criteria of the discharge perfume in the discharge control of the perfume are opposite to that of the second embodiment.

<< transformation example >>

① You may combine this unit with accessories or eyeglasses.

(2) Although two fragrance discharge units were used, an apparatus in which only one type of fragrance was discharged may be used as one.

(3) In the mode (7), the perfume is discharged when the cyclic dynamics parameter changes in response to changes in the time zone (rising tendency / falling tendency) in the past, but the mode is modified. You may also do it.

That is, in place of the mode (7) or in addition to the mode (7), the range of the difference of the value of the cyclic dynamics parameter in the time zone of the past several days in a specific time zone (for example, the average value of E ± 3α) In the case where a cyclic dynamics parameter deviating from the range, where α is the standard deviation, is measured, a mode for discharging the perfume having an effect of returning to within the gap range may be configured.

④ Lavender and sandalwood are used as fragrances, but there are individual differences in what kind of fragrances are appropriate, and depending on the user, fragrances suitable for generating sedation or excitement may be different from these. Therefore, in using the apparatus according to each of the above embodiments, after confirming which perfume is appropriate to use, an appropriate perfume is set in the first perfume discharge unit 500 or the second perfume discharge unit 600. It is preferable to use.

In addition, the drug was described as an example of the perfume of lavender and sandalwood. However, as long as they have the above-mentioned correlations between the living states, perfumes other than these may be used, or drugs other than perfumes may be used.

(5) Two manual switches may be added, and lavender may be discharged when the first switch is operated, and sandalwood may be discharged when the second switch is operated.

(6) According to the spectral analysis of the pulse wave, the amplitude of the harmonic wave of the pulse wave or the phase of the harmonic wave (for example, the phase of the fourth harmonic) with respect to the fundamental wave may be detected, and perfume discharge control may be performed based on the value of the phase. According to the experiments of the present inventors, it is confirmed that when a stress is applied to a human, the amplitude of each phase or third wave of the second wave, the third wave, and the fourth wave of the pulse wave changes. For example, a pulse wave of eight subjects was examined for physical stress received when immersing one hand in 4 ° C water, and there was a 95% probability that each phase or third phase of second, third, and fourth harmonics had a 95% probability. It was confirmed that the amplitude of the three harmonics changes. In addition, when the pulse waves of eight subjects were examined for the mental stress of repeating the [1000-9] calculation, it was confirmed that the phase of the fourth harmonic wave also had a 95% probability.

In the third embodiment, a heart rate may be used instead of RR50. As noted, a negative correlation is seen between RR50 and heart rate. Therefore, the same effect as the third embodiment can be obtained by controlling the ejection of the perfume by selecting the perfume as the opposite of the third embodiment (or the same as the second embodiment). Moreover, you may use various quantities, body temperature, pulse rate, etc. which are obtained from the waveform of an electrocardiogram.

⑧ You may make it possible to discharge the drug such as perfume by the user's key input.

(9) The pulse wave measurement may be performed by using the input unit 742 after confirming that the user has settled on a stable state. In the above case, if the suitability of the pulse wave measurement determined by the output value of the body motion detection unit 756 is notified, the state is good for determining whether the user is in a stable state.

In addition, the microcomputer 745 may always perform the detection of the stable state using the brake detection part 756, and may detect the pulse wave only when a predetermined period is in a stable state.

In addition, the pulse wave and the body motion are measured over a predetermined period without waiting for a stable state, and these measured values are stored together in the memory 741. Based on the measured results of the stored body dynamics, the user may select only the pulse wave measurement results at the time when the user is in a stable state for only a predetermined period of time, so as to obtain pulse wave information.

각 In each of the above embodiments, the presence of a drug such as perfume may be detected and the user notified of the fact. That is, even after the microcomputer 745 instructs the spraying of the fragrance, the state of the living body obtained by continuously measuring the pulse wave and calculating the living state by the user (the state differs for each of the above-described modes) Determine if you have reached. And when the effect of a fragrance appears and it is judged that there is no necessity of spraying of a fragrance | flavor afterwards, the output part 743 notifies the effect.

