JP2002000576A - Organism information measuring sensor - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an organism information measuring sensor capable of measuring organism information reliably even during massaging, though not contactless. SOLUTION: A massage machine 100 is provided with a headphone 1 having a pulse wave sensor and a heart rate measuring electrode and having an ear lobe sensor attached on one ear lobe and a respiration sensor, and a finger- attached probe 2 having a pulse wave sensor and a heart rate measuring electrode and attached on a finger.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a biological information measuring sensor for measuring biological information such as heart rate, and more particularly to a biological information measuring sensor suitable for use in a massage machine.

[0002]

2. Description of the Related Art As a biological information measuring sensor in a conventional massage machine, as disclosed in Japanese Patent Application Laid-Open No. 8-584, a light emitting portion is bent from an optical fiber attached below a seating surface of the massage machine to a light receiving portion. Some devices detect minute movements related to the heartbeat by measuring a change in the amount of light that reaches the target. Further, as disclosed in Japanese Patent Application Laid-Open No. H8-117300, there is a type in which a respiratory cycle is detected based on pressure information applied to a treatment element during a massage operation. All of these can measure the biological information without contacting the user, so that the biological information can be obtained without giving the user a sense of restraint.

[0003]

However, in the above-described biological information measurement sensor, when a massage stimulus is strong or when a part close to the seat such as the back or the waist is massaged, noise due to the massage operation is large. There is a possibility that the measurement of the biological information may be difficult, and the body movement of the user due to an utterance during the measurement may affect the measurement of the biological information.

The present invention has been made in order to solve the problems of the prior art, and it is an object of the present invention to provide a method for measuring biological information which is not non-contact, but which can reliably measure biological information even during massage treatment. It is to provide a measurement sensor.

[0005]

In order to achieve the above object, the present invention comprises a heart rate measuring electrode provided so as to be able to contact one of the left and right earlobes and a finger opposite to the earlobe. Biological information measurement sensor.

Also, a heart rate measuring electrode provided in contact with the earlobe, a head mounted probe having a mounting member for mounting on the head, and a heart rate measuring electrode provided in contact with fingers. And a finger mounting probe having a finger mounting member for mounting on a finger.

[0007] The head mounted probe may be provided with a pulse wave sensor for detecting a pulse wave.

Further, a pulse wave sensor for detecting a pulse wave may be provided on the finger-mounted probe.

[0009] The head-mounted probe may be provided with a thermistor and a holding member for holding the thermistor near the nasal cavity.

Preferably, the holding member is a deformable member for adjusting the position of the thermistor.

Further, the head-mounted probe may be provided with an earpiece which abuts on or covers the ear, and a speaker provided on the earpiece and opposed to the ear.

Further, the finger mounting member may be a belt-like member wound around a finger.

The finger mounting member may be a sack-shaped member into which a finger is inserted.

[0014]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS FIG. 1 shows the overall schematic configuration of a massage machine provided with a biological information measuring sensor according to an embodiment of the present invention.

The user sits on the seat 101 of the chair-type massage machine 100, leans the back and head on the backrest 102 and the head pad 103, and places the forearm on the armrest 1
04. An earlobe sensor having a pulse wave sensor and a heart rate measurement electrode, and an earlobe sensor mounted on a left earlobe, and a headphone 1 integrally formed with a head mounted probe having a respiration sensor are mounted on the head. A finger mounting probe 2 having a pulse wave sensor and a heart rate measuring electrode is mounted on the index finger. A cable containing a lead wire is drawn out from each sensor, and connected to the biological amplifier 3 provided on the side of the seat 101.

First, an earlobe sensor will be described with reference to FIG.

