JP3296137B2 - Drug ejection device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a drug ejection device for performing a process such as relaxation by ejecting a drug.

[0002]

2. Description of the Related Art At the present time, there is increasing public interest in relaxation, and there is a demand for relaxation means that can be easily used in daily life. As a means for this kind of relaxation, the sedative action of perfume has been conventionally used. An example that has been used for a long time is a form of utilization in which incense is burned down. Further, a recent air conditioner or the like in which a fragrance is mixed with air to blow air is used.

[0003]

In order to prevent stress from accumulating, it is preferable to perform relaxation at an appropriate frequency. However, busy modern people tend to neglect such relaxation. In the first place, it is impossible to pay attention to relax yourself, and a means for relaxation that does not require such efforts is desired.

In order to prevent the accumulation of stress, appropriate relaxation is required, but it is not always necessary to always perform only relaxation. That is,
In order to live a truly healthy life, it is preferable to properly switch between a sedated state and an excited state, such as a sedated state when resting and a moderately excited state when working.

The present invention is directed to responding to such a demand, and automatically discharges a fragrance at an appropriate timing without bothering the user, and the user is in an excited state or a sedated state. It is an object of the present invention to provide a drug ejection device capable of controlling an internal state.

[0006]

Means for Solving the Problems and Their Functions
The invention according to the invention relates to a measuring means for measuring a state of a living body, a storage means for storing the state of the living body measured up to the present time, and a time when a drug should be ejected based on a fluctuation rhythm of the state of the living body in the past. And a control unit that outputs a drug ejection command at that time, and an ejection unit that ejects a drug in accordance with the drug ejection command. The invention according to claim 2 is characterized in that the control means selects a time zone in which the state of the living body changes with a predetermined tendency, and outputs the drug ejection command in the time zone. The drug ejection device described above is a gist. According to these inventions, the timing at which the drug is to be ejected is determined based on the fluctuation rhythm of the state of the living body, so that an operation such as suppression or promotion of an excitable state or suppression or promotion of a sedation state due to drug ejection is performed at an optimal timing. Can be done automatically.

According to a third aspect of the present invention, there is provided a measuring means for measuring a state of a living body, a storage means for storing the state of the living body measured up to the present time, a change rhythm of the state of the living body in the past and a present state. The gist of the present invention is a drug ejection device comprising: control means for outputting a drug ejection command based on a state of a living body; and ejection means for ejecting a drug in accordance with the drug ejection command. Claim 4
In the invention according to the invention, the control means selects a time zone during which the state of the living body changes with a predetermined tendency, and when the state of the living body changes with a different tendency from the past in the time zone, the drug The gist of the drug ejection device according to claim 3 is to output an ejection command. Further, in the invention according to claim 5, the control means selects a predetermined time period, and the state of the living body in the time period is a fixed amount from a moving average of the state of the living body in the time period in a past predetermined period. The gist of the drug ejection device according to claim 3, wherein the medicine ejection command is output when the device is separated from the above.
According to these inventions, since the ejection of the drug is controlled based on the fluctuation rhythm of the state of the living body in the past and the current state of the living body, the drug is controlled so as to change the state of the living body according to a certain rhythm fluctuation waveform. Can be discharged.

According to a sixth aspect of the present invention, the state of the living body is represented by an element of an electric circuit model imitating a system extending from the central part to the peripheral part of the arterial system of the human body, and the measuring means The drug ejection device according to any one of claims 1 to 4, wherein a pulse wave is measured from the living body, and a value of an element of the electric circuit model is determined based on the pulse wave. Make a summary. In the invention according to claim 7, the measuring means measures the amplitude of the fundamental wave and the amplitude and phase of the harmonic wave of the pulse wave from the living body, and determines the value of the element of the electric circuit model based on the measurement result. The gist of the drug ejection device according to claim 6 is as follows. The invention according to claim 8, wherein the measuring means measures the amplitude of the fundamental wave and the amplitude and phase of the harmonic wave of the pulse wave from the living body, calculates the distortion rate of the pulse wave from the measurement result, and calculates the distortion rate. And determining a value of the element of the electric circuit model from a regression equation between the distortion factor and a value of the element of the electric circuit model.
The drug ejection device described above is a gist.

According to a ninth aspect of the present invention, the electric circuit model corresponds to a first resistance corresponding to vascular resistance due to blood viscosity at the central part of the arterial system, and an inertia of blood at the central part of the arterial system. An inductance, a capacitance corresponding to the viscoelasticity of the blood vessel at the central part of the artery, and a second resistance corresponding to the vascular resistance at the peripheral part, wherein the first resistance is provided between a pair of input terminals. 9. A drug according to claim 6, wherein the drug is a four-element lumped-constant model in which a series circuit consisting of an inductance and a parallel circuit consisting of the capacitance and the second resistor are sequentially inserted in series. The gist of the discharge device is as follows. According to these inventions, since a parameter directly representing the circulatory system of the human body is used as information representing the state of the living body, it is possible to accurately determine the state of the living body and control drug ejection. . In the invention according to claim 10, the state of the living body is represented by a phase or an amplitude of a harmonic component of a pulse wave of an artery of a human body, and the measuring unit measures a pulse wave from the living body. The gist of the drug ejection device according to any one of claims 1 to 4, wherein an amplitude or a phase of a harmonic component of the pulse wave is measured from the measurement result.

According to an eleventh aspect of the present invention, the condition of the living body is based on a ratio of amplitudes of two spectral components of a low frequency component and a high frequency component obtained from a time interval variation of a pulse wave of an artery of a human body. The measuring means measures a pulse wave from the living body, calculates a time interval between adjacent pulse waves,
The gist of the drug ejection device according to any one of claims 1 to 5, wherein a spectrum component of a low frequency and a spectrum component of a high frequency are obtained from a spectrum analysis of the fluctuation of the time interval. According to the twelfth aspect of the present invention, the state of the living body is based on the number of time interval fluctuations of the pulse wave of the artery of the human body, and the measuring means measures the pulse wave from the living body and detects the adjacent pulse. The method according to claim 1, wherein a time interval of the wave is calculated, and the number of continuous fluctuations of the time interval exceeding a predetermined time is output as the number of fluctuations.
A gist of the drug ejection device according to any one of the above items 5 is provided. According to these inventions, since the measured amount representing the circulatory system of the human body is used as information representing the state of the living body,
It is possible to accurately determine the state of a living body and control drug ejection.

[0013] The invention according to claim 13 is characterized in that it comprises means for determining the discharge amount of the drug, and notifying when the integrated value of the discharge amount reaches a predetermined amount. The gist of the present invention is a drug ejection device according to any one of claims 1 to 12. According to this invention, the user can know that it is time to replenish the drug. The invention according to claim 14 is characterized in that it comprises means for monitoring whether or not the ejection of the drug is performed normally, and notifying the operator when there is an abnormality. The gist of the present invention is a drug ejection device. According to this invention, when the ejection of the drug is not performed normally, the user is immediately notified of the fact, so that the treatment such as adjustment of the ejection unit can be performed quickly.

According to a fifteenth aspect of the present invention, there is provided a drug ejection device which is carried and used and operates based on a voltage supplied from a battery, wherein an output voltage of the battery is intermittently measured by the measuring means and the control means. And a power supply control means for supplying power to said discharge means.
A gist of the drug ejection device according to any one of claims 14 to 14. According to the invention, since the device is portable, the drug ejection device can be used while performing daily life. Further, since the voltage of the battery is intermittently supplied to each section, the power consumption can be kept low and the battery can be used for a long time.

According to a sixteenth aspect of the present invention, there is provided a drug ejection device according to the fifteenth aspect, further comprising means for notifying when the output voltage of the battery has fallen below a predetermined voltage. . According to this invention, the user can know that it is time to replace the battery. The invention according to claim 17 is provided with a sensor worn on a human body, wherein the sensor measures the movement of the living body and compensates for the state of the living body based on the measurement result. The gist is a drug ejection device according to any one of the above items. According to this invention, even when the user is exercising, it is possible to accurately grasp the state of the living body and perform accurate drug ejection control.

The invention according to claim 18, wherein the measuring means measures the pulse wave by measuring a pulse pressure. The drug ejection according to any one of claims 6 to 17, wherein The device is the gist. The invention according to claim 19 is
18. The method according to claim 6, wherein the measuring unit irradiates a blood vessel under the skin with light and receives the reflected light reflected by the blood vessel to detect the pulse wave. The gist is the drug ejection device described in the paragraph.

According to a twentieth aspect of the invention, there is provided a case having the storage means and the control means therein, the discharge means being provided on a surface thereof, the case being attached to a chain of a necklace, and the measuring means being provided with: A case in which the case is attached to the chain of the necklace, a light emitting element that irradiates light to blood vessels under the skin, and a photoelectric sensor that receives light reflected by the blood vessels under the skin. The gist of the drug ejection device according to any one of claims 6 to 17, wherein the pulse wave is measured by a pulse wave sensor.

According to a twenty-first aspect of the present invention, there is provided a case in which the storage means and the control means are incorporated, and the discharge means has a case provided on a surface thereof, the case is attached to a vine of a frame of spectacles, The means includes: a light emitting element that irradiates light to a blood vessel under the skin; and a light sensor that receives light reflected by the blood vessel under the skin. The gist of the drug ejection device according to any one of claims 6 to 17, wherein the measurement is performed.