토출 In discharging the drug, the pulse wave waveform is detected and synchronized with the ejection of blood (and thus the pulse cycle) transferred from the heart, and the drug is applied to the living body from one ejection to the next ejection (and thus between the pulse wave and the pulse wave). May be discharged. In this way, the drug can be discharged in a state where the tissue internal pressure of the living body is low, and the discharge efficiency is improved and is very effective.

Section 4 sleepiness prevention device

In this section, an application example in which diagnosis and control based on a living state (pulse index of pulse wave) is performed while also considering periodic fluctuations of the living state is described. In addition, although the drowsiness prevention apparatus demonstrated below is not an apparatus which directly controls a biological state, but controls an external apparatus (car etc.), it is demonstrated in this section from a "control" viewpoint.

Recently, there have been a number of traffic accidents caused by drowsiness while driving in automobiles and the like. Therefore, various apparatuses are conventionally designed for the purpose of preventing such an accident in advance. One example is a device installed in a handle. In such an apparatus, conductors are attached to the left and right sides of the handle, and the resistance of the human body (driver) is measured so that both hands of the driver always touch the conductor. Since the resistance value between conductors changes when the driver slumbers and releases the handle, an accident can be prevented by holding the phenomenon drowsy and causing the driver to beep.

As another example, the use of heart rate fluctuations that can be obtained in the measurement of the electrocardiogram of the driver, the use of breathing fluctuations of the driver, and the like have been considered.

By the way, in the method of attaching the conductor to the handle as described above, accurate drowsiness monitoring cannot be performed when the driver is driving with one hand or when the driver is wearing gloves. In addition, as a method of grasping heart rate fluctuations, respiration fluctuations, and the like, it is not suitable for carrying a driver on a daily basis since the apparatus is large.

This apparatus solves this problem, and is an apparatus which detects drowsiness state by analyzing the arousal level of a human body in the pulse wave behavior acquired in a living body.

<< First Example >>

The drowsiness prevention device which concerns on a present Example detects the drowsiness state of a human body based on the correlation between the information contained in a pulse wave, and the arousal level of a human body. In that case, the measured amount of several values obtained from a pulse wave is used as an index in judging the arousal state of a human body, and LF, HF, "LF / HF", and RR50 are used as the specific example below. According to the correlation, as the sleep becomes deeper, the living body state is considered to gradually increase, for example, the value of RR50 gradually increases from drowsiness to drowsiness. Therefore, drowsiness can be detected by detecting a change of these indices.

<Configuration of the device>

126 is a block diagram showing the structure of the apparatus. The user of the apparatus (for example, a driver of a car or a driver of a train) is equipped with a wrist watch 790 shown in FIG. 127, and the apparatus shown in FIG. 126 is configured inside the wrist watch 790.

In FIG. 126, CPU 781 is a central part which controls each circuit in this apparatus, and the function is performed as description of the operation mentioned later.

The ROM782 stores a control program executed by the CPU 781, control data, and the like.

The temporary storage memory 783 is a kind of RAM, and is used as a work area when the CPU 781 performs arithmetic.

The pulse wave detection unit 784 constantly measures the pulse wave in the artery part of the user's fingertip, and outputs the measurement result as an analog signal.

The A / D converter 785 digitizes the analog signal, converts it into a digital signal, and outputs the digital signal.

The data memory 786 is a nonvolatile memory including battery-backed RAM and the like. The data of the pulse wave obtained by the CPU 781 from the A / D converter 785, LF, HF, "LF / HF", the value of RR50, etc. are stored.

Clock circuit 787 generates a time, which is used to display on watch 790. In addition, the CPU 781 has read the time from the clock circuit 787 for the purpose of informing the current time.