As shown in FIG. 2A, the earlobe sensor 4 is a pulse wave sensor 8 supported by two substantially elliptical support members 6, 7 which are openably and closably connected via a hinge 5. And a heart rate measuring electrode 9. The pulse wave sensor is configured to irradiate a light beam from an opening provided in one of the support members 6.
a and a light receiving unit 8 for receiving light rays from the irradiating unit 8a transmitted through the earlobe through an opening provided in the other support member 7
b. The heart rate measuring electrode 9 is formed of an annular copper plate surrounding the periphery of the opening of the light receiving section 8b. The heart rate measuring electrode 9 can also be formed from other conductive materials such as stainless steel and silver. The lead wires connected to the pulse wave sensor 8 and the heartbeat measurement electrode 9 are accommodated in a cable 10 that passes through the inside of the support members 6 and 7 and is drawn out from the hinge-side end of the support member 7. At this time, the lead wire 9a of the heart rate measuring electrode 9 may pass through the inside of the support members 6 and 7, but the lead wire 9a coming out of the heart rate measuring electrode may cause insufficient pinching of the earlobe, In order to prevent disturbance light from entering through the gap, a groove 7a into which the lead wire 9a fits may be provided in the support member 7, and the lead wire 9a may be drawn out from the groove 7a. The support members 6 and 7 are urged in a direction to close each other, and are attached so that the earlobe is sandwiched between the support members 6 and 7 as shown in FIG.

The earlobe sensor 4 includes an earpiece 12 provided at both ends of a band 11 attached to the crown (only one earpiece is shown in FIG. The headphone 1 is mounted on the earlobe so that it is exposed to a recess for accommodating the ear formed inside the earpiece. be able to. A speaker is provided in the recess of the earpiece 12 so as to face the ear. The lead wire connected to the living body amplifier 3 is housed in a cable 14 drawn from the earpiece 12. In this way, the earlobe sensor 12 can also shield the earlobe sensor 4 from light. Also, as shown in FIG.
If the earlobe is small and the earlobe is exposed, the earlobe sensor 4 suspended from the band 11 or the earpiece 12 with the cable 10
May be directly attached to the earlobe. Here, the mounting member is the band 11, or the band 11 and the earpiece 1.
2 and 13.

Next, the respiration sensor will be described with reference to FIG.

The respiration sensor 15 is supported by a tip of a support member 16 extending from the earpiece 12 to the front of the face.
A thin, substantially rectangular parallelepiped mounting member 17 is bonded to the tip of the support member 16. The mounting member 17 has a hole 17a for receiving the lead wire of the thermistor 18 therein. The hole 17a is open at the center of the mounting member 17 on the face side and at the end on the support member 16 side. The tip of the thermistor 18 is exposed from the opening at the center on the face side, Is the lead wire 1 connected to the thermistor 18
9 is coated and pulled out. Since the support member 16 has a bellows structure and can be freely bent, it is adjusted by the support member 16 so as to be located near the user's nasal cavity. Further, by providing the attachment member 17, damage to the thermistor 18 can be prevented, the influence of disturbance such as airflow from the side opposite to the breathing air can be removed, and the thermistor 18 can be securely fixed to the support member 16. . The lead wire 19 pulled out from the mounting member 17 is guided to the earpiece 12 along the support member 16, and together with the lead wires of other sensors is housed in the cable 14 and pulled out from the earpiece 12. When the headphone is equipped with a microphone, the above-described attachment member may be attached to the microphone.

A strain gauge may be wound around the thorax or abdomen as a respiration sensor, and a respiration curve to be described later may be obtained from a change in resistance according to the movement. It is not preferable because the treatment may cause an effect of the treatment element moving on the back. In this regard, it is preferable to use the above-described respiratory sensor because there is almost no sense of discomfort when considering that the user during the massage usually closes his or her eyes.

Next, referring to FIG. 6, the finger-mounted probe will be described.