According to these inventions, since the drug ejection device is incorporated in the necklace or eyeglasses worn on a daily basis, the user can wear the drug ejection device without special awareness and can easily carry the drug ejection device. It is possible to provide a discharge device. Furthermore, light is emitted from the light emitting element to the blood vessel under the skin, and the reflected light from the blood vessel is received by the optical sensor, so that the pulse wave can be easily measured for any part of the human body. The range of choices can be expanded.

[0018]

Embodiments of the present invention will be described below with reference to the drawings. In the following examples, a description will be given by taking a fragrance as an example of a drug.

A. Prior study The inventor of the present application made the following preliminary study when designing the drug ejection device according to the present embodiment.

(1) Confirmation of the Effect of Fragrance There is a close relationship between a human state such as an excited state and a sedated state and the circulatory parameters of the person, and the human body is changed from the sedated state to the excited state or from the excited state to the excited state. It is known that a change to a sedated state appears as a change in circulatory parameters such as vascular resistance. Therefore, the inventor of the present application has determined the effect of the fragrance by examining the behavior of the circulatory dynamic parameters of the human body when the fragrance is smelled.

Measurement Method Seven males aged 23 to 39 were used as subjects. For each subject, smell the lavender and sandalwood aroma oil, and measure the subject's stroke volume, radial artery wave, etc. at each time before, during, and after the smell. did.

Analysis The inventor of the present application assumes that the circulatory dynamic parameters of the human body constitute a four-element lumped parameter model shown in FIG. 17, and how each element of the four-element lumped parameter model changes over time. I decided to check. This four-element lumped parameter model is based on the circulatory parameters that determine the behavior of the circulatory system of the human body, including the inertia of blood in the central part of the arterial system, the vascular resistance (viscous resistance) due to blood viscosity in the central part, Focusing on four parameters of blood vessel compliance (viscoelasticity) and peripheral blood vessel resistance (viscous resistance), these are modeled as an electric circuit. The correspondence between each element constituting the four-element lumped parameter model and each of the above parameters is as follows.

Inductance L: inertia of blood at the central part of the arterial system [dyn · s ² / cm ⁵ ] Capacitance C: compliance (viscoelasticity) of blood vessels at the central part of the arterial system [cm ⁵ / dyn] Compliance is a quantity representing the softness of a blood vessel, and is viscoelasticity. Electric resistance R _c : vascular resistance due to blood viscosity at central part of arterial system [dyn · s / cm ⁵ ] Electric resistance R _p : vascular resistance due to blood viscosity at peripheral part of arterial system [dyn · s / cm ⁵ ]

The currents i, i _P , and _ic flowing through the respective parts in the electric circuit are determined by the blood flow [cm ³ / cm] flowing through the corresponding parts.
s]. The input voltage e applied to this electric circuit corresponds to the pressure [dyn / cm ² ] at the aortic root.
The terminal voltage v _P of the capacitance C corresponds to the pressure [dyn / cm ² ] at the radial artery.

In general, the pressure waveform at the aortic root is shown in FIG. 18, but this pressure waveform is approximated by a triangular wave shown in FIG. In FIG. 19, E _o is the diastolic blood pressure (diastolic blood pressure), E _o + E _m is the systolic blood pressure (systolic blood pressure), t _P is the time of one beat, and t _P1 is the diastolic blood pressure from the rise of the aortic pressure. It is the time to reach a value.

The inventor of the present application considers that when a circulatory dynamic parameter corresponding to the radial artery wave and the stroke volume measured from each subject, that is, a triangular wave shown in FIG. The values of the respective elements R _c , R _p , C, and L of the four-element lumped constant model as conditions for obtaining the same waveform as the radial artery wave at both ends of the capacitance C were obtained. A method of mathematically calculating the values of the respective elements R _c , R _p , C, and L of the four-element lumped constant model from the radial artery waveform and the stroke volume is described in Japanese Patent Application No. It is disclosed in Japanese Patent Laid-Open No. 5-1431.

Results In this experiment, it was confirmed that the circulatory dynamic parameters were changed by the fragrance. Data for stroke volume SV and blood vessel resistance R _P of the experimental data obtained in this study are shown in Figure 20. In the figure, the abscissa has a notation indicating the measurement time point, of which “before” is the time point before smelling the incense, and “middle” is the time point after 6 minutes from the start of smelling the incense. At the time,
"Immediately" means a point in time three minutes after the incense was stopped, and "after" means a point in time six minutes after the incense was stopped.

As shown in FIG. 20, a significant increase in vascular resistance R _P (ie, transition to a sedated state) by smelling the lavender scent was significant when smelling the sandalwood scent. Increase in stroke volume SV, vascular resistance R
A decrease in _P (ie, transition to an excitable state) was observed. As described above, the preliminary examination conducted this time confirmed that lavender had a sedative effect and sandalwood had an excitatory effect.

(2) Confirmation of rhythm fluctuation of circulatory dynamics It is known that a human state repeats an excited state and a sedated state in accordance with a regular rhythm with one cycle per day.
An object of the present invention is to control a human state to a preferable state by discharging a fragrance, but in examining means for achieving this object, an original state of the human state when no operation is performed is considered. It is necessary to understand the behavior. Therefore, the inventor of the present application has confirmed the state of the rhythm variation of the human condition by examining the temporal change of the human circulatory dynamic parameters.

Measurements Thirteen healthy adult men (age 21 ± 9)
The same behavior was performed in the same facility for 36 hours a day. The temperature is 24.0-24.5 ° C and the humidity is 40-
It was kept at 50%. Meals were provided at noon and 6:00 pm.
Also, the same menu for two days, about 1700 per day
Gave a Kcal meal. He went to bed at midnight and waked up at 6:00 the next morning and was given six hours of sleep. Then, the radial artery waveform and the stroke volume were measured every two hours. Upon measurement, the subject was allowed to sit in a resting position for 15 minutes before measurement.
During the measurement, a steady breath was made in a resting position in accordance with a 0.25 Hz metronome. After the start of measurement,
An average added waveform for one beat was obtained from 10 heartbeats after 0, 40, and 50 seconds, and was used as an analysis target described in the next section.

Analysis From the radial artery waveform and the stroke volume collected from each subject, each of the elements R _c , R _p ,
The values of C and L were determined.

Results FIG. 21 shows each element R _c , R _p ,
For each of C and L, the average value of 13 test subjects is compared with a daily fluctuation waveform obtained by synthesizing a fundamental wave spectrum and a second harmonic spectrum obtained by rhythm analysis. According to the measurement results obtained this time, although there are individual differences in the circadian variation waveforms of the circulatory dynamic parameters R _c , R _p , C, and L, all subjects have common features. . That is, the values of R _c , R _p , and L are large in the morning, gradually decrease toward noon, rise again after a small peak occurs in the evening. The value of C tends to be high in the first half of the day and to decrease in the second half.

Based on the results of the above preliminary study, the points to be considered when designing the drug ejection device according to the present embodiment are as follows. a. Since the effect differs depending on the fragrance, it is necessary to determine the type of fragrance based on the desired effect. b. The amplitude of the diurnal rhythm is quite large. Therefore, even if the human state is controlled by the fragrance, the discharge of the fragrance should not be controlled based only on the current value of the circulation dynamics parameter, but must be performed in consideration of the rhythm of the daily fluctuation. c. The values of hemodynamic parameters vary greatly between individuals. Therefore, it is necessary to control the discharge of the fragrance based on the circadian rhythm of the user's circulatory dynamic parameters.

B. Embodiment §1. 1. First Example (1) Outline of Example From the above preliminary examination, it was confirmed that a human is originally to be repeatedly excited and sedated according to a certain rhythm. Here, there is no problem if a person having a good rhythm as a change / excitation state change rhythm is maintained for a long period of time. However, if the rhythm breaks, you should perform an operation to restore the original rhythm. Also, those who do not want to be in an extremely excited state or a sedated state may need to perform an operation to avoid falling into such a state. In addition, for a person who tends to be in a sedated state, an operation for appropriately shifting to an excited state may be necessary. In addition, a person who is always in an excited state will need an operation to appropriately shift to a sedated state.

The drug ejection device according to the present embodiment periodically measures the circulatory dynamics of a user, and ejects a fragrance as needed based on the measurement result. As described above, the circulatory dynamics vary in rhythm with a cycle of one day. Therefore, it is not possible to determine whether to discharge the fragrance only from the circulatory dynamics at a specific time. Therefore, taking into account the rhythm fluctuation of the circulation dynamics, the control of the fragrance discharge is performed based on each parameter value of the current circulation dynamics. Further, how to operate the fluctuation rhythm of the excited state / the sedated state is preferable depending on the user. Therefore, the user can select a desired control mode in which state the fragrance should be discharged.

FIGS. 10 to 16 show the modes of the fragrance discharge control 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 / sedation state), and the broken line indicates the temporal change of the user's state controlled by the spice discharge. is there. Each mode of the fragrance discharge control in the present embodiment shown in these figures will be described as follows.