The operation unit 788 is provided with various buttons provided on the wristwatch 790, and detects that these buttons are pressed and outputs the types of the buttons.

The buzzer 789 issues a warning sound to the user based on the alarm start and alarm stop instructions from the CPU 781. In practice, the buzzer 789 is, for example, an alarm mechanism attached to a commercially available digital wrist watch.

The I / P interface 850 is a means for communicating with devices installed outside the apparatus, as described in Chapter 5, Section 3. By using the I / O interface 850, for example, information such as LF, HF, &quot; LF / HF &quot;, RR50, and the like stored in the data memory 786 can be transmitted to an external device.

The acceleration sensor 851 is an example of body motion detection means which grasps the body motion of the user of this apparatus. In addition, the A / D converter 852 has the same configuration as the A / D converter 852 and converts the output of the acceleration sensor 851 into a digital signal and sends it to the bus.

On the other hand, the watch 790 shown in FIG. 127 has a watch having two modes of "normal use mode" used as a normal watch and "watch mode" which detects a state where the user is dozing and warns the user. to be.

In the figure, reference numeral 791 denotes a main body of a wrist watch, and a time display unit 792 for displaying a current time and date is provided on an upper surface of a wrist watch as in a general wrist watch. Further, a time alignment button 794 (so-called crown) and a mode change button 795 for adjusting the time are provided on the right side of the watch 790. The mode switching button 795 is a button for switching between the normal use mode and the monitoring mode, and each time the button is pressed, the normal use mode and the monitoring mode alternately. In addition, it is initialized to a normal use mode at the time of power supply.

In addition, as demonstrated in "Chapter 2 Section 1 Clause 4", code | symbol 47 is a pressure type pulse wave sensor, 48 is a mechanism to install, 49 is a band of a watch.

<Operation of the device>

Hereinafter, the case where drowsiness is detected based on RR50 as the above-mentioned index is demonstrated.

(1) transition of monitoring mode

The user of this apparatus presses the mode change button 795 of the wristwatch 790, for example in driving a car. When the operation unit 788 that detects the push down of the button sends the CPU 781 that the replacement button 795 is pressed down, the CPU 781 switches the device from the current normal use mode to the monitoring mode and is in operation. Enable drowsiness monitoring function.

(2) recording the waveform of the pulse wave

The pulse wave detection unit 784 always measures the pulse wave of the artery of the user's finger joint. The measurement result is converted into digital data by the A / D converter 785 and output to the common bus. When the monitoring mode is established by the above-described button press, the CPU 781 reads the digital data at a predetermined time interval and stores the digital data in the data memory 786 together with the current time read by the clock circuit 787.

In addition, in order to measure a pulse wave more correctly, it is as follows. That is, the CPU 781 reads the output of the acceleration sensor 851 through the A / D converter 852 and stores it in the temporary storage memory 783. Then, it is determined whether the output value of the acceleration sensor 851 indicates that the user is in a stable state. Since the pulse wave may be measured incorrectly unless it is in a stable state, the CPU 781 uses a buzzer 789 or the like and notifies the user of the foregoing. Thereafter, the user recognizes that the user is in a stable state suitable for measuring the pulse wave, and then measures the pulse wave.

(3) Analysis of waveform of pulse wave

Next, the CPU 781 interprets waveforms of pulse waves for a predetermined time in the past stored in the data memory 786, calculates RR50, and stores the data in the data memory 786 simultaneously with the current time read by the clock circuit 787. do.

(4) Determination of Awakening State and Control of Beep

Next, the CPU 781 calculates RR50, and determines whether the user is in a doze state based on the calculated RR50. That is, the magnitude relationship between the calculated value of RR50 and the predetermined reference value is examined, and if the calculated value of RR50 is larger than the reference value, the user is considered to be asleep. The CPU 781 sends an alarm instruction to the buzzer 789, and the buzzer 789 issues a warning sound to awaken the user.