As shown in FIG. 6 (a), the finger mounting probe 2 is a belt (finger mounting member) 2 wound around a finger.
Pulse wave sensor 21 and heart rate measurement electrode 22 held at 0
Consists of The pulse wave sensor 21 includes an irradiation unit 21 a and a light receiving unit 21 provided on a support member 23 held by the belt 20.
b. The heartbeat measuring electrode 22 is formed of a disk-shaped copper plate provided at a position different from the support member 23 of the pulse wave sensor 21. Irradiation unit 21a and light receiving unit 2 of pulse wave sensor 21
1b and the heartbeat measuring electrode 22 are exposed on the inner surface of the belt 20, and are wound so as to be in contact with the fingers as shown in FIG. The belt 20 is fixed by fixing means such as a hook-and-loop fastener. The lead wires 24 and 25 connected to the pulse wave sensor 21 and the heart rate measurement electrode 22 are:
The belt 20 is covered and pulled out from the lateral end of the belt 20. The pulse wave sensor and the heart rate measuring electrode may be provided not only on the belt-shaped finger mounting member as described above but also on a finger-suck-shaped finger mounting member.

A description will be given of the heart rate measurement by the heart rate sensor having the heart rate measuring electrodes 9 and 22.

The heart rate measurement is usually performed by detecting a characteristic waveform (R wave) appearing on the electrocardiogram. Electrocardiograms are clinically measured with electrodes attached to the limbs and chest, but if the purpose is to detect R waves instead of analyzing the ECG waveform itself, the mounting position of the electrodes for detection is so strict. No need.
The waveform shown by the broken line in FIG. 7A indicates the potential difference detected when the measurement electrodes are attached to the fingers of both hands and measurement is performed. The waveform shown by the solid line is a result of simultaneous recording of an electrocardiogram (ECG) induced by the chest three-electrode method (CM ₅ ). Comparing the two, it can be seen that a characteristic potential corresponding to the R-wave is also recorded by the measurement electrodes attached to the fingers of both hands. However, if it is assumed to be used in a massage machine, the body will not move spontaneously during the treatment, but it may be necessary to operate the remote control etc. It is not preferable to mount electrodes. Therefore, in such a case, it is preferable to attach one measuring electrode to a finger and the other measuring electrode to a different part. The waveform shown by the broken line in FIG. 7B indicates the potential difference detected when the measurement is performed by attaching the measurement electrodes to the left finger and the right earlobe. The waveform shown by the solid line is the result of simultaneously recording an electrocardiogram (ECG) induced by the chest three-electrode method (CM5) as in FIG. 7A. FIG.
As can be seen by comparing FIG. 7A and FIG. 7B, the R of the electrocardiogram can be calculated from the potential difference between the fingers and the fingers and between the fingers and the earlobe.
A waveform corresponding to a wave can be recorded. For this reason, in the present embodiment, one heartbeat measurement electrode is attached to a finger, and the other heartbeat measurement electrode is attached to an earlobe.

Since the pulse wave can be easily measured by the photoelectric volume pulse wave method, the pulse wave is usually recorded by attaching a photoelectric sensor to an earlobe or a finger. Thus, as described above, by incorporating the heartbeat measuring electrode 9 around the earlobe pulse wave sensor 8 and attaching the heartbeat measuring electrode 22 to the finger, heartbeat and pulse wave information can be obtained simultaneously. Also, heart rate and pulse wave information can be obtained simultaneously by incorporating a heart rate measurement electrode around the finger pulse wave sensor and attaching a heart rate measurement electrode to the opposite finger.

There are a transmission type and a reflection type as a pulse wave sensor using such a photoelectric sensor. In the case of the reflection type, there is no particular problem. However, in the case of the transmission type sensor, it is necessary to attach a heart rate measurement electrode so as not to block the photocell of the light receiving unit. As shown in FIG. It can be attached at a position surrounding the periphery of the portion 8b.

In the case of a finger-mounted probe, a belt-type probe is wound so that the heart rate measuring electrode 22 is located on the ventral side of the finger. Although the lead wires 24 and 25 are attached to the belt 20, if the arm is moved in such a length that the arm can be moved, the feeling of restraint that the hand is fixed even during massage treatment is eliminated. Lead wires 24 and 25
Of course, it may be housed in the cable of the book.