Mode 1: The user emits a sandalwood scent having an excitatory action during the transition to the sedative state, thereby suppressing the transition to the sedated state (see FIG. 10). It is suitable for users who do not want to be in an extremely sedated state. Mode 2: The user emits sandalwood incense having an excitatory action during the time of transition to the excited state, thereby promoting the transition to the excited state (see FIG. 11). It is suitable for a user who needs to quickly recover from a sedated state. Mode 3: The scent of lavender having a sedative effect is released during the time when the user shifts to the excited state, and the shift to the excited state is suppressed (see FIG. 12). It is suitable for a user who does not want to be in an extremely excited state. Mode 4: The user releases a scent of lavender having a sedative effect during a time period when the user shifts to the sedated state, thereby promoting the shift to the sedated state (see FIG. 13). It is suitable for a user who needs to quickly recover from an excited state. Mode 5: When the user shifts to the excited state, the lavender scent is released to suppress the shift to the excited state, and when the user shifts to the sedated state, the sandalwood scent is released to the sedated state. (See FIG. 14). It is suitable for a user who needs to keep the state constant. Mode 6: When the user transitions to the excitement state, she emits sandalwood incense to promote the transition to the excitement state, and when the user transitions to the sedation state, she releases the lavender incense to enter the sedation state. (See FIG. 15). This is suitable for attaching a rhythm to life. Mode 7: When there is a change contrary to the change rhythm of the excitement state / sedation state in the past, a fragrance for suppressing the change is discharged. That is, when the transition to the sedated state is recognized in the time zones A and C during which the transition to the excited state is normally made, the scent of sandalwood is released, and the transition to the sedated state is suppressed. Also,
Normally, when the transition to the excitable state is recognized in B and D during the period of transition to the sedated state, the scent of lavender is released and the transition to the excited state is suppressed (see FIG. 16).
It is effective in suppressing sudden excitement and sedation.

(2) Configuration of the Embodiment FIG. 1 is a block diagram showing the functional configuration of the drug ejection device according to the present embodiment. As shown in the drawing, in the present embodiment, a pulse wave detecting unit 200 and a first fragrance discharging unit 3
00 and the second fragrance discharging section 400 are connected. The pulse wave detector 200 is a unit provided for measuring a radial artery waveform from a patient. The first and second fragrance discharging units 300 and 400 are means provided for releasing lavender and sandalwood incense, respectively. Also,
The drug ejection device according to the present embodiment includes a battery 500 and a power supply control unit 501 for performing intermittent power supply.
The power supply control unit 501 includes the control unit 100, the pulse wave detection unit 20
0, first fragrance discharging section 300 and second fragrance discharging section 400
Supplies the output voltage of the battery 500 to each unit only during a period during which power supply is required (for example, a period during which arithmetic processing is performed for the control unit 100 and a period during which a fragrance is discharged in the case of a fragrance discharging unit). As described above, since the voltage of the battery 500 is intermittently supplied to each unit, power consumption can be suppressed low, and the device can be operated for a long time. The output voltage of the battery 500 is
The microcomputer is monitored by a microcomputer (described later), and when the voltage falls below a predetermined voltage, a notification to that effect is given.

FIG. 2 shows the overall configuration of the drug ejection device according to the present embodiment, wherein (a) is a perspective view showing the external appearance,
FIG. 2B is a sectional view taken along line AA ′ of FIG. As shown in this figure, this drug ejection device is a portable device incorporated in a wristwatch. In FIG. 2A, reference numeral 13 denotes a pressure sensor, and reference numeral 12 denotes a fixture. These components constitute the pulse wave detection unit 200 in FIG. Here, the pressure sensor 13 is attached to the surface of the attachment 12, and the attachment 12 is slidably attached to the watch band 11. Then, when the wristwatch is worn on the wrist, the pressure sensor 13
Is pressed against the radial artery with moderate pressure. The pressure sensor 12 is constituted by a strain gauge or the like, and a pulse wave signal (analog signal) representing the radial artery waveform of the user is obtained from both ends of the pressure sensor 12. This pulse wave signal is taken into a control unit 100 (not shown in FIG. 2; see FIG. 1) incorporated in the watch main body 10 via a signal line (not shown) embedded in the band 11 for the detection watch.
The cross-sectional structure of the mounting portion of the watch band 11 in the watch main body 10 is as shown in FIG. 2B, and the tank 361, the micro pump 301, and the like are built in this portion. These constitute the first fragrance discharging section 300 in FIG. The micro pump 301 is connected to the control unit 100
Lavender is pumped from the tank 361 via the tube 305T according to the drive command sent from. The pumped-up fragrance is ejected to the outside from the ejection hole 16 formed on the surface of the timepiece body 10 through the tube 306T. The watch main body 10 further includes a built-in counterpart to the second fragrance discharging section 400 in FIG. 1, but is not shown in order to avoid complication. The sandalwood fragrance pumped up by the second fragrance discharging unit 400 is injected from the injection holes 17 to the outside. The configuration of the micro pump 301 and the like will be described later in detail.

Next, the configuration of the control unit 100 will be described with reference to FIG. The control unit 100 includes a memory 1, an input unit 2, an output unit 3, a waveform extraction storage unit 4, and a microcomputer 5. The memory 1 is a non-volatile memory including a battery-backed-up RAM (random access memory) or the like, and is used for temporary storage of control data when the microcomputer 5 controls other units. Further, in a predetermined storage area of the memory 1, circulating dynamic parameters measured at a plurality of different times are stored.

The input unit 2 is a means provided for inputting various commands to the microcomputer 5 such as an instruction for setting any one of the above-mentioned modes 1 to 7, and is shown in FIG. The watch is composed of a crown and the like provided on the watch main body 10. The output unit 3 includes a liquid crystal display device, an alarm sound generation device, and the like (both not shown) provided in the watch main body 10.

The waveform extraction storage unit 4 captures a detection signal obtained from the pulse wave detection unit 200 under the control of the microcomputer 5, and extracts a pulse wave of one wavelength (one beat) from the captured signal. To remember. Here, the configuration of the waveform extraction storage unit 4 will be described with reference to FIG. In FIG. 3, reference numeral 101 denotes an A / D (analog / digital) converter, which converts a pulse wave signal output by the pulse wave detector 200 into a digital signal in accordance with a sampling clock φ having a constant period, and outputs the digital signal. Reference numeral 102 denotes a low-pass filter which performs a process of removing components having a predetermined cut-off frequency or higher from a digital signal sequentially output from the A / D converter 101, and sequentially outputs the result as a waveform value W. Reference numeral 103 denotes a waveform memory constituted by a RAM, which sequentially stores the waveform values W supplied via the low-pass filter 102. Reference numeral 111 denotes a waveform value address counter, which is a waveform sampling instruction STA from the microcomputer 5.
While RT is being output, the sampling clock φ is counted, and the count result is supplied to the address input terminal of the waveform memory 103 as the waveform address ADR1 where the waveform value W is to be written. Also, this waveform address ADR
1 is monitored by the microcomputer 5.

Reference numeral 121 denotes a differentiating circuit which calculates and outputs the time derivative of the waveform value W sequentially output from the low-pass filter 102. Reference numeral 122 denotes a zero cross detection circuit, which outputs a zero cross detection pulse Z when the time derivative of the waveform value W becomes zero. More specifically, the zero cross detection circuit 1
Reference numeral 22 denotes a peak point P in the pulse wave waveform illustrated in FIG.
A circuit provided for detecting 1, P2,...
When a waveform value W corresponding to these peak points is input, a zero cross detection pulse Z is output. Reference numeral 123 denotes a peak address counter, which counts the zero-cross detection pulse Z while the microcomputer 5 outputs the waveform sampling instruction START, and outputs the count result as a peak address ADR2. Reference numeral 124 denotes a moving average calculation circuit that calculates the average value of the time differential values of a predetermined number of past waveform values W output from the differentiating circuit 121 up to the present time, and calculates the result as the pulse wave gradient up to the current time. Is output as inclination information SLP representing Reference numeral 125 denotes a peak information memory provided for storing peak information described later.

The microcomputer 5 controls each unit in the control unit 100 according to a command input through the input unit 2. The microcomputer 5 has a built-in clock circuit, and performs the following timer interrupt processing every time a predetermined time elapses.

Control of pulse wave signal fetching processing and pulse wave extraction processing for one wavelength by the waveform extraction storage unit 4 The peak point of the pulse wave is determined by the differentiation circuit 121 and the zero-cross detection circuit 122 in the waveform extraction storage unit 4. Each time it is detected, the information listed below (hereinafter collectively referred to as peak information) is obtained and written to the peak information memory 125 in accordance with the table format shown in FIG.

(Contents of Peak Information) Waveform value address ADR1: Write address ADR1 output from waveform address counter 111 when waveform value W output from low-pass filter 102 reaches a maximum value or a minimum value, that is, This is a write address in the waveform memory 103 of the waveform value W corresponding to the maximum value or the minimum value. Peak type B / T: Information indicating whether the waveform value W written in the waveform value address ADR1 is a local maximum value T (Top) or a local minimum value B (Bottom). Waveform value W: a waveform value corresponding to the maximum value or the minimum value. Stroke STRK: A change in waveform value from the immediately preceding peak value to the peak value. Slope information SLP: Average value of time derivative of a predetermined number of waveform values in the past up to the peak value.