Then, when a user opens his eyes, the value of RR50 will gradually fall, and will eventually fall below the said reference value. Upon detecting this, the CPU 781 sends an alarm stop instruction to the buzzer 789 and stops the generation of the alarm sound from the buzzer 789.

Alternatively, when the user who opens his eyes presses the mode change button 795, the operation unit 788 is notified of the button press, and the CPU 781 switches the device from the monitoring mode to the normal use mode. At this time, an alarm stop instruction is sent to the buzzer 789, and the generation of the warning sound is stopped.

<< Second Embodiment >>

In the first embodiment, a warning is given when the RR50 at the present time exceeds the "fixed" reference value. However, it is more desirable and considered to be able to enter in consideration of the periodic fluctuations of the wave index of the pulse wave. In addition, in the following description, it demonstrates using RR50 like 1st Example.

<Configuration of the device>

The configuration of the apparatus according to the present embodiment is the same as that of the first embodiment. Only the wave index of the pulse wave extracted at predetermined time intervals is sequentially stored in the data memory 786.

<Operation of the device>

(1) transition of monitoring mode

When the user presses the mode change button 795, the CPU 781 switches the device to the monitoring mode and simultaneously sets the clock circuit 787 to generate intervention at predetermined time intervals.

(2) Regular measurement of RR50

After this, the CPU 781 records the arterial wave of the finger node in the pulse wave detection unit 784 through the A / D converter 785 each time the intervention signal enters the clock circuit 787, calculates RR50, and stores the data. The memory 786 is stored.

(3) Determination of awakening state and control of warning sound

When the above process is finished, the CPU 781 performs subsequent determination of sleepiness. That is, the CPU 781 reads the value of the RR50 of the past predetermined period (for example, one week) from the data memory 786, and calculates a moving average of the RR50 of the past one week. When the calculated RR50 is larger than the moving average value by more than a predetermined value, it is regarded as a dozing state, and the buzzer 789 emits a warning sound.

The operation after this is the same as the first embodiment, and the user wakes up with the passage of time, or the user presses the mode change button 795, so that the CPU 781 uses the device normally. Switch to the mode and stop the alarm sound.

By doing the above, the user can determine the state of dozing at the level of the daily RR50 of the user, and the error detection of the state of dozing can be performed, on the contrary, the possibility of overlooking the state of dozing is extremely reduced, It is also excellent in view.

<< Third Example >>

In each of the above embodiments, a warning sound is issued to the driver when a state of dozing is detected. However, instead of giving a warning to the driver, consider wirelessly connecting the device and the vehicle wirelessly and instructing the brake device of the vehicle to brake automatically when the driver detects drowsiness. .

<Configuration of the device>

The structure of the apparatus which concerns on a present Example is shown in FIG. In the same figure, the same code | symbol is attached | subjected to the thing which has the same function as FIG. 126, and the description is abbreviate | omitted.

The transmitter 800 provided in the wristwatch 790 amplifies the electric signal transmitted from the CPU 781 to be suitable for the transmission antenna 801. The transmitting antenna 801 converts the signal into radio waves and transmits the signal.

810 is the car the driver is riding on. In addition, the receiving antenna 811 receives the radio wave transmitted from the transmitting antenna 801 and converts it into an electrical signal. Alternatively, the receiver 812 amplifies the electric signal and outputs the cut-off part 813 to block. The control unit 813 manages the receiving unit 812, the brake device 814, and various devices not shown in the interior of the vehicle 810. The brake device 814 controls the braking operation of the vehicle 810 according to the instruction of the controller 813.