As described above, if the pulse wave sensors 8, 21 and the heart rate measuring electrodes 9, 22 are incorporated in both the earlobe sensor 4 and the finger-worn probe 2, the heart rate R wave and two types of pulse waves can be measured. can do.

Further, since the respiration sensor 15 is constituted by the thermistor 18 as described above, it can detect a change in temperature. Since expiration and inspiration have different temperatures, the respiration curve shown in FIG. 8 can be obtained from the temperature change of expiration and inspiration detected by the thermistor 18.

Next, a description will be given of a configuration of a detection unit that processes signals detected by the earlobe sensor 4, the finger mounting probe 2, and the respiration sensor 15 to measure biological information. FIG. 9 is a block diagram schematically illustrating a circuit configuration of the detection unit. Signals detected by the earlobe sensor 4, the respiration sensor 15, and the finger-worn probe 2 are amplified by the amplification unit 26, and then a predetermined calculation process is performed by the biological information calculation unit 27. The amplification unit 26 and the biological information calculation unit 27 are housed in the biological amplifier 3. The biological information calculation unit 27 includes a ROM (Read Only Memory) storing a program.
ry), RAM (Randum Access Memor) for storing data
y) etc. and a CPU (Central
Processing Unit) and signal processing means such as a filter as appropriate.

In the biological information calculation unit 27, the heart rate, the RR interval, the RR interval variation coefficient, the pulse rate, the pulse interval, the pulse interval variation coefficient, the respiration rate, the respiration Calculate measures such as the peak interval and the inter-respiration peak interval variation coefficient.

A procedure for calculating the heart rate, the RR interval, and the RR interval variation coefficient from the electrocardiogram-like waveform will be described with reference to the flowchart shown in FIG.

First, the signal of the heart rate measuring electrode is amplified in the amplifying section, and an electrocardiogram-like waveform is measured (step 1).
The baseline fluctuation is removed from the waveform thus obtained by a filter (step 2). Next, a threshold is set (step 3), and a section having a value larger than the threshold is extracted (step 4). The maximum value in the extracted section is determined (Step 5), and the R wave is detected (Step 6).
By detecting the R wave, the RR interval can be calculated (step 7). Here, the RR interval is a time interval between R waves of the ECG waveform shown in FIG. RR
From the interval, the heart rate for each beat can be calculated (step 8). In general, it is said that when relaxing, the RR interval is extended and the heart rate is decreased. Since the RR interval is not constant but fluctuates, an RR interval variation coefficient is calculated (step 9). Here, the RR interval variation coefficient refers to an average value and a standard deviation of RR interval data within a certain section,
The standard deviation is divided by the average value, multiplied by 100, and expressed in units of percent. This RR interval variation coefficient is generally considered to be large in a relaxed state.

Next, a process for calculating the pulse rate, the pulse interval, and the pulse interval variation coefficient from the pulse waveform will be described with reference to the flowchart shown in FIG.

First, the pulse wave waveform is measured by amplifying the signal of the pulse wave sensor in the amplifying section 26 (step 11), and the baseline fluctuation is removed from the waveform thus obtained by a filter (step 12). . Next, EC
Two points at which the R wave is detected in the G waveform are selected as reference points (step 13). A section having the reference point at both ends is extracted (step 14). The maximum value in the section is determined (step 15), and the peak value of the pulse wave is detected (step 16). Next, an interval between pulse wave peaks is calculated as an interval between pulse waves (step 17). Here, the pulse wave interval is a time interval between the selected points of the pulse wave shown in FIG. 13, and as the point, the peak of the pulse wave waveform may be selected as described above. Any point up to (for example, a 50% value) may be selected. Next, a pulse rate and a pulse wave interval variation coefficient are calculated from the pulse wave interval (steps 18 and 19). The pulse-to-pulse interval variation coefficient is defined in accordance with the RR interval variation coefficient, finds the average value and the standard deviation of the pulse-pulse interval data in a certain section, divides the standard deviation by the average value and multiplies by 100, It is expressed in units of percentage. Generally, in the relaxed state, the pulse rate decreases, the pulse interval increases, and the pulse interval variation coefficient increases.