Calculation of Circulation Kinetic Parameters The waveform value of the pulse wave for one wavelength is read out from the waveform memory 103 based on the above-mentioned peak information, and the pulse wave for one wavelength is read based on the pulse wave. That is,
The value of each element of the above-described four-element lumped parameter model is obtained.
In this case, first, the waveform of the pulse wave read from the waveform memory 103 is subjected to Fourier analysis, so that the amplitudes I, I2, I3,. Find P2, P3, P4 ... Next, the distortion factor d of the pulse wave is obtained from the obtained amplitude values I, I2, I3,. d = √ (I2 ² + I3 ² +... + In ² ) / I Then, from the regression formula of the distortion factor d, the phase P2, P3. Ask for. Next, a regression equation is shown. Rc (dyn · s / cm ⁵ ) =-179.00 × d + 2.275 × P5 + 2.295 × P2 + 7
26.74 (R ² = 0.86, P <0.00001, n = 106) Rp (dyn ・ s / cm ⁵ ) = 6.90 × P5-391.5 × d + 192.3 (R ² = 0.49, P <0.00001, n = 106) or Rp (dyn · s / cm ⁵ ) = 0.68 × P2-788.10 × d + 1957.
3 (R ² = 0.30, P = 0.008, n = 106) L (dyn ・ s ² / cm ⁵ ) =-31.40 × d + 0.16 × P5 + 11.50 (R ² = 0.74, P <0.00001, n = 106) C (cm ⁵ /dyn)=2.34×d−0.007×P5+0.69 (R ² = 0.74, P <0.00001, n = 106) In the above equation, R ² is the coefficient of determination, P is the risk factor, and n is The number of samples.

These regression formulas measure radial artery waves for a large number of subjects and obtain the amplitude and phase of the fundamental wave and harmonics by performing Fourier analysis on the measured pulse waves.
On the other hand, for each subject, the value of each element of the four-element lumped parameter model of FIG. 17 described above from the stroke volume and the radial artery waveform, that is, the hemodynamic parameters, and the amplitude, phase, It is obtained by determining the correlation of the parameters. Next, the circulatory dynamic parameters obtained in this way are stored in the memory 1 together with information indicating the measurement time of the pulse wave. By repeating the above processing at regular time intervals, the circulating dynamic parameters at each time are accumulated in the memory 1.

The microcomputer 5 controls the fragrance discharge of the first fragrance discharging unit 300 and the second fragrance discharging unit 400 with reference to the circulation dynamic parameters in the past fixed period stored in the memory 1. Note that this control will be described together with the description of the operation of the present embodiment, and redundant description here will be avoided.

FIG. 6 shows the structure of the first fragrance discharging section 300 (second fragrance discharging section 400). As shown in this figure, the micro pump 301 has an input port 305 connected to the tube 30.
It is inserted into the tank 361 via 5T, and the output port 306 is connected to a tube 306T for injection. The drive circuit 363 receives a drive command from the microcomputer 5 and operates at a predetermined level (about 100
A driving pulse V) is generated and supplied to the piezoelectric element 326 as a driving unit of the micro pump 301. Oscillation circuit 364
Generates a number of pulses having a cycle shorter than the pulse width of the drive pulse, and applies the pulses to the operation detection switch 350 of the micro pump 301 via the capacitor C and the resistor R.
Here, the operation detection switch 350 is connected to the micro pump 3
Each time the liquid is discharged from the output port 306 of No. 01, it is turned on for a predetermined time width. Therefore, when the micropump 301 is operating normally, a drive pulse is applied to the micropump 301, and every time the liquid is discharged by this, the operation detection switch 35 is turned on.
The voltage at both ends of 0 will decrease. Abnormality detection circuit 3
65 rectifies the voltage across the operation detection switch 350,
If the level of the voltage obtained by this rectification does not change with time corresponding to the drive pulse, an abnormality detection signal is output.

FIG. 7 is a sectional view of the micropump 301 constituting the fragrance discharging section. This micro pump 301
Is based on a sandwich structure of a substrate 302, a thin film plate 303 and a surface plate 304.

The substrate 302 is made of, for example, a glass substrate having a thickness of about 1 mm, and is provided with an input port 305 and an output port 306. Tubes 305T and 306T are joined to these ports by an adhesive so as not to leak liquid.

The thin film plate 303 is made of, for example, a Si substrate having a thickness of about 0.3 mm. An inlet valve 307 and an outlet valve 308 are formed by an etching method, and a diaphragm 309 is formed between these valves. Further, the pump chamber 32 below the diaphragm 309
2 and a pump channel system leading to the pump 2 are formed.
A piezoelectric element 326 made of a piezo disk is adhered to the upper part of the diaphragm 309 as a driving means.

The inlet valve 307 is formed so as to cover the substrate 302, and the through hole 3 is formed substantially at the center of the upper plane portion.
A valve element 316 is formed to project downward so as to surround the through hole 318. This valve 3
The chamber 16 is formed by the side of the inlet valve 307 and the valve body 316. The chamber 317 communicates with the input port 305 via a flow path (not shown). On the other hand, the outlet valve 308 includes a cap-shaped valve body 325 that covers the inlet of the output port 306.

A surface plate 304 made of a glass substrate similar to the substrate 302 is adhered on the thin film plate 303 by an anodic bonding method. An upper wall is configured. A window 328 is formed on the surface plate 304 at a position corresponding to the diaphragm 309. The piezoelectric element 326 is bonded to the surface of the diaphragm 309 exposed through the window 328. The thickness of the face plate 304 is about 1 mm.

Next, the operation detection switch 350 will be described. The operation detection switch 350 is connected to the outlet valve 30.
8 is provided to detect the behavior of the partition wall, and a projection 351 projecting above the partition wall,
1, an electrode plate 352 adhered to the surface of the
2 is formed by a back electrode plate 353 bonded to a lower portion of the front plate 304 so as to face the second electrode 2. Here, an output pulse of the oscillation circuit 364 is applied to the electrode plates 352 and 353 via the capacitors C and R. Electrode plate 35
2 and 353 are, for example, Pt-Ir, W, T
a, Ni, Pt, Pd, Mo, Ti, polycrystalline Si, WS
A contact material such as i ₂ , CP1, CP2 is used.

(3) Operation of Embodiment The operation of this embodiment will be described below. Periodic Measurement of Circulation Parameters As described above, the microcomputer 5 is periodically interrupted by a timer. As a result, the following processing is executed by the microcomputer 5 as a timer interrupt routine.

First, a process for collecting a waveform and its peak information is executed. This process will be described in detail. First, the microcomputer 5 outputs a waveform sampling instruction START, and the waveform address counter 111 and the peak address counter 12 in the waveform extraction storage unit 4.
3 is released. As a result, the count of the sampling clock φ is started by the waveform address counter 111, and the count value is supplied to the waveform memory 103 as the waveform address ADR1. Then, the radial artery waveform detected by the pulse wave detection unit 200 is input to the A / D converter 101, and is sequentially converted into a digital signal in accordance with the sampling clock φ.
Are sequentially output as waveform values W through The waveform values W output in this manner are sequentially supplied to the waveform memory 103, and are written into a storage area specified by the waveform address ADR1 at that time. By the above operation, FIG.
A series of waveform values W corresponding to the radial artery waveform illustrated in FIG.

On the other hand, in parallel with the above operation, detection of peak information and writing to the peak information memory 125 are performed as described below. First, the low-pass filter 102
Is calculated by the differentiating circuit 121, and the time differential is calculated by the zero-cross detection circuit 12
2 and the moving average calculation circuit 124. The moving average calculation circuit calculates the average value (ie, moving average value) of a predetermined number of time differential values in the past each time the time differential value of the waveform value W is supplied in this way, and outputs the calculated result to the slope information S.
Output as LP. Here, when the waveform value W is rising or has finished rising and is in the maximum state, the inclination information S
A positive value is output as LP, and a negative value is output as the slope information SLP when it is in the minimum state during or after the descent.

For example, when the waveform value W corresponding to the local maximum point P1 shown in FIG. 4 is output from the low-pass filter 102, 0 is output from the differentiating circuit 121 as the time differentiation, and the zero-cross detecting circuit 122 detects the zero-cross. Pulse Z
Is output. As a result, the microcomputer 5 causes the waveform address ADR1, which is the count value of the waveform value address counter 111, the waveform value W, and the peak address A, which is the count value of the peak address counter, at that time.
DR2 (in this case, ADR2 = 0) and inclination information SL
P is taken in. Further, the count value ADR2 of the peak address counter 123 becomes 2 by outputting the zero cross detection signal Z.

Then, the microcomputer 5 determines the peak type B / P based on the sign of the acquired inclination information SLP.
Create T. As in this case, the waveform value W of the maximum value P1
Is output at this point in time, the microcomputer 5 sets the value of the peak information B / T to correspond to the maximum value. Then, the microcomputer 1 converts the peak address ADR2 (in this case, ADR2 = 0) fetched from the peak address counter 123 into the write address ADR3.
And the waveform value W, the waveform address ADR1 corresponding to the waveform value W, the peak type B / T, and the slope information SLP
As the first peak information, the peak information memory 125
Write to. In the case of the first writing of the peak information, the stroke information is not created or written because there is no immediately preceding peak information.