<Operation of the device>

First, in the monitoring mode, the CPU 781 measures and analyzes the waveform of the pulse wave of the driver in the monitoring mode and detects a state where the driver is dozing. The CPU 781 transmits a brake braking command signal to the transmitter 800. The braking instruction is converted into radio waves by the transmitting unit 800 to the transmitting antenna 801 and radiated outside the wrist watch 790. The radio wave is received by the receiving antenna 811 installed on the vehicle 810 side and converted into an electric signal, and the electric signal is amplified by the receiving unit 812 and sent to the control unit 813. The control unit 813 receives the electric signal from the receiving unit 812, interprets the instruction, and sends a braking instruction to the brake apparatus 814 when recognizing that the instruction is a braking instruction of the brake. As a result, the brake device 814 applies the brake to stop the vehicle 810.

As described above, according to each of the above embodiments, as a relatively simple method of detecting pulse waves, the user can detect drowsiness, the apparatus does not become large, and the user can realize the apparatus freely transported at all times. . In addition, when combined with a portable device such as a wrist watch, there is an advantage that driving of the vehicle is not disturbed.

<< transformation example >>

① You may combine this unit with accessories or glasses.

(2) In the first embodiment, the awakening state of the user is determined based on the value of RR50. By the way, it is also possible to use LF, HF, or "LF / HF" mentioned above instead of RR50. In other words, it can be said that the biological state is in a "state where the amplitude of the LF component is small", "the degree where the amplitude of the HF component is large", and "the degree where the value of the LF / HF is small" is in a steady state. And in judging the arousal state of the user in the process of (4) of 1st Example mentioned above, when the amplitude of LF is below the reference value, respectively, when the value of HF exceeds the reference value, it is "LF / HF Value is less than the reference value, it may be determined that the user is drowsy.

(3) Instead of always making the same sound level, it is considered to apply strength and weakness according to the difference between the calculated RR50 and the reference value.

(4) The individual values of LF, HF, "LF / HF", and RR50 may not be used alone, but may be determined whether or not a warning is given after considering some or all of these values. .

(5) In the third embodiment, the brake may be stopped and the driver may be warned by the warning means such as the buzzer 789 described above.

(6) It is more effective to warn the buzzer or the like and to spray the fragrances having the arousal effect together as used in the above-described fragrance discharge control.

(7) The pulse wave measurement may be made to inform the apparatus by using the operation unit 788 after confirming that the user has stabilized himself. In the above case, if the determination is made based on the output value of the acceleration sensor 851 and the suitability of the pulse wave measurement is notified, the state is good for determining whether the user is in a stable state.

In addition, the CPU 781 may perform the detection of the stable state using the acceleration sensor 851 at all times, and may detect the pulse wave when only the predetermined period is in the stable state.

In addition, the pulse wave and the body motion are measured over a predetermined period without waiting for a stable state, and these measured values are stored together in the data memory 786. Based on the measured results of the stored body dynamics, the user may select only the pulse wave measurement results at the point in time when the user is in a stable state for only a certain period of time, and obtain pulse wave information.

(8) In the third embodiment, the case of driving a car has been described, but it goes without saying that the present embodiment can be applied to a vehicle other than this. Note that the notification means may not be provided on the portable device side, but may be controlled and notified of the crashon or the like provided on the vehicle side.

(9) In each of the above embodiments, the state of dozing is detected and a warning is given. However, on the contrary, the awakening state of the user may be calculated, and when the awakening degree is sufficiently high, the user may be notified of the purpose. In this way, the user's attention is called up every time the notification is given, and the user himself is more effective from being aware of not sleeping slowly.

Claims (43)