In the present embodiment, since the heartbeat and the pulse wave can be measured simultaneously, the step 16 is performed based on the measurement of the R wave and the pulse wave detected in step 6 based on the electrocardiogram waveform measurement (step 1) (step 11). Pulse wave delay time (PTT: Pulse Transit T)
ime) can be calculated (step 21). The pulse wave delay time is, for example, a time lag between the R wave and a certain point of the pulse wave waveform as shown in FIG. PTT is regarded as an index related to blood pressure (New Physiological Psychology Volume 1, p.
161), since it also relates to information on the parasympathetic nervous system, it can be used for evaluation of a feeling of relaxation.

Next, the procedure for calculating the respiratory rate, the respiratory peak interval, and the respiratory peak interval variation coefficient will be described with reference to the flowchart shown in FIG.

First, the signal of the respiratory sensor is amplified by the amplifying unit to measure the respiratory curve (step 31), and the respiratory curve obtained in this way is smoothed (step 3).
2). Next, a differentiated waveform is obtained by differentiating the smoothed respiration curve (step 33). A zero cross point is extracted from the differential value waveform (step 34). A point where the sign reverses from positive to negative or from negative to positive before and after the zero cross point is determined (step 35), and the peak value of the respiration curve is detected (step 36). Next, the peak interval of the respiration curve is calculated (step 37). Calculate the respiratory rate and interbreathing interval variation from the peak interval of the respiratory curve (Step 3)
8, 39). Generally, in the relaxed state, the respiratory rate is reduced, the inter-breath interval is extended, and inter-breath interval variation is reduced.

In recent years, many studies have been conducted to evaluate the feeling of relaxation and the like from heartbeat fluctuations. However, since heartbeat fluctuations are affected by respiration, measurement of respiration is required for strict evaluation. Therefore, by using the respiration sensor according to the present embodiment, it is possible to evaluate a feeling of relaxation or the like based on the heartbeat fluctuation.

FIG. 15 shows the results obtained when four types of stimuli were loaded in combination with the striking stimulus and the fir stimulus, in which the strength and the slowness were combined. Data show the average of 20 subjects. As described above, these indices change depending on the massage stimulus, so that more appropriate massage stimulus control can be performed by using various sensors according to the present invention.

In this embodiment, the head-mounted probe integrated with the headphones has been described. However, the head-mounted probe may be configured without a speaker or the like.

[0043]

As described above, according to the biological information sensor according to the present invention, it is possible to reliably measure biological information even during massage treatment, although it is not non-contact.

[Brief description of the drawings]

FIG. 1 is a diagram showing a use state of a massage machine including a sensor according to an embodiment of the present invention.

FIG. 2A is a perspective view showing an overall configuration of an earlobe sensor, FIG. 2B is a diagram illustrating an example of arrangement of heart rate measurement electrodes, and FIG. 2C is an earlobe. FIG. 4 is a view showing a mounting state of the sensor for use.

FIG. 3 is a diagram showing a state of wearing headphones equipped with an earlobe sensor.

FIG. 4 is a diagram showing a state of wearing another headphone provided with an earlobe sensor.

FIG. 5A is a diagram illustrating an overall configuration of a headphone including a respiration sensor, and FIG. 5B is an enlarged view of a tip portion of the respiration sensor.

FIG. 6A is a diagram illustrating an entire configuration of a finger-mounted probe, and FIG. 6B is a diagram illustrating a mounted state of the finger-mounted probe.