Thereafter, when the waveform value W corresponding to the minimum point P2 shown in FIG.
As described above, the zero cross detection pulse Z is output, and the write address ADR1, the waveform value W, and the peak address ADR2
(= 1), the inclination information SLP (<0) is taken in by the microcomputer 5. Then, similarly to the above, the microcomputer 1 determines the peak type B / T (in this case, bottom B) based on the inclination information SLP. Further, the microcomputer 5 supplies an address smaller than the peak address ADR2 by 1 to the peak information memory 125 as the read address ADR3, and reads the first written waveform value W.
Then, the microcomputer 5 calculates a difference between the waveform value W fetched this time from the low-pass filter 102 and the first waveform value W read from the peak information memory 125, thereby obtaining stroke information STRK. Then, the peak type B / T and the stroke information STRK obtained in this manner are used as other information ADR1, W, and SLP.
And the peak information memory 1 as the second peak information
The data is written to the storage area corresponding to the 25 peak addresses ADR3 = 1. Thereafter, the same operation is performed when the peak points P3, P4,... Are detected. Then, when the predetermined time has elapsed, the microcomputer 5 stops outputting the waveform collection instruction START, and the collection of the waveform value W and the peak information ends.

Next, the microcomputer 5 executes a waveform reading process and a calculation process of circulating dynamic parameters. First, the microcomputer 5 sequentially reads the inclination information SLP and the stroke information STRK corresponding to each peak point P1, P2,... From the peak information memory 125. Next, stroke information corresponding to the positive slope (that is, the corresponding slope information SLP has a positive value) is selected from the stroke information STRK,
From these pieces of stroke information, a higher-order predetermined number having a larger value is further selected. Then, one corresponding to the median value is selected from the selected stroke information STRK, and the rising portion of the pulse wave of one wavelength for which the waveform parameter is to be extracted, for example, the rising portion indicated by the symbol STRM in FIG. Stroke information is required. Then, the peak address one before the peak address corresponding to the stroke information, that is, the start point P of the pulse wave for one wavelength at which the waveform parameter should be extracted.
Six peak addresses are determined.

Next, the microcomputer 5 reads the waveform value of the pulse wave for one wavelength starting from the peak address of the starting point from the waveform memory 103, and performs the FFT processing to obtain the pulse wave spectrum (amplitude information and phase information). ) Is required. Then, one parameter of the four-element lumped parameter model, for example, the value of the inductance L is calculated based on this spectrum, and another parameter of the four-element lumped parameter model is calculated based on the value of L and the waveform of the pulse wave for one wavelength. The value of the parameter is calculated. And the microcomputer 5
Writes in the memory 1 the thus obtained circulating dynamic parameters together with information indicating the current date and time.

The operation related to the control of the discharge of the fragrance is performed in the modes 1 to 6 described above.
Are different between the case where any one of them is selected and the case where mode 7 is selected. The operation will be described below in each case.

A. When any one of modes 1 to 6 is selected When these modes are selected, the microcomputer 5 performs a process of determining a time to perform the fragrance discharge at a predetermined time in the midnight time zone. That is, the circulatory dynamic parameters stored in the memory 1 during the past fixed period (for a predetermined number of days) are read out, and the moving average of each of the time when the specific parameter (for example, the resistance R _P ) becomes maximum and the time when it becomes minimum is calculated. I do. Then, according to this calculation result,
A time zone for transition from the sedation state to the excitement state (periods A and C illustrated in FIG. 16) and a time zone for transition from the excitement state to the sedation state (periods B and D illustrated in FIG. 16) are obtained.

Then, at a predetermined time in the time zone obtained in this manner (for example, the time at the center of the time zone), a fragrance discharge command is set so as to discharge fragrance corresponding to each mode. For example, when the mode 5 is set, the following four types of fragrance discharge time limits are set. At a predetermined time in the time zone A, the second fragrance discharging unit 400
At a predetermined time within the time zone B, the first fragrance discharging section 300
At a predetermined time within the time zone C, the second flavor discharge section 400
At a predetermined time within the time zone D, the first fragrance discharging unit 300
Then, at the time set as described above in the daytime, the microcomputer 5 sends a drive command to the perfume discharger.

When a drive command is generated by the microcomputer 5, the first fragrance discharging section 300 receiving the drive command
Alternatively, the following operation is performed in the second fragrance discharging unit 400.
First, the drive circuit 363 receives a drive command from the microcomputer 5 to set a predetermined level (approximately 100
A drive pulse V) is generated and supplied to the piezoelectric element 326 of the micro pump 301. When this drive pulse is applied, the piezoelectric element 326 is deformed as shown in FIG. 8, and the diaphragm 309 is bent in a concave shape. As a result, the pressure in the pump chamber 322 increases, the partition wall of the output valve 308 is lifted, and the valve body 325 separates from the substrate 302. Then, the fragrance in the pump chamber 322 flows out to the output port 306 through the gap between the valve body 325 and the substrate 302, and the tube 306T and the injection hole 16 (or the injection hole 17).
Injected to the outside via Then, when the drive pulse falls, the pump chamber 322 is turned to return from the state where the diaphragm 309 is depressed inward as shown in FIG.
, A negative pressure is generated. Therefore, the valve element 3 of the outlet valve 308
The output port 306 is closed by pressing the substrate 25 against the substrate 302. Conversely, the partition of the input valve 307 is lifted upward, and accordingly, the valve element 316 is moved to the substrate 302.
Move away from As a result, the fragrance flows in from the input port 305, and the gap between the valve body 316 and the substrate 302 and the through hole 31
8 and is sucked into the pump chamber 322. Thereafter, every time the drive pulse is applied, the same discharge and inhalation of the fragrance as described above is repeated.

While the micro pump 301 is operating,
The voltage at both ends of the operation detection switch 350 is monitored by the abnormality detection circuit 365. If the fragrance is not discharged smoothly due to tube clogging or the like, the relationship between the drive pulse generation timing and the timing at which the operation detection switch 350 is turned on deviates from the normal one. The abnormality detection circuit 365 outputs an abnormality detection signal to the microcomputer 5 when detecting this deviation. The microcomputer 5 causes the output unit 3 to display an alarm by receiving the abnormality detection signal.

When the discharge of the fragrance is completed, the current discharge amount is calculated based on the number of times of the drive command, and this discharge amount is calculated as follows.
The type of fragrance discharged this time is written into the memory 1 as discharge recording information. Further, the accumulated value of the ejection amount so far is obtained for each fragrance, and the result is written in the memory 1. here,
When the accumulated value exceeds a predetermined value, the microcomputer 5
Sends a warning output command to the output unit 3. The output unit 3 prompts the user to replace the chemical solution tank by displaying an alarm such as lighting of a warning lamp. The warning may be output by producing a sound.

B. When Mode 7 is Selected Also in this mode, the microcomputer 5 reads out the circulatory state parameters stored in the memory 1 at a predetermined time in the midnight time zone, and switches from the sedated state to the excited state based on this. And time zone (period A, C)
And a time zone (period B, D) in which the state changes from the excitement state to the sedation state (see FIG. 16). Then, in this mode, in the time zone obtained in this way, the monitoring of the temporal change of the circulation dynamics and the discharge control of the fragrance based on the monitoring result are performed.

That is, during the daytime, the microcomputer 5 periodically measures the circulatory parameters during any one of the above periods A, B, C, and D, and the obtained circulatory parameters are obtained. It is determined whether it is increasing or decreasing based on the previously obtained circulatory parameters. Next, the microcomputer 5 determines whether or not the temporal change of the circulatory parameters is contrary to the normal temporal change of the circulatory parameters in the time zone. Then, when a change contrary to a normal temporal change of the circulatory dynamic parameter is recognized, a fragrance for suppressing such an abnormal change is discharged.

For example, the period A is a time period in which the resistance R _P among the circulatory dynamic parameters decreases and the user shifts from the sedated state to the excited state. In this period A, if the resistance R _P is if reduced, there is no problem because of the usual change. However, if the resistance R _P is assumed to increase, this would be contrary to the usual temporal change in the resistance R _P. Therefore, the microcomputer 5 includes the second fragrance discharging unit 400
Sending a drive command to ejected perfume sandalwood, increased resistance R _P, i.e., inhibits the transition to sedation. Also,
In the period B, the resistance R _P increases because of a normal temporal change. Therefore, when the resistance R _P decreases, a driving command is sent to the first fragrance discharging unit 300 to discharge the lavender fragrance and discharge the fragrance. _Stop the decrease in R _P.

As described above, according to the present embodiment, the control of the discharge of the fragrance is performed based on the temporal change of the circulation dynamics parameter, and the state of the user is temporally controlled according to the desired fluctuation rhythm by the discharge of the fragrance. Control is performed so as to change.