In the device for diagnosing a living state, Measuring means for measuring the indicator of the living state over a specified time period; A time circuit for providing time data indicative of the current time; And Detect the periodic variation of the living state based on the indicator measured by the measuring means and the visual data provided by the clock circuit when each of the indicators is measured by the measuring means, and consider the periodic variation And diagnosing means for diagnosing the living state. The method of claim 1, The measuring means measures the indicator of the living state at a plurality of times each day; The diagnostic means, Recording means; And The indicator and the time data provided by the clock circuit when each of the indicators are measured by the measuring means, stored in the recording means, and based on the data stored in the recording means, the current measurement by the measuring means And control means for determining whether the determined indicator is within a range of the variation indicated by the indicator measured at the same past time as the current time, and providing a notification of the result of the determination. The method of claim 1, The measuring means measures the indicator of the living state at a plurality of times each day; The diagnostic means, Recording means; And Storing the time data provided by the clock circuit when the indicators and each of the indicators are measured by the measuring means in the recording means, and from the standard indicators calculated from the indicators measured at the past time equal to the current time. And control means for providing notification of the deviation of the indicator currently measured by the measuring means. The method of claim 1, The measuring means measures the indicator of the living state at a plurality of times each day; The diagnostic means, Recording means; And Storing the indicator and the time data provided by the clock circuit when the indicators are measured by the measuring means in the recording means, obtaining a change mode of the currently measured indicator, and changing the currently measured indicator. Data indicating a mode is stored in the recording means, and based on the data stored in the recording means, it is determined whether the change mode of the currently measured indicator matches the change mode of the indicator measured at the same past time as the current time. And control means for determining and providing a notification of the result of the determination. The method of claim 1, The measuring means measures the indicator of the living state at a plurality of times each day; The diagnostic means, Recording means; And The recording means storing the indicator and the time data provided by the clock circuit when each of the indicators are measured by the measuring means in the recording means, and the time of the maximum value at which the currently measured indicator takes the maximum value. Based on the data stored in the data storage device, storing the data representing the time of the maximum value, and based on the data stored in the recording means, the index of the change measured by the current measured indicator is measured at a past time equal to the current time. And control means for determining whether to coincide with the change mode indicated by and providing a notification of the determination result. The method of claim 1, The measuring means measures the indicator of the living state at a plurality of times each day; The diagnostic means, Recording means; And Storing the indicator and the time data provided by the clock circuit when each of the indicators are measured by the measuring means in the recording means, and storing the time of the minimum value at which the currently measured indicator takes the minimum value in the recording means. A data obtained based on the data, storing data representing the time of the minimum value, and based on the data stored in the recording means, the change represented by the indicator measured at a past time in which the change mode of the currently measured indicator is equal to the current time. And control means for determining whether to match a mode and for providing a notification of the determination result. The method of claim 2, The control means calculates an index value at a predetermined time during an interval of a past time by interpolation using the indicator measured by the measuring means during the interval, and based on the calculation result, the range of the variation is calculated. Determination, biometric diagnostic apparatus. The method of claim 1, The measuring means measures the indicator of the living state at a plurality of times each day; The diagnostic means, Recording means; And A waveform for the daily variation of the indicator and the time data provided by the clock circuit when each of the indicators are measured by the measuring means in the recording means and stored in the recording means over a plurality of days. And a control means for calculating the correlation of the values and outputting the calculation result. The method of claim 1, The measuring means measures the indicator of the living state at a plurality of times each day; The diagnostic means, Recording means; And A waveform for the daily variation of the indicator and the time data provided by the clock circuit when each of the indicators are measured by the measuring means in the recording means and stored in the recording means over a plurality of days. And a control means for generating a graph superimposed and outputting the graph. The method of claim 1, The diagnostic means, Recording means; First control means for taking the indicator measured by the measuring means and time data provided by the clock circuit when each of the indicators is measured, and storing the