FIG. 7A is a graph showing an example of a measurement result obtained by the heartbeat measurement electrode, and FIG. 7B is a graph showing a measurement result obtained by the heartbeat measurement electrode according to the present embodiment.

FIG. 8 is a graph showing an example of a respiration curve.

FIG. 9 is a block diagram illustrating a schematic configuration of a detection unit.

FIG. 10 is a flowchart illustrating an outline of a procedure of calculating a heart rate and the like based on electrocardiogram-like waveform measurement.

FIG. 11 is a flowchart illustrating an outline of a procedure for calculating a pulse rate and the like based on pulse wave waveform measurement.

FIG. 12 is a flowchart showing an outline of a procedure for calculating a pulse wave delay time based on measurement of an electrocardiogram-like waveform and a pulse wave waveform.

FIG. 13 is a graph showing a pulse wave delay time.

FIG. 14 is a flowchart showing an outline of a process for calculating a respiratory rate and the like based on respiration curve measurement.

FIGS. 15 (a), (b) and (c) are graphs showing examples of changes in pulse rate, pulse wave interval, and sense of relaxation measured during massage stimulation, respectively.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Headphone 2 Probe for wearing fingers 4 Sensor for earlobe 8 Pulse wave sensor 8a Irradiation part 8b Light receiving part 9 Electrode for heart rate measurement 11 Band 12, 13 Earpiece part 15 Respiration sensor 18 Thermistor 16 Support member 17 Mounting member 20 Belt 21 Pulse wave Sensor 21a Irradiation part 21b Light receiving part 22 Electrode for heart rate measurement 100 Massager

──────────────────────────────────────────────────の Continued on the front page (51) Int.Cl. ⁷ Identification symbol FI theme coat ゛ (Reference) A61B 5/16 A61B 5/04 310M (72) Inventor Yoko Moroki 24 Yamanouchi Yamanoshitamachi, Ukyo-ku, Kyoto-shi, Kyoto Address: OMRON Life Science Research Inc. (72) Inventor Yoshihiro Nakatsuji 24, Yamanouchi Yamanoshitamachi, Kyoto, Kyoto, Japan No. 24 OMRON Life Science Research Laboratories F-term (reference) 4C017 AA02 AA09 AA14 AA19 AB03 AB08 AB10 AC12 AC16 AC27 AC28 BC07 BC17 BC18 4C027 AA00 AA02 BB05 EE01 EE08 FF02 FF03 GG02 GG05 GG01 P00

Claims (9)

[Claims] 1. A biological information measuring sensor comprising a heart rate measuring electrode provided so as to be able to come into contact with one of right and left earlobes and a finger opposite to the earlobe. 2. A heart-rate measuring electrode provided so as to be able to contact the earlobe, a head-mounted probe having a mounting member to be mounted on the head, and a heart-rate measuring electrode provided so as to be able to contact a finger. The biological information measurement sensor according to claim 1, further comprising: a finger mounting probe having a finger mounting member for mounting on a finger. 3. The biological information measuring sensor according to claim 2, wherein a pulse wave sensor for detecting a pulse wave is provided on the head-mounted probe. 4. The biological information measurement sensor according to claim 2, wherein a pulse wave sensor for detecting a pulse wave is provided on the finger-mounted probe. 5. The biological information measurement sensor according to claim 2, wherein the head-mounted probe is provided with a thermistor and a holding member for holding the thermistor near the nasal cavity. 6. The biological information measurement sensor according to claim 5, wherein the holding member is a member that can be deformed to adjust a position of the thermistor. 7. The head-mounted probe according to claim 2, further comprising: an earpiece that abuts on or covers the ear, and a speaker that is provided on the earpiece and faces the ear. 7. The biological information measuring sensor according to any one of claims 6 to 6. 8. The biological information measuring sensor according to claim 2, wherein the finger mounting member is a belt-shaped member wound around a finger. 9. The biological information measuring sensor according to claim 2, wherein the finger mounting member is a sack-shaped member into which a finger is inserted.