In the above embodiment, the fragrance discharge control is performed based on the circulating dynamic parameters. Instead, the amplitude of the pulse wave or the phase of the harmonic (phase difference with respect to the fundamental wave) is changed. Perfume discharge control may be performed based on this. In other words, according to experiments by the inventors, when stress is applied to a human, the phases of the second, third, and fourth harmonics of the pulse wave or the amplitude of the third harmonic change. Has been confirmed. For example, when examining the pulse wave of eight testers against the physical stress that occurs when one hand is immersed in water at 4 ° C., the second harmonic and the third harmonic have a 95% probability.
It was confirmed that the phase of each of the harmonic and the fourth harmonic or the amplitude of the third harmonic changed. Also, [1000-
9] against mental stress that repeats the calculation
Examination of the pulse wave of a human tester confirmed that the phase of the fourth harmonic also changed with a probability of 95%. Therefore, the pulse wave is subjected to spectrum analysis to obtain, for example, the fourth wave.
The phase of the harmonic may be detected, and the fragrance discharge control may be performed based on the value of the phase. Also, the phase of the pulse wave (for example, the fourth
It is known that the phase of the harmonic changes according to the excitement state. Therefore, the detection of the excited state may be performed based on the phase of the pulse wave.

§2. 2. Second Embodiment (1) Outline of Embodiment In contrast to the first embodiment in which the control of the discharge of the fragrance is performed based on the shape of the pulse wave, the drug discharge device according to the present embodiment. Controls the discharge of the fragrance based on the information of the "fluctuation" of the pulse wave. In the electrocardiogram, R of a certain heartbeat
The time interval between the wave and the R-wave of the next heartbeat is called the RR interval. The RR interval is a numerical value serving as an index of the autonomic nervous function in the human body. FIG. 22 illustrates heartbeats in an electrocardiogram and RR intervals obtained from these heartbeats. When a body surface electrocardiogram of a subject is actually measured, it is known that the RR interval varies with time as shown in the figure.

On the other hand, the fluctuation of the blood pressure measured in the radial artery and the like is defined as the fluctuation of the systolic blood pressure and the diastolic blood pressure for each beat, and corresponds to the fluctuation of the RR interval in the electrocardiogram. FIG. 23 shows the relationship between the electrocardiogram and the blood pressure. As can be seen from the figure, the systolic and diastolic blood pressures for each beat are measured as the maximum value of the arterial pressure in each RR interval and the minimum value seen immediately before the maximum value. When the results of the spectrum analysis of the heart rate variability or the blood pressure variability are graphed, it can be seen that they are composed of waves of a plurality of frequencies. These waves are classified into the following three types of fluctuation components. -HF (High Frequency) component, which is a fluctuation that matches respiration-LF (Low Frequency), which fluctuates in a cycle of about 10 seconds
Component ・ Trend that fluctuates at a frequency lower than the measurement limit (Tren
d)

The RR interval is obtained between the pulse waves adjacent to the measured pulse wave, and the obtained RR interval discrete values are interpolated. Then, in the same manner as in the first embodiment, by subjecting the interpolated curve to FFT processing and spectrum analysis, the above-mentioned fluctuation component can be extracted as a peak on the frequency axis. FIG. 24A shows an example of the fluctuation of the RR interval of the measured pulse wave and each fluctuation component when the RR interval fluctuation is decomposed into the above three components. FIG. 24B shows a result of spectrum analysis performed by performing FFT processing on the RR interval fluctuation waveform shown in FIG. 24A, and the horizontal axis represents the amplitude of each frequency component.
The vertical axis represents the frequency. As can be seen from this figure, peaks are observed at two frequencies around 0.07 Hz and around 0.25 Hz, the former being the LF component and the latter being the HF component.

The LF component represents the degree of the sympathetic tone, and the greater the value of this component, the greater the tone. On the other hand, the HF component represents the degree of parasympathetic tone, and the larger the value of this component, the more relaxed. In the present embodiment, the HF component and LF
Considering that there are individual differences in the absolute value of the component amplitude,
The degree of tension of the subject is estimated based on “LF / HF” which is the ratio of the amplitudes of the HF component and the LF component, and is used for adjusting the rhythm variation of the subject. The LF component described above and H
Due to the nature of the F component, the greater 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 (ie, relaxed). Therefore, the internal state of the subject can be grasped from the value of “LF / HF”, and the state of the subject is adjusted by performing the fragrance discharge control based on this.

(2) Configuration of the Embodiment The configuration of the present embodiment is the same as that of the first embodiment, and a description thereof will be omitted. (3) Operation of Embodiment The operation of this embodiment will be described below. Periodic Measurement of Pulse Wave and Spectrum Analysis As described above, the timer interrupt is periodically (for example, every two hours) generated in the microcomputer 5. At this moment, the microcomputer 5 executes the following processing as a timer interrupt routine.

In the same manner as in the first embodiment, the waveform of the radial artery and the peak information of the waveform are collected. Thereby, the radial artery waveform output from the pulse wave detection unit 200 in FIG. 1 is converted into the A / D converter 101 and the LPF 10 in FIG.
2 is written to the waveform memory 103. In the present embodiment, this capturing process is performed for one measurement, for example, for 30 seconds. In parallel with this waveform sampling process, a differentiating circuit 121, a zero-cross detecting circuit 122, a peak address counter 123, a moving average calculating circuit 124
Operates, waveform value address ADR1, waveform value W, peak address ADR3, peak type B / T, stroke S
The TRK and the slope information SLP are written into the peak information memory 125.

When one measurement is completed, the microcomputer 5 detects the peak of each pulse wave. The microcomputer 5 selects stroke information having a positive slope based on the information stored in the peak information memory 125. When the absolute value of the difference between the maximum and the minimum for these strokes (for example, the peak point P7 and the peak point P6 in the stroke STRKM in FIG. 4) is equal to or greater than a predetermined value, the maximum point (P7 in FIG. 4) is determined. The time of the peak is calculated at the same time as the peak of the beat.
This peak detection process is performed on all the pulse waves obtained within the above measurement period.

Next, the intervals between the peaks (corresponding to the RR intervals on the electrocardiogram) are sequentially calculated based on the times of two consecutive peaks. Here, since the obtained value of the peak interval is discrete on the time axis, the interval between adjacent peak intervals is interpolated by an appropriate interpolation method (for example, linear interpolation). As a result, a graph similar to the curve of the RR interval as shown in FIG. Therefore, an FFT process is performed on the interpolated curve to obtain a spectrum as shown in FIG. Next, the maximum
The local maximum value in this spectrum and the frequency corresponding to the local maximum value are obtained by the same method as that for determining the local minimum.
The maximum value obtained in the low frequency region is defined as the LF component, and the maximum value obtained in the high frequency region is defined as the HF component. Then, “LF / HF” is calculated by obtaining the amplitude of each component, and “LF / H” is calculated together with the time when the pulse wave was measured.
F ”is stored in the memory 1. The above-described periodic measurement and spectrum analysis of the pulse wave are repeated every two hours every day.

As in the first embodiment, the operation relating to the control of the discharge of the fragrance is performed when one of the modes 1 to 6 is selected.
This is different from the case where mode 7 is selected. The operation of each case will be briefly described below. a. When Any of Modes 1 to 6 is Selected The microcomputer 5 determines the timing of spice discharge at a predetermined time in the midnight time zone. That is, the value of “LF / HF” for a predetermined number of days (for example, the past week) is read from the memory 1, and the average of “LF / HF” at each time is obtained. Next, the time when the average value of “LF / HF” becomes maximum / minimum is calculated.

Next, according to the calculation result, a time period for shifting from the sedated state to the excited state and a time period for shifting from the excited state to the sedated 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 center time) in the obtained time zone. Thereafter, when the time set above is reached, the microcomputer 5 sets the corresponding fragrance discharging unit 300 or 40
0 is driven to discharge the fragrance. When the discharge of the fragrance is completed, the discharge amount of the fragrance is calculated in the same manner as in the first embodiment, and the type of the fragrance is stored in the memory 1 as discharge recording information.
To store. Further, a cumulative value of the discharge amount for each flavor is obtained and stored in the memory 1.

B. When mode 7 is selected a. In the same manner as described above, the microcomputer 5 sets “LF / H” in the memory 1 at a predetermined time in the midnight time zone.
Average value for one week is calculated based on "F". Next, a time at which the average value of the “LF / HF” becomes maximum or minimum is obtained. Then, based on the obtained times, a time period for shifting from the sedated state to the excited state and a time period for shifting from the excited state to the sedated state are determined. Next, during the day of the next day, a temporal change of “LF / HF” in the obtained time zone is monitored, and the discharge of the fragrance is controlled based on the monitoring result.

That is, the microcomputer 5 comprises:
When performing the periodic measurement of the value of “LF / HF”, it is determined whether the current value of “LF / HF” is increasing or decreasing compared to the previous value. Next, it is checked whether or not this temporal change is contrary to a normal temporal change in a time zone to which the time of the periodic measurement belongs. If contrary to this, it is determined that the fragrance is discharged so as to suppress the abnormal temporal change. For example, if “LF / HF” decreases during the time when the subject's internal state should transition from the sedated state to the excited state, this is contrary to a normal time change. Therefore, the microcomputer 5 drives the second fragrance discharging unit 400 to discharge sandalwood fragrance, and shifts the subject to an excited state. Further, if “LF / HF” is increased during a time period when the internal state of the subject is to transition from the excitable state to the sedated state, the first fragrance discharging unit 300 is driven to discharge the lavender fragrance, and the subject is discharged. To sedation.