indicator and the time data in the recording means; Calculating means for extracting an indicator measured at the same past time as the current time from the indicator stored in the recording means, performing a specific calculation, and outputting the calculation result when instructed by a user; Second control means for taking an indicator at the current time measured by the measuring means when instructed by the user; And And notifying means for providing a notification of the calculation result and the indicator at the current time. The method of claim 10, The calculating means calculates a moving average of the indicator measured at a past time equal to the current time; And the notification means provides notification of the moving average and the indicator at the current time. The method of claim 10, The computing means outputs the indicator measured at a past time equal to the current time without modification; And said notifying means provides a notification of a transition over time for said indicator output by said computing means over a particular time period in the past. The method of claim 1, The diagnostic means, Recording means; First control means for taking the indicator measured by the measuring means and time data provided by the clock circuit when each of the indicators is measured, and storing the indicator and the time data in the recording means; Computing means for extracting an indicator measured over a specific time period in the past from the indicator stored in the recording means, when instructed by a user, and obtaining a maximum value among the indicators measured over the past specific time period; At an instruction by the user, taking an indicator at the current time measured by the measuring means, comparing the indicator at the current time with the maximum value, and abnormal when the indicator at the current time is greater than the maximum value Second control means for determining that a state exists or determining that there is no abnormal state when the indicator at the current time is not greater than the maximum value; And And notification means for providing notification of the determination result. The method of claim 13, The computing means obtains a maximum value of the indicators measured during the day and a maximum value of the indicators measured during the night; And the second control means checks whether the current time belongs to day or night, and obtains the maximum value of the day or the maximum value of the night according to the confirmation result. The method of claim 1, The diagnostic means, Recording means; First control means for taking the indicator measured by the measuring means and time data provided by the clock circuit when each of the indicators is measured, and storing the indicator and the time data in the recording means; Computing means for extracting an indicator measured over a specific time period in the past from the indicator stored in the recording means when instructed by a user, and obtaining a minimum value among the indicators measured over the past specific time period; When instructed by the user, an indicator at the current time measured by the measuring means is taken, and the indicator at the current time is compared with the minimum value, and an abnormal state occurs when the indicator at the current time is smaller than the minimum value. Second control means for determining that there is, or determining that there is no abnormal state when the indicator at the current time is not less than the minimum value; And And notification means for providing notification of the determination result. The method of claim 15, The computing means obtains a minimum value of the indicators measured during the day and a minimum value of the indicators measured during the night; And the second control means checks whether the current time belongs to day or night, and obtains the minimum value of the day or the minimum value of the night according to the checking result. The method of claim 1, The diagnostic means, Physical motion detecting means for detecting physical activities of degrees of the body; Recording means; Taking the indicator measured by the measuring means, the time data provided by the clock circuit when each of the indicators are measured, and the body mobility measured by the body motion detecting means over the specific time period, and the indicator First control means for storing together the visual data and the body dynamics in the recording means; At the instruction by the user, the body dynamics measured by the body dynamics detecting means is taken, and the body dynamics closest to the currently measured body dynamics is selected from the body dynamics stored in the recording means; Computing means for outputting an indicator of the living state stored with the selected body dynamics; Second control means for taking an indicator at the current time measured by the measuring means when instructed by the user; And And notification means for providing notification of the indicator output by the computing means and the indicator taken by the second control means. The method of claim 1, And a control means for operating the biological state to a desired state. The method according to any one of claims 1, 2 to 6, 10 to 18, And the indicator of the living state is a circulatory parameter of the body. The method of claim 19, And the cyclic dynamics parameter is determined based on the amplitude of the fundamental wave of the pulse wave, the amplitude of the harmonic wave of the pulse wave, and the phase of the harmonic wave of the pulse wave measured in the body. The method of claim 19, The cyclic dynamics parameter is determined based on a strain obtained from the amplitude of the harmonics of the pulse wave spectrum and the fundamental wave of the spectrum measured in the body, and a relationship between the strain and the cyclic dynamics parameter. Diagnostic device. The method of claim 19, The circulatory dynamics parameter is calculated from a regression equation between the cyclic dynamics parameter and the strain obtained from the amplitude of the harmonics of the pulse wave spectrum, the amplitude of the fundamental waves of the spectrum, and the phase of the spectrum, measured in the body. Device. The method according to any one of claims 1, 2 to 6, 10 to 18, And each of the indicators of the living state is an amplitude of harmonic components of the pulse wave measured in the body. The method according to any one of claims 1, 2 to 6, 10 to 18, Wherein each indicator of the living state is a phase of a harmonic component of a pulse wave measured in the body. The method of claim 24, And wherein the phase of the harmonic component is the phase of the fourth harmonic of the pulse wave spectrum clearly showing the change of the living state. The method according to any one of claims 1, 2 to 6, 10 to 18, Wherein the indicators of the biological state are the amplitudes of the spectral components obtained by calculating the time interval between each pair of consecutive pulses of pulse waves measured in the body and performing spectral analysis on the variation of the time intervals. . The method according to any one of claims 1, 2 to 6, 10 to 18, Each of the indicators of the biometric state comprises two spectral components selected from a plurality of spectral components obtained by calculating a time interval between each pair of consecutive pulses of pulse waves measured in the body and performing a spectral analysis on the variation of the time interval. A living body diagnostic device, wherein the amplitude ratio is. The method according to any one of claims 1, 2 to 6, 10 to 18, Wherein each of the indicators of the biological state is a number of times when the difference between adjacent time intervals between successive pulses of pulse waves measured in the body exceeds a specific time period. The method according to any one of claims 1, 2 to 6, 10 to 18, And each of the indicators of the biological state is a pulse rate of pulse wave measured in the body. The method according to any one of claims 1, 2 to 6, 10 to 18, And the measuring means comprises pulse wave detecting means for detecting pulse wave in the body and extracting an indicator of the living state from the waveform of the pulse wave. The method of claim 30, The pulse wave detecting means includes a pressure sensor, and detects the pulse wave by measuring the pulse pressure using the pressure sensor. The method of claim 30, The pulse wave detecting means is provided with a photoelectric pulse wave sensor having a light emitting element for irradiating light through the blood vessel under the skin of the body and an optical sensor for receiving the light reflected from the blood vessel. The method of claim 30, The apparatus further comprises body dynamics detecting means for measuring body dynamics of the body; And the pulse wave detecting means detects the pulse wave when the body motion currently measured by the body motion detecting means is lower than a specific value. The method of claim 33, wherein And the pulse wave detecting means detects the pulse wave only when the present measured body dynamics remain below the specific value for a specific time period. The method of claim 30, The diagnostic means, Body dynamics detection means for measuring the body dynamics of the body; Storage means; And Stores the pulse wave detected by the pulse wave detection means and the body dynamics measured by the body motion detecting means over a specific time period, extracts the stored pulse wave together with the body dynamics lower than a specific value, and extracts the extracted pulse wave. An apparatus for diagnosing a living body, comprising extracting means for outputting as a pulse wave in a resting state of the body. The method of claim 30, The apparatus further comprises command detection means for detecting a pulse wave measurement instruction from a user; And the pulse wave detecting means detects the pulse wave when a pulse wave measuring instruction is detected by the instruction detecting means. The method according to any one of claims 1, 2 to 6, 10 to 18, The apparatus further comprises body dynamics detecting means for measuring body dynamics; And the measuring means measures the indicator of the living state based on the body dynamics measured by the moving body detecting means. The method according to any one of claims 1, 2 to 6, 10 to 18, And the indicator of the living state is corrected based on an annual variation of the living state. The method according to any one of claims 1, 2 to 6, 10 to 18, And the indicator of the biometric state is corrected based on ambient temperature. The method according to any one of claims 1, 2 to 6, 10 to 18, The apparatus further includes means for performing notification by vibrating a piezoelement attached to a recess provided in a portable device including the apparatus, wherein the diameter of the piezo element is about 80% of the diameter of the recess. , Biometric diagnostic device. The method according to any one of claims 1, 2 to 6, 10 to 18, And the apparatus further comprises communication means for transmitting and receiving data to and from an external device provided external to the apparatus, the data comprising an indication of the biometric status. 42. The method of claim 41 wherein The communication means is assigned a unique identification number, and the communication means adds the unique identification number to data transmitted to the external device. 42. The method of claim 41 wherein And the data transmitted to and received from the external device is compressed data.

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