JP2004113811A - Pressure detector - Google Patents

Abstract

PROBLEM TO BE SOLVED: To easily and accurately position a measurement object.
SOLUTION: The pulse wave detecting device includes a plurality of pulse wave detecting units 3, and a beam 81 of the pressure detecting device is attached to a support of the pulse wave detecting unit 3. The contact portion at the tip of the beam 81 is brought into contact with the arm of the subject, and a pressure change accompanying the pulsation of the radial artery 100 is detected by the piezoelectric element 82 on the beam. The supporting body that supports the beam is provided with two pressing legs 68 and 72 on both sides of the contacting portion of the beam, and the tip of the pressing leg is pressed against the arm of the subject. The pressing legs 68, 72 have a higher hardness than the radial artery 100, and the interval between them can be changed by operating the micrometer head 28. Further, the tip of the contact portion of the beam is located above the tip of the pressing leg, which is on the opposite side to the direction in which the tip is directed.
[Selection] Fig. 2

Description

The present invention relates to a pressure detecting device.

A pressure wave or a vibration of a blood vessel wall, which is generated along with the heartbeat and propagates in a blood vessel, is generally called a pulse wave. Since various medical information such as the motion state of the heart can be obtained from the pulse wave, an examination method of palpating the pulse wave has been adopted by Oriental medicine and the like for a long time.
In oriental medicine, when palpating a pulse wave, a measurer presses a wrist portion of a subject with a finger, and measures a pulse in the radial artery by tactile sensation (fingering). Depending on the pressing force at this time, the size of the perceived pulse changes, but in the field of oriental medicine, attention is paid to the change in pulse width (pulse amplitude) due to the change in pressing pressure, and this is used as a diagnostic element. .
For example, FIGS. 22 (A) to 22 (C) each show a change curve (hereinafter, referred to as a trend curve) of the pulse width according to the pressure change. The trend curve shown in FIG. 22A is a curve in the case where the peak is at the center and the clearest pulsation chart is obtained at the position of the middle (medium pressure), and such a curve is called a normal curve. . The fact that the pulse position (position of the pulse) is at a middle position is said to be one of the features of the normal pulse (normal wave).

The peak of the trend curve shown in FIG. 22B is shifted to the left. Such a trend curve is called a descending curve, and is a curve in a case where the best pulse diagram can be obtained by reducing the pressure. In other words, the curve shows a case where the pulse of the pulse is immediately and clearly obtained when the finger is lightly touched, and the pulse weakens when the force is applied. Such a pulse position is called floating, and a pulse whose pulse position is floating is called floating pulse.
The peak of the trend curve shown in FIG. 22C is shifted to the right, and such a curve is called a rising curve. It is a curve when the pulse is not felt even if the finger is pressed lightly, and the best pulse is obtained only when the finger is pressed heavily. Such a pulse position is called a sink and a pulse whose pulse position is a sink is called a sink pulse.
The floating vein is said to be a pulse indicating that the illness is present on the body surface, and the sinking vein is said to indicate that the illness is deep in the body. As described above, in pulse diagnosis, the relationship between pressure and pulse width is an important factor in knowing the state of a subject.

However, some of the subjects are fat and some are thin, and their muscles and fat are attached in various ways, and their elasticity is various. That is, the degree of deformation of the living tissue with respect to the change in the pressing force varies from person to person. Then, the amplitude of the pulse greatly varies depending on the distance from the epidermis to the blood vessel or the way the blood vessel is crushed when pressed. In palpation, the measurer can determine whether the pulse wave pattern of the subject is a normal pulse, a floating pulse, or a sediment while changing the pressing force by himself / herself. When diagnosing a pulse wave using the apparatus, it is preferable that the initial pressure given to the blood vessel to be measured can be appropriately changed in advance.