§3. 3. Third Embodiment (1) Overview of the Embodiment The drug ejection device according to the present embodiment is similar to the second embodiment in that a fragrance is ejected based on information on “fluctuation” of a pulse wave. . However, this embodiment is different in that RR50 is used as a measured value for control. Here, RR50 is a predetermined time (for example, 3
RR of two consecutive heartbeats in the measurement of pulse wave
The number of times that the absolute value of the interval fluctuates by 50 milliseconds or more. R
It is conventionally known that the larger the value of R50, the more sedated the subject is, while the smaller the value of RR50 is, the more excited the subject is. In this embodiment, the fragrance discharge is controlled using this property. (2) Configuration of the Embodiment The configuration of the present embodiment is the same as that of the first or second embodiment, and a description thereof will be omitted.

(3) Operation of Embodiment The operation of this embodiment will be described below. Periodic Measurement of Pulse Wave As described above, the timer interrupt is periodically (for example, every two hours) generated in the microcomputer 5. At this moment, the microcomputer 5 executes the following processing as a timer interrupt routine. As in the second embodiment, the waveform of the radial artery and the peak information of the waveform are collected, and various information is written to the waveform memory 103 and the peak information memory 125.

When one measurement is completed, the microcomputer 5 detects the peak of each pulse wave for all the pulse waves obtained during the measurement period. Next, the peak interval is sequentially calculated for all the pulse waves from the time of two consecutive peaks. Thereafter, the time difference between adjacent peak intervals is obtained in order, and the number of time differences of 50 ms or more is counted, and this number is defined as RR50 at the measurement point. Then, this value is stored in the memory 1 together with the time at the time of the measurement. The above-described periodic measurement of the pulse wave is repeated every two hours every day.

Perfume Discharge Control The operation of the perfume discharge control in this embodiment is described as “LF / H
F "instead of RR50
The operation is the same as that of the embodiment. As described above, “LF
The value of / HF is higher when the value is larger, and the lower the value, the more sedated. On the other hand, RR50 is in a sedated state as its value is large, and is in an excited state as its value is small. Therefore, the selection criterion of the discharged fragrance in the discharge control of the fragrance is opposite to that of the second embodiment.

In the third embodiment, RR5
A heart rate may be used instead of zero. As is well known, there is a negative correlation between RR50 and heart rate. Therefore, by performing the discharge control of the fragrance with the selection of the fragrance being opposite to that of the third embodiment (or the same as in the second embodiment), the same effect as that of the above-described embodiment can be obtained.

§4. Fourth Embodiment In this embodiment, a drug ejection device is provided as an accessory (accessory).
The case where this is combined will be described. Here, the necklace shown in FIG. 25 is taken as an example of the accessory, but there is no problem with other accessories. In this figure, reference numeral 31 denotes a sensor pad, which is made of, for example, a sponge-like cushioning material. In the sensor pad 31, a photoelectric pulse wave sensor 32 corresponding to the pulse wave detector 200 in FIG. 1 is attached so as to come into contact with the skin surface. Thus, when the necklace is put on the neck, the photoelectric pulse wave sensor 32 comes into contact with the skin on the back side of the neck to measure the pulse wave.

The main unit 33 incorporates the components shown in FIG. 1 (the control unit 100, the power supply control unit 501, etc.) except for the pulse wave detection unit 200. The main body 33 has a broach-like shape, and the front surface thereof has the same injection holes 1 as shown in FIG.
6 and injection holes 17 are provided. The injection hole 16
Alternatively, the injection hole 17 may be attached to the back side of the main body 33 so as to discharge to the skin. The photoelectric pulse wave sensor 32 and the main body 33 are respectively attached to a chain 34, and a lead wire embedded in the chain 34 (not shown).
Are electrically connected via

Next, the configuration of the photoelectric pulse wave sensor 32 is shown in FIG. In this figure, 35 is a wavelength of 940n.
m is a light emitting element composed of an infrared light emitting diode or the like; The light emitted from the infrared light emitting diode 35 is reflected by a blood vessel passing directly under the skin where the photoelectric pulse wave sensor 32 contacts. The reflected light is received by the optical sensor 36, and a pulse wave detection signal M is obtained as a result of the photoelectric conversion. This pulse wave detection signal M is sent to the waveform extraction storage unit 4 in FIG. In the present embodiment, the only difference is that the pulse wave is captured by the photoelectric pulse wave sensor 32 instead of the pressure sensor 13 of FIG. 2 and the pulse wave of the neck portion is measured instead of the radial artery pulse wave. . Therefore, the operation of the drug ejection device according to the present embodiment is the same as that of the above-described first to third embodiments, and the description thereof is omitted here.

§5. Fifth Embodiment In this embodiment, a case will be described in which the drug ejection device is combined with eyeglasses. FIG. 27 is an enlarged view of the vine portion of the glasses. According to the example of this figure, the drug ejection device is attached to a vine 41 of a frame of glasses. The components (the control unit 100, the power supply control unit 501, and the like) of FIG. 1 except for the pulse wave detection unit 200 are incorporated in the main body 42 of the drug ejection device. The main body 42 has the same injection holes 16 as those in FIG.
And an injection hole 17 are provided. In FIG. 27, the injection holes are provided on the upper surface of the main body 42. However, the injection holes may be attached to the side surface so that the medicine can be discharged to the skin.

The configuration of the pulse wave detector 200 shown in FIG. 1 is the same as that of the fourth embodiment, and is shown in FIG.
Here, the infrared light emitting diode 35 and the optical sensor 36
Are embedded in pads 45 and 46 shown in FIG. 27, respectively, and are fixed to the ear by sandwiching an earlobe between the pads 45 and 46. The pads 45 and the pads 46 are electrically connected by lead wires 47, 47 drawn from the main body 42 as shown in FIG. In the present embodiment, the only difference is that the pulse wave is captured by the photoelectric pulse wave sensor 32 instead of the pressure sensor 13 in FIG. 2 and the pulse wave of the earlobe is measured instead of the pulse wave of the radial artery. Therefore, the operation of the drug ejection device according to this embodiment is the same as that of the above-described first to fourth embodiments, and a description thereof will be omitted.

[0098] In the above embodiment, the fragrance discharging section is set to two.
Although a single device is used, a single device may be used to configure a drug ejection device that ejects only one type of fragrance. Further, in the mode 7 of the above-described embodiment, in a specific time zone, the fragrance is discharged when the circulatory dynamics parameter changes in the past against the change (upward trend / downward trend) in the time zone in the past. However, this mode may be modified. That is, in place of or in addition to mode 7, the value of the circulatory dynamics parameter in a specific time zone in the past several days is out of the range of the variation of the value of the circulatory dynamic parameter (for example, the range of average value ± 3σ). When the circulatory dynamics parameter is measured, a mode may be provided for discharging a fragrance having an effect of returning the variation to within the range of the variation.

In the above embodiment, lavender and sandalwood are used as fragrances. However, there are some individual differences in what kind of fragrance is appropriate, and depending on the user, a sedative action or an excitatory action may occur. Suitable perfumes may differ from these. Therefore, when using the apparatus according to these embodiments, after confirming which fragrance is appropriate to use, the appropriate fragrance is supplied to the first fragrance discharging unit 3.
It is preferable to use it by setting it to 00 or the second fragrance discharging section 400. In the above embodiment, two manual switches are added, and when the first switch is operated, the lavender is operated, and when the second switch is operated, the sandalwood is discharged. Is also good. In the first to third embodiments, the watch body 10 shown in FIG.
May be displayed on the display surface of the current state of excitement / sedation, that is, the current value of the parameter Rp or the like.

In the above embodiment, the subject is equipped with an acceleration sensor or the like to quantitatively grasp the operation state of the subject, and the measured values (circulation dynamic parameters, “L
F / HF ”, RR50, etc.). That is, when the subject is moving, “LF / H
Since the value of “F” becomes larger than usual, it is conceivable to correct this to a value similar to that of normal. Further, in the above-described embodiment, the state of the living body is represented by LF, HF, “LF / HF”, RR50 obtained from the pulse wave waveform.
It was decided to use it for analysis of health condition. However, the state of the living body is not limited to this, and various quantities such as LF obtained from the waveform of the electrocardiogram, heart rate, body temperature,
The pulse rate may be used. Further, in the above-described embodiment, lavender and sandalwood fragrances have been described as examples of drugs. However, any other fragrance or drug other than the fragrance may be used as long as it has the above-mentioned correlation with the state of the living body.

[0101]

As described above, according to the present invention, the state of a user as a living body is periodically measured, and the ejection control of the drug is automatically performed based on a temporal change of the state. So without bothering the user,
The effect is obtained that the internal state of the user such as the excited state and the sedated state can be controlled.

[Brief description of the drawings]

FIG. 1 is a block diagram showing a functional configuration of a drug ejection device according to an embodiment of the present invention.

FIG. 2 is a diagram showing a mechanical configuration of the embodiment.

FIG. 3 is a block diagram showing a configuration of a waveform extraction storage unit 4 in the embodiment.

FIG. 4 is a diagram illustrating an example of a waveform of a Yue bone artery.

FIG. 5 is a diagram showing storage contents of a peak information memory 125 in the embodiment.

FIG. 6 shows a fragrance discharging section 300 (40) in the embodiment.
FIG. 2 is a block diagram showing the configuration of FIG.

FIG. 7 is a cross-sectional view illustrating a configuration of a micropump 301 according to the same embodiment.

FIG. 8 is a diagram illustrating the operation of the micro pump 301.

FIG. 9 is a diagram for explaining the operation of the micro pump 301.

FIG. 10 is a diagram illustrating a control mode of the fragrance discharge according to the embodiment.

FIG. 11 is a diagram illustrating a control mode of the fragrance discharge according to the embodiment.

FIG. 12 is a diagram illustrating a control mode of the fragrance discharge according to the embodiment.

FIG. 13 is a diagram illustrating a control mode of the fragrance discharge according to the embodiment.

FIG. 14 is a diagram illustrating a control mode of the fragrance discharge according to the embodiment.

FIG. 15 is a diagram illustrating a control mode of the fragrance discharge according to the embodiment.

FIG. 16 is a diagram illustrating a control mode of the fragrance discharge according to the embodiment.

FIG. 17 is a circuit diagram of a four-element lumped parameter model.

FIG. 18 is a diagram illustrating an arterial waveform at an aortic root.

FIG. 19 is a diagram showing a model of an arterial waveform at an aortic root.

FIG. 20 is a diagram showing the effect of fragrance discharge.

FIG. 21 is a diagram showing circadian variation of circulatory dynamic parameters.

FIG. 22 is a diagram showing a relationship between an electrocardiogram and an RR interval.

FIG. 23 is a diagram showing a relationship between an electrocardiogram and a pulse wave.

FIG. 24A is a diagram showing a relationship between RR interval fluctuation and frequency components constituting the fluctuation. (B) is RR
FIG. 9 is a diagram showing a result of performing a spectrum analysis of an interval variation.

FIG. 25 is a diagram showing a configuration of a drug ejection device according to a fourth embodiment of the present invention.

FIG. 26 is a circuit diagram of a photoelectric pulse wave sensor 32 according to fourth to fifth embodiments of the present invention.

FIG. 27 is a view illustrating a configuration of a drug ejection device according to a fifth embodiment of the present invention.

[Explanation of symbols]

200 pulse wave detection unit, 100 control unit, 300
First fragrance discharging section, 400... Second fragrance discharging section.

──────────────────────────────────────────────────続 き Continuation of front page (56) References JP-A-4-300562 (JP, A) JP-A-6-3920 (JP, A) JP-A-1-94825 (JP, A) JP-A-4-300 108424 (JP, A) JP-A-61-187835 (JP, A) (58) Fields investigated (Int. Cl. ⁷ , DB name) A61M 11/00 A61B 5/02-5/0295

Claims (21)

(57) [Claims] 1. A measuring means for measuring a state of a living body, a storage means for storing the state of the living body measured up to the present time, and a time at which a drug is to be ejected based on a past change rhythm of the state of the living body And a discharge unit that discharges a drug according to the drug discharge command at that time. A drug discharge device comprising: 2. The drug ejection device according to claim 1, wherein the control unit selects a time zone in which the state of the living body changes with a predetermined tendency, and outputs the drug ejection command in the time zone. . 3. A measuring means for measuring a state of a living body, a storage means for storing the state of the living body measured up to the present time, and a change rhythm of the state of the living body in the past and a state of the living body at the present time. A drug ejection device, comprising: a control unit that outputs a drug ejection command through a pump; and an ejection unit that ejects a drug in accordance with the drug ejection command. 4. The control means selects a time period during which the state of the living body changes with a predetermined tendency, and when the state of the living body changes with a different tendency from the past during the time period, the control means selects the drug. The drug ejection device according to claim 3, wherein the device outputs an ejection command. 5. The method according to claim 1, wherein the control unit selects a predetermined time period, and when the state of the living body in the time period is apart from the moving average of the state of the living body in the predetermined time period by a predetermined amount or more within a past predetermined period. The drug ejection device according to claim 3, wherein the drug ejection command is output to the device. 6. The state of the living body is represented by an element of an electric circuit model that simulates a system from a central part to a peripheral part of an arterial system of a human body, and the measuring unit converts a pulse wave from the living body. The drug ejection device according to any one of claims 1 to 4, wherein the value is measured and a value of an element of the electric circuit model is determined based on the pulse wave. 7. The measurement means measures the amplitude of a fundamental wave and the amplitude and phase of a harmonic wave of a pulse wave from the living body, and determines the value of an element of the electric circuit model based on the measurement result. The drug ejection device according to claim 6, characterized in that: 8. The measuring means measures the amplitude of a fundamental wave and the amplitude and phase of a harmonic wave of the pulse wave from the living body, calculates a distortion rate of the pulse wave from the measurement result, and calculates the distortion rate and the distortion rate. The drug ejection device according to claim 7, wherein a value of an element of the electric circuit model is determined from a regression equation between a distortion factor and a value of an element of the electric circuit model. 9. The electric circuit model includes a first resistance corresponding to a blood vessel resistance due to blood viscosity in the central part of the arterial system,
An inductance corresponding to the inertia of blood at the central part of the arterial system, a capacitance corresponding to viscoelasticity of blood vessels at the central part of the artery, and a second resistance corresponding to vascular resistance at the peripheral part. A four-element lumped-constant model in which a series circuit composed of the first resistor and the inductance and a parallel circuit composed of the capacitance and the second resistor are sequentially inserted in series between a pair of input terminals; The drug ejection device according to any one of claims 6 to 8, wherein: 10. The state of the living body is represented by a phase or an amplitude of a harmonic component of a pulse wave of an artery of a human body, and the measuring unit measures a pulse wave from the living body, and The drug ejection device according to any one of claims 1 to 4, wherein an amplitude or a phase of a harmonic component of the pulse wave is measured. 11. The state of the living body is based on a ratio of amplitudes of two spectral components of a low-frequency component and a high-frequency component obtained from a time interval variation of a pulse wave of an artery of a human body, and the measuring unit includes: 2. The method according to claim 1, wherein a pulse wave is measured from a living body, a time interval between the adjacent pulse waves is calculated, and a low-frequency spectral component and a high-frequency spectral component are obtained from a spectrum analysis of the fluctuation of the time interval. ~
6. The drug ejection device according to any one of items 5 to 5. 12. The state of the living body is based on the number of fluctuations of the time interval fluctuation of the pulse wave of the artery of the human body, and the measuring means measures the pulse wave from the living body, and measures the time of the adjacent pulse wave. The drug ejection device according to any one of claims 1 to 5, wherein an interval is calculated, and a number in which the amount of change of the continuous time interval exceeds a predetermined time is output as the number of changes. 13. The apparatus according to claim 1, further comprising: means for determining a discharge amount of the drug, and notifying that the integrated value of the discharge amount is equal to a predetermined amount.
The drug ejection device according to claim 1. 14. The apparatus according to claim 1, further comprising means for monitoring whether or not the ejection of the drug is performed normally, and notifying the abnormality when there is an abnormality. The drug ejection device according to claim. 15. A drug ejection device that is carried and used and operates based on a voltage supplied from a battery,
The drug according to any one of claims 1 to 14, further comprising a power supply control unit that intermittently supplies the output voltage of the battery to the measurement unit, the control unit, and the discharge unit. Discharge device. 16. The drug ejection device according to claim 15, further comprising means for notifying when the output voltage of said battery has become equal to or lower than a predetermined voltage. 17. The apparatus according to claim 1, further comprising a sensor attached to a human body, wherein the sensor measures a movement of the living body, and compensates for the state of the living body based on the measurement result.
Item 18. The drug ejection device according to any one of Items 16. 18. The apparatus according to claim 6, wherein the measuring means detects the pulse wave by measuring a pulse pressure.
18. The drug ejection device according to any one of items 17 to 17. 19. The pulse wave measuring device according to claim 6, wherein the measuring unit irradiates a blood vessel under the skin with light and receives the light reflected by the blood vessel to measure the pulse wave. 18. The drug ejection device according to any one of items 17 to 18. 20. A case incorporating the storage means and the control means, wherein the discharge means has a case provided on a surface thereof, wherein the case is attached to a chain of a necklace, and wherein the measuring means is such that the case is formed of the necklace. A light-emitting element attached to the chain of the skin, irradiating light to blood vessels under the skin, and a photoelectric pulse wave sensor comprising a light sensor for receiving the light reflected by the blood vessels under the skin, The pulse wave is measured.
Item 18. The drug ejection device according to any one of items 17. 21. A case incorporating the storage means and the control means, wherein the discharge means has a case provided on a surface thereof, the case is attached to a vine of a frame of spectacles, and the measuring means is provided under the skin. The pulse wave is measured by a photoelectric pulse wave sensor including a light emitting element that irradiates light to a blood vessel and an optical sensor that receives light reflected by the blood vessel under the skin. The drug ejection device according to any one of claims 6 to 17, wherein