Conventionally, a device for detecting such a pulse wave includes a pressure detection device provided with a pressure sensor such as a piezoelectric element or a strain gauge, and a part of the pressure detection device is brought into contact with the surface of a living body, for example, near a radial artery. It is made to let. Then, the stress applied to the pressure sensor in accordance with the pulsation of the blood vessel displaces the pressure sensor, and the pressure sensor outputs a pulse wave signal corresponding to the change in the stress.
These pressure detecting devices are pressed with a certain amount of pressure toward the surface of the living body, thereby trying to constantly detect a pulse wave. Generally, as disclosed in JP-A-4-102438, JP-A-4-108424, JP-A-4-67839 and JP-A-4-67840, a pressure detecting device generally has an elastic bag-like shape. The pressure detection device is pressed against the surface of the living body by wrapping the cuff around the arm of the subject and forcing air into the cuff.
However, it is difficult to change the initial pressure applied to the blood vessel to a desired value if the pressure detection device is pressed against the surface of the living body with the cuff as in the related art. That is, since the surface of the cuff is substantially flat, when pressed with this, not only the blood vessels but also the surrounding muscles and tissues are pressed flat at the same time. Therefore, even if the same pressure is applied to the cuff, the pressure in the blood vessel cannot be uniquely determined. Furthermore, when a pressure detecting device is attached to the cuff, it is difficult to accurately position the pressure detecting device with respect to a blood vessel to be measured, for example, a radial artery.

In addition, a pen-shaped pulse wave detection device having a sensor attached to the tip is also used. In such a pulse wave detection device, the tip attached with the sensor is brought into contact with the epidermis of the subject, for example, near the radial artery, and the sensor detects the pulse wave according to the pulsation of the blood vessel.
Further, as disclosed in Japanese Patent Application Laid-Open No. 6-197873, there is an apparatus using a rubber glove having a strain gauge attached to a finger pad. The measurer puts on this rubber glove and presses a finger against the epidermis near the radial artery of the subject. In this state, the strain gauge attached to the finger pad detects a pulse wave.

However, when performing measurement using a pen-shaped pulse wave detection device or the above-described pulse wave detection device using rubber gloves, it is necessary for the measurer to press the sensor against the position of the radial artery of the subject. However, during the measurement, it is difficult for the measurer to keep the strain gauge provided at the finger pad and the sensor at the tip of the pen at the position of the radial artery, May deviate from the position. If the sensor deviates from the position of the radial artery as described above, accurate measurement cannot be performed.
If the analysis of the condition of a living body (for example, the analysis of the effect of a drug such as a hypotensive agent) is performed based on the measurement result having a problem with the accuracy measured by the above-described device, an erroneous analysis is performed.
Therefore, Japanese Patent Laid-Open Publication No. 1-155828 discloses a pulse wave detecting device capable of automatically determining a detection position. This device detects a pulse wave at a plurality of locations while moving the sensor in a direction intersecting the blood vessel, and detects a portion directly above the blood vessel from the amplitude of the obtained pulse wave and the like, and places the sensor at that position. It is fixed and detects pulse waves.

However, the technology disclosed in Japanese Patent Application Laid-Open No. 1-155828 requires a driving device for driving a sensor and a device for automatically determining a detection position, and has a problem that the device becomes large-scale. .
The present invention has been made in view of the above circumstances, and has as its object to provide a pressure detecting device with low energy loss.

The pulse wave detection device according to the present invention, one beam body whose base end side is supported by a support, a detection target part pressing part provided on the beam and pressed against a surface on the detection target part, A piezoelectric element that is mounted on the beam and outputs an electric signal corresponding to a change in pressure applied through the detection target portion pressing portion. Between the portion and the detection target portion pressing portion, a thin portion thinner than the other portion is formed, the piezoelectric element is longer than the thin portion, and in the longitudinal direction of the beam body It is characterized in that it is mounted on the entire thin portion and on the base end side or the detection target portion pressing portion side of the thin portion. According to this pressure detecting device, the strain energy accumulated in the piezoelectric element when pressure is applied to the beam is increased by extending the piezoelectric element to a portion closer to the base end of the beam than the thin portion. It is possible to do. As a result, the output current generated by the piezoelectric element can be made larger than before.

From another point of view, the pressure detection device according to the present invention includes: a beam having a base end side supported by a support; and a detection target portion pressing provided on the beam and pressed against a surface on a detection target. And a piezoelectric element mounted on the beam body and outputting an electric signal corresponding to a change in pressure applied through the detection target pressing section, wherein the piezoelectric element is mounted. The ratio of the cross-sectional area of the beam to the total cross-sectional area of the beam and the piezoelectric element is 60% or less. According to this pressure detecting device, by reducing the ratio of the cross-sectional area of the beam, the strain energy stored in the beam decreases, and the strain energy stored in the piezoelectric element relatively increases. It is possible to relatively increase the rate at which the element is converted from strain to electrical energy. Thereby, it is possible to increase the amplitude of the output signal from the piezoelectric element.

Hereinafter, various embodiments according to the present invention will be described with reference to the accompanying drawings.

<1. First Embodiment>
<1-1. Configuration of Pulse Wave Detection Device of First Embodiment>
First, as shown in FIG. 1, a pulse wave detection device 1 according to a first embodiment of the present invention includes a stand 2 placed on a floor, and three similar pulse waves supported by the stand 2. And a detection unit 3. The stand 2 includes an erect shaft 2a and an arm 2b attached to the shaft 2a, and a bracket 4 is disposed at a tip of the arm 2b.
The mounting height of the base end of the arm 2b with respect to the shaft 2a is adjustable, the arm 2b is rotatable about the shaft 2a, and the position in the rotation direction is adjustable. Further, the arm 2b is rotatable along a vertical plane, and its position in the rotation direction is adjustable. These adjustment mechanisms are known, and the description thereof is omitted. By adjusting the stand 2 in this manner, the position of the bracket 4 can be adjusted. However, as long as the position of the bracket 4 can be adjusted, any mounting means may be used instead of the stand 2.

This pulse wave detection device 1 is provided with an arm support 5. The arm support 5 has a substantially rectangular parallelepiped shape, and an upper surface 5a thereof has a planar shape. The arm support 5 has a recess 5b that opens upward. An upwardly protruding convex wall 5c is formed near the concave portion 5b, and a cylindrical rod 6 parallel to the upper surface 5a facing upward of the concave portion 5b is attached to the convex wall 5c.
On the upper surface 5a of the arm support 5, a human arm (detection target) 7 as a subject is placed. Then, the palm of the subject is turned upward, and the hand 8 is arranged below the rod 6. In this state, the hand 8 is slightly bent downward from the wrist and is made to enter the inside of the concave portion 5b. In this way, the arm 7 is fixed unless the subject intentionally moves. By adjusting the stand 2 as described above, three pulse wave detection units (pulsation detection devices) 3 are arranged above the arm 7 placed above the upper surface 5a. Each of the three pulse wave detection units 3 detects a pulse wave corresponding to a dimension, a seki, and a scale in Oriental medicine.

2 (A), 2 (B), 3 and 4 show a single pulse wave detection unit 3. FIG. The pulse wave detection unit 3 includes a support 10 and a pressure detection device 80 supported on the support 10 in a cantilever manner. As will be described later, the supporting body 10 is formed with two pressing legs (a blood vessel pressing portion and a detection target portion pressing portion) 68 and 72, and the pressing legs 68 and 72 are attached to the arm 7 of the subject. It is directed to press it.
The support 10 includes a rectangular flat plate-like mounting plate 11 located above in these figures. As shown in FIG. 1, the mounting plate 11 is fixed to the bracket 4 by screws 13, whereby the support 10 is arranged in a vertical plane. In the three pulse wave detection units 3, these mounting plates 11 are parallel to each other. As shown in FIGS. 2 (A), 2 (B), 3 and 4, a pair of through holes 12 for inserting screws 13 are formed in the upper part of the mounting plate 11.
A circular opening 14 is formed in the lower part of the mounting plate 11. A first vertical sliding plate 16 is fixed to the mounting plate 11 by four screws 15 arranged around the opening 14. The first vertical sliding plate 16 has a substantially rectangular flat plate shape, and a vertical guide groove 17 extending in the vertical direction is provided on a surface opposite to the mounting plate 11.

On the opposite side of the first vertical sliding plate 16 from the mounting plate 11, a second vertical sliding plate 18 slidable with respect to the first vertical sliding plate 16 is arranged. The second vertical sliding plate 18 is also a substantially rectangular flat plate, and two parallel rails 19 and 20 are fixed to the surface on the first vertical sliding plate 16 side. The rails 19 and 20 are fitted in the vertical guide grooves 17 of the first vertical sliding plate 16, whereby the second vertical sliding plate 18 is vertically moved with respect to the first vertical sliding plate 16. It can be moved to. Further, the first and second vertical sliding plates 16 and 18 are engaged by a mechanism (not shown) so as not to be separated from each other in the front and back directions.
Pins 21 and 22 are arranged in the space between the rails 19 and 20. The upper pin 21 is fixed to the second vertical sliding plate 18, and the lower pin 22 is fixed to the first vertical sliding plate 16. Hooks provided at both ends of the coil spring 23 are hooked to these pins 21 and 22, whereby the second vertical sliding plate 18 is constantly drawn downward.
As shown in FIGS. 2A and 3, an L bracket 25 is fixed to the second vertical sliding plate 18 by screws 24, and the first vertical sliding plate 16 is fixed to the second vertical sliding plate 16 by screws 26. The L fitting 27 is fixed. The bent front end portion 25a of the L bracket 25 projects toward the near side of the paper of FIG. 2A, and the bent front end portion 27a of the L bracket 27 projects to the back side of the paper of FIG. 2A. Thus, the distal end portion 25a and the distal end portion 27a overlap each other on a vertical straight line.
A sleeve 29 of a micrometer head 28 is attached to a tip 25 a of the L bracket 25 by a nut 30. The micrometer head 28 is of a known form having a sleeve 29, a thimble 31, and a spindle 32.

On the other hand, a headless screw 34 is screwed to the distal end portion 27a of the L bracket 27, and the position of the headless screw 34 is fixed by a nut 35. The spindle 32 of the micrometer head 28 and the headless screw 34 are arranged coaxially with each other, and the end face of the spindle 32 of the micrometer head 28 because the coil spring 23 pulls the second vertical sliding plate 18 downward. Is always butted against the upper end surface of the thimble 31.
With this configuration, when the thimble 31 of the micrometer head 28 is rotated around its axis, the spindle 32 expands and contracts. Since the headless screw 34 is fixed to the first vertical sliding plate 16 at the stationary position, when the spindle 32 is extended, the second vertical sliding plate is opposed to the urging force of the coil spring 23 described above. 18 rises. Conversely, when the spindle 32 is shortened, the second vertical sliding plate 18 moves down with respect to the first vertical sliding plate 16 by the urging force of the coil spring 23. FIG. 7 shows a state in which the second vertical sliding plate 18 has risen as compared with the state shown in FIG. The displacement of the second vertical sliding plate 18 is read by a known method using a scale provided on the thimble 31 of the micrometer head 28 and the sleeve 29.

On the side opposite to the micrometer head 28, two pins 36 are projected from the first vertical sliding plate 16. A thin plate 37 is stretched over these pins 36, and both ends of the thin plate 37 are fixed to the pins 36 by screws 38. A rectangular parallelepiped holding block 39 is attached to the second vertical sliding plate 18, and the thin plate 37 is fitted in a vertical groove 39 a formed in the holding block 39. A set screw 40 is screwed into the holding block 39. When the set screw 40 is fastened, the thin plate 37 fitted in the vertical groove 39a is firmly held by the holding block 39. . Therefore, after adjusting the height of the second vertical sliding plate 18 by operating the micrometer head 28, the second vertical sliding plate 18 is maintained at that height by fastening the set screw 40. Before adjusting the height of the second vertical slide plate 18 by operating the micrometer head 28, the set screw 40 is loosened to release the thin plate 37 from the holding force of the holding block 39.

As shown in FIGS. 2B and 3, a connecting plate 42 is fixed by screws 41 to a surface of the second vertical sliding plate 18 opposite to the first vertical sliding plate 16. . The connecting plate 42 has a length in the vertical direction that is at least twice as long as the second vertical sliding plate 18, and circular openings 43 are formed in the upper and lower portions, respectively.
A first horizontal sliding plate 44 is fixed to a lower portion of the connecting plate 42 with a screw 45. The first lateral sliding plate 44 is substantially rectangular and has a flat plate shape, and a lateral guide groove 46 extending in the lateral direction is provided on a surface opposite to the connecting plate 42.
A second horizontal sliding plate 47 slidable with respect to the first horizontal sliding plate 44 is disposed on the side of the first horizontal sliding plate 44 opposite to the connecting plate 42. The second horizontal slide plate 47 is also substantially rectangular flat plate, and two parallel rails 48 and 49 are fixed to the surface on the first horizontal slide plate 44 side. The rails 48 and 49 are fitted in the lateral guide grooves 46 of the first lateral sliding plate 44, so that the second lateral sliding plate 47 is moved in the lateral direction with respect to the first lateral sliding plate 44. It can be moved to. Further, the first and second vertical sliding plates 44 and 47 are engaged by a mechanism (not shown) so as not to be separated from each other in the front and back directions.
In the space between the rails 48 and 49, pins 50 and 51 are arranged. The left pin 50 in FIG. 2A is fixed to the second horizontal sliding plate 47, and the right pin 51 in FIG. 2A is fixed to the first horizontal sliding plate 44. Have been. Hooks provided at both ends of the coil spring 52 are hooked to these pins 50 and 51, whereby the second horizontal sliding plate 47 is constantly pulled to the left in FIG. Has been.

As shown in FIGS. 2A and 3, an L bracket 54 is fixed to the first horizontal sliding plate 44 with a screw 53, and the second horizontal sliding plate 47 is fixed with a screw 55. The L fitting 56 is fixed. The bent front end portion 54a of the L bracket 54 projects toward the near side of the paper of FIG. 2A, and the bent front end 56a of the L bracket 56 projects toward the back side of the paper of FIG. 2A. Thus, the distal end portion 54a and the distal end portion 56a overlap each other on a horizontal straight line.
A sleeve 58 of a micrometer head (adjustment means) 57 is attached to a distal end 56 a of the L fitting 56 by a nut 59. The micrometer head 57 has a sleeve 58, a thimble 60, and a spindle 61, like the micrometer head 28.

On the other hand, a headless screw 63 is screwed into the distal end portion 54 a of the L fitting 54, and the position of the headless screw 63 is fixed by a nut 64. The spindle 61 and the headless screw 63 of the micrometer head 57 are arranged coaxially with each other, and the coil spring 52 pulls the second horizontal sliding plate 47 to the left in FIG. The end face of the spindle 61 of the meter head 57 always abuts on the upper end face of the thimble 60. For clarity, FIG. 5 shows a state where the pulse wave detection unit 3 is viewed from below.
With this configuration, when the thimble 60 of the micrometer head 57 is rotated around its axis, the spindle 61 expands and contracts. Since the headless screw 63 is fixed to the stationary first horizontal sliding plate 44, when the spindle 61 is extended, the first horizontal sliding plate 44 resists the urging force of the coil spring 23. On the other hand, the second horizontal sliding plate 47 moves to the right in FIG. Conversely, when the spindle 61 is shortened, the second horizontal sliding plate 47 moves to the left in FIG. 2A with respect to the first horizontal sliding plate 44 by the urging force of the coil spring 23. . FIG. 7 shows a state in which the second horizontal slide plate 47 has been moved to the left as compared with the state shown in FIG. The displacement of the second horizontal slide plate 47 is read by a scale provided on the thimble 60 and the sleeve 58 of the micrometer head 57.

A rectangular notch 42a for reading the scale of the micrometer head 57 is formed at the lower end of the connection plate 42 described above. In FIG. 2A, a bent first pressing plate 65 is fixed to the right end surface and the lower end surface of the connecting plate 42. The first pressing plate 65 includes a vertical portion 66 fixed to the right end face of the connecting plate 42, a horizontal portion 67 bent at a right angle from a lower end of the vertical portion 66, and a vertical portion bent obliquely downward from the horizontal portion 67. And one pressing leg 68. As shown in FIG. 3, the horizontal portion 67 is fixed to the lower end surface of the connecting plate 42. On the other hand, the lower end of the first pressing leg 68 is bent downward.
Further, a second pressing plate 70 is fixed to the second horizontal sliding plate 47 by a screw 69. The second pressing plate 70 has a flat mounting portion 71 fixed to the front surface in FIG. 2A of the second horizontal sliding plate 47, and a long rectangular shape bent at a right angle from the mounting portion 71. A second pressing leg 72 having a flat plate shape. The lower part of the second pressing leg 72 is wider than the upper part, and is opposed to the first pressing leg 68 of the first pressing plate 65. On the other hand, the lower end of the second pressing leg 72 is bent obliquely downward. As described above, the second lateral sliding plate 47 is moved in the lateral direction with respect to the first lateral sliding plate 44, so that the first pressing leg 68 and the second pressing leg 72 Is adjusted.

As shown in FIG. 2A, the pressing legs 68 and 72 are brought into contact with both sides of the radial artery (detection target) 100 in the arm 7 of the subject. FIG. 2A shows a cross-sectional view of the arm 7, in particular, the radius 101, the ulna 102, the brachioradialis tendon 103, and the radial carpal flexor tendon 104. The first pressing leg 68 compresses a highly elastic portion between the radial artery 100 and the radial carpal flexor tendon 104 in the living body, and the second pressing leg 72 presses the radial artery 100 and the brachioradialis tendon 103. Squeeze the elastic part between. On the surface of the living body, the elasticity near the blood vessel or tendon is low, and the elasticity is high in other parts. Therefore, the pressing legs 68 and 72 are configured to depress the pressed part.
The mounting plate 11, the first vertical sliding plate 16, the second vertical sliding plate 18, the connecting plate 42, the first horizontal sliding plate 44, and the second horizontal sliding, which are components of the support 10 described above. The moving plate 47, the first pressing plate 65, and the second pressing plate 70 are all made of metal, but have higher hardness than a blood vessel (radial artery in this embodiment) from which a pulse wave is measured. However, it is not limited to these. For example, these may be formed of a hard resin or the like.

Now, a pressure detecting device 80 is supported on the horizontal portion 67 of the first pressing plate 65. The pressure detection device 80 includes a beam 81 supported in a cantilever manner on the horizontal portion 67 and a piezoelectric element (pulsation detection sensor, pressure sensor) 82 bonded to the beam 81. The beam body 81 includes a planar supported portion 85 serving as a base end portion fixed to the horizontal portion 67, a contact portion (a blood vessel pressing portion, a measurement target portion pressing portion) 86 that bends vertically from the supported portion 85, and And a substantially L-shaped member. The center of the supported portion 85 of the beam body 81 is fastened to the horizontal portion 67 by bolts 83 and nuts 84, and the end of the supported portion 85 is pressed onto the horizontal portion 67 by a pressing plate 84a. Is fixed to the horizontal portion 67.
The contact portion 86 of the beam 81 is disposed in a space between the first pressing leg 68 and the second pressing leg 72 facing each other. In other words, the pressing legs 68, 72 are arranged on both sides of the contact portion 86. The tip of the contact portion 86 is directed downward, and is brought into contact with the surface of the arm 7 of the subject just above the radial artery 100. The distal end of the contact portion 86 is located above the distal ends of the pressing legs 68 and 72, that is, on the opposite side of the direction in which the distal ends are directed. In a state where no stress is applied to the beam 81, the tip of the contact portion 86 is preferably 0.5 to 2 mm above the tips of the pressing legs 68 and 72, and more preferably 0.9 to 1 .1 mm above.

先端 As shown in FIG. 6A, the distal end side of the supported portion 85 of the beam 81 is formed to be thinner than other portions (this portion is referred to as a thin portion 87). As shown in FIGS. 6B and 6C, three parallel grooves 88 are formed from the thin portion 87 of the supported portion 85 to the contact portion 86. In other words, the portion from the thin portion 87 to the contact portion 86 is branched into four. Then, the four piezoelectric elements 82 are bonded to the upper surfaces of the thin-walled portions 87 branched into four. More precisely, the four piezoelectric elements 82 are longer than the thin portion 87, and are bonded to the entire thin portion 87 and the supported portion 85 side of the thin portion 87 in the longitudinal direction of the beam 81. . 6A and FIG. 6C, reference numeral 90 denotes a through hole through which the fixing bolt 83 is inserted.

In the above configuration, the stress applied to the four contact portions 86 fluctuates according to the pulsation of the radial artery 100. This stress variation is transmitted to each piezoelectric element 82 via each thin portion 87. Each piezoelectric element 82 outputs a voltage corresponding to the fluctuation of the stress as a pulse wave signal (pulsation signal). On the supported portion 85 of the beam 81, four signal amplification units 89 each having a built-in operational amplifier described later are mounted. The pulse wave signal from the piezoelectric element 82 is supplied to a corresponding signal amplification unit 89, where it is amplified and output to the outside.
As described above, the beam 81 of each pulse wave detection unit 3 is provided with four contact portions 86, and these contact portions 86 are arranged at intervals along the extending direction of the radial artery 100. In this manner, each pulse wave detection unit 3 detects four pulsations in the arm 7 of the subject. As described above, since three pulse wave detection units 3 are provided, the pulse wave detection device 1 detects pulsations at a total of 12 points.

FIG. 18 shows an output circuit of the piezoelectric element 82. FIG. 18A shows an output circuit for extracting the output of the piezoelectric element 82, and this output circuit a is composed of four operational amplifiers OP1 to OP4. These operational amplifiers OP <b> 1 to OP <b> 4 are respectively built in the signal amplification unit 89. Each of the operational amplifiers OP1 to OP4 is connected to an inverting input terminal and an output terminal so as to form a voltage follower. The piezoelectric element 82 is interposed between the inverting input terminals of the operational amplifiers OP1 to OP4 and the ground. The input impedance of each operational amplifier in the above configuration is about 10 ⁸ to 10 ¹² Ω. In this case, if each operational amplifier is constituted by, for example, a MOSFET, the input impedance generally becomes high as described above. The reason why the output circuit having the high input impedance is used is that the output signal of the piezoelectric element 82 is very small, so that if an input circuit having a low impedance is used, the output signal cannot be obtained. As shown in FIG. 19, according to the experiment, an amplitude of about 0.15 V was obtained from the output terminals of the operational amplifiers OP1 to OP4.

The output signals of the operational amplifiers OP1 to OP4 are supplied to an external analog / digital converter (not shown), where they are converted into digital signals and supplied to a computer (not shown). The output circuit a shown in FIG. 18 is for the single pulse wave detection unit 3, that is, provided for the single beam 81. The circuit a shown in FIG. The above-described analog / digital converter performs signal conversion for a total of 12 channels corresponding to the operational amplifiers OP1 to OP4 of the three pulse wave detection units 3, and the computer performs a predetermined program based on the signals of the total 12 channels. Make a diagnosis of the subject.

Further, in the above-described pressure detecting device 80, since the thin portion 87 is formed in the beam 81, the curvature and the distortion of the piezoelectric element 82 due to the pressure fluctuation are compared with the case where the thin portion 87 is not formed. The detection accuracy of the piezoelectric element 82 can be improved. On the other hand, the four piezoelectric elements 82 are longer than the thin portion 87, and each piezoelectric element 82 is bonded to the entire thin portion 87 and the supported portion 85 side of the thin portion 87 in the longitudinal direction of the beam 81. I have. By increasing the length of the piezoelectric element 82 up to the supported portion 85 in this manner, it is possible to increase the strain energy stored in the piezoelectric element 82 when pressure is applied to the beam 81.

Conventionally, in a pressure detecting device using a beam as described above, a piezoelectric element is bonded only to a tip side (a contact portion 86 side, for example, a thin portion 87 in the embodiment) of a cantilever having a large curvature. Was common. However, in this case, since the size of the piezoelectric element is small, the strain energy stored in the piezoelectric element is very small, and the output current of the piezoelectric element becomes extremely weak, which may not be detected. This is because a high voltage can be easily obtained with a pressure detecting device using a piezoelectric element, but the generated current is very small.
On the other hand, in the pressure detection device 80 described above, by increasing the strain energy stored in the piezoelectric element 82, the output current generated by the piezoelectric element 82 can be made larger than in the past. This makes it possible to increase the amplitude of the output signal in combination with the output circuit having a high input impedance. In the above description, each piezoelectric element 82 is bonded to the entire thin portion 87 and the supported portion 85 side of the thin portion 87 in the longitudinal direction of the beam 81, but from the entire thin portion 87 and the thin portion 87. May be bonded to the contact portion 86 side, or may be bonded to the entire thin portion 87 and to both the supported portion 85 side and the contact portion 86 side.
In order to store a large amount of strain energy, it is desirable that the area of the piezoelectric element 82 be as large as possible. However, if the area of the piezoelectric element 82 is increased, the capacitance increases, which may lead to a decrease in detection accuracy. Therefore, the area of the piezoelectric element 82 is set to 130% to 150% with respect to the area of the thin part 87, and the area of the piezoelectric element 82 which protrudes from the thin part 87 becomes 30% to 50% of the area of the thin part 87. It is preferable to do so.

FIG. 20 is a cross-sectional view of the pressure detection device 80 as viewed along the line XX-XX in FIG. As shown in FIG. 20, the thickness Ts of the thin portion 87 of the beam 81 is substantially the same as the thickness Tp of the piezoelectric element 82. This is for the following reason.
In FIG. 21, in a pressure detecting device 80 using phosphor bronze as a beam member 81 and a ceramic piezoelectric element 82, a piezoelectric member with respect to a relative thickness (Ts / (Ts + Tp)) of a thin portion (support layer of the piezoelectric element 82) 87. 6 shows a change in the electromechanical coupling coefficient of the element 82. The electromechanical coupling coefficient indicates the conversion efficiency of electro-mechanism in the pressure detecting device 80, and in this example, indicates the square root of the ratio of energy converted into electric output with respect to energy input in a mechanical form. . However, the result of FIG. 21 is not limited to the case where the beam 81 is formed of phosphor bronze, and the same result is obtained when the beam 81 is formed of another spring material. That is, the present invention is not limited to the case where the beam 81 is formed of phosphor bronze.

よ う As is clear from FIG. 21, the electromechanical coupling coefficient becomes maximum when the relative thickness of the thin portion 87 is about 20%, and gradually decreases when the relative thickness exceeds about 20%. When the relative thickness of the thin portion 87 is about 60%, the electromechanical coupling is equivalent to that of the thin portion 87 having a thickness of 0 (the contact portion 86 is supported by a cantilever-shaped piezoelectric element). When the relative thickness of the thin portion 87 exceeds about 60%, the electromechanical coupling coefficient decreases almost linearly. The experimental results show that the relative thickness of the thin portion 87 is preferably about 60% or less. Further, in order to increase the conversion efficiency of the piezoelectric element 82 by increasing the electromechanical coupling coefficient, the relative thickness of the thin portion 87 is preferably about 20%. The above result was obtained because, when the cross-sectional area of the thin portion 87 was increased, the strain energy stored in the thin portion 87 was increased, and the strain energy stored in the piezoelectric element 82 was relatively reduced. It is considered that the rate of conversion into electric energy by the element 82 is relatively reduced.

On the other hand, it is also conceivable to support the contact portion 86 with a cantilever piezoelectric element without providing the thin portion 87 of the beam 81. In this case, it is theoretically considered that the conversion efficiency is improved because all the applied strain energy is accumulated in the piezoelectric element. However, considering factors such as the speed at which the applied pressure is stored as strain energy and the damping of vibration, a beam 81 separate from the piezoelectric element 82 is provided as in the above-described embodiment, and the piezoelectric element 82 is provided thereon. It is desirable to mount 82.
For the above reason, the beam 81 is provided separately from the piezoelectric element 82, and the piezoelectric element 82 is mounted on the beam 81, and the sectional area of the beam 81 with respect to the total sectional area of the beam 81 and the piezoelectric element 82. It can be seen that it is preferable to set the ratio to 60% or less. Thereby, the amplitude of the output signal from the piezoelectric element 82 can be increased.

<1-2. Method of Using Pulse Wave Detector of First Embodiment>
Now, a method of using the pulse wave detection device 1 according to the above embodiment will be described. Before this use, the micrometer head 28 is operated to raise the second vertical sliding plate 18 and the members suspended therefrom in advance, and the micrometer head 57 is operated to operate the pressing leg 68. , 72 are widened.
First, with the subject's arm 7 positioned as shown in FIG. 1, the stand 2 is adjusted so that the three pulse wave detection units 3 are positioned just above the arm 7 in size, seki, and length. To At the same time, the four contact portions 86 of the pressure detection device 80 of each pulse wave detection unit 3 are set to be almost directly above the radial artery 100 of the subject.

Next, by operating the micrometer head 28, the spindle 32 is shortened, and the second vertical sliding plate 18 is lowered. As a result, the connecting plate 42 suspended from the second vertical sliding plate 18 is also lowered, and the pressing leg portions 68 and 72 and the contact portion 86 are brought into contact with the surface of the arm 7. In this case, the micrometer head 28 is operated until the first pressing leg 68 presses the highly elastic portion between the radial artery 100 and the radial carpal flexor tendon 104 to dent it to a predetermined depth.
Thereafter, by operating the micrometer head 57, the spindle 61 is shortened, and the second pressing leg 72 is brought closer to the first pressing leg 68. Then, when the second pressing leg 72 dents the highly elastic portion between the radial artery 100 and the brachioradialis tendon 103 and enters this portion, the operation of the micrometer head 57 is stopped and the second The pressing leg 72 is stopped. In FIG. 7, the solid line shows the second pressing leg 72 before approaching the first pressing leg 68, and the imaginary line shows the second pressing leg 72 after approaching. Then, with the contact portion 86 positioned just above the radial artery 100 in this way, pulse waves at 12 locations are diagnosed using output signals from a total of 12 piezoelectric elements 82.

As described above, by making the second pressing leg 72 movable with respect to the first pressing leg 68, the elastic surfaces (soft) on both sides of the radial artery 100 at the pressing legs 68, 72 are provided. And the four contact portions 86 of the pressure detection device 80 can be easily positioned directly above the radial artery 100. Moreover, since the distal end of the contact portion 86 is located higher than the distal ends of the pressing legs 68 and 72, the radial artery 100 having a lower elasticity (harder) than the other tissues is pressed by the pressing legs 68 and 72. It is designed to be easily positioned between 72. In other words, according to the present embodiment, the four contact portions 86 of the pressure detecting device 80 can be easily moved to the radial artery 100 without the subject moving the arm 7 or the diagnostician tilting the support 10. Can be positioned directly above the

Furthermore, when the pressure detection device is pressed against the surface of the living body with the cuff as in the conventional method, not only the blood vessels but also the surrounding muscles and tissues are simultaneously pressed flat, so that the initial pressure applied to the blood vessels is reduced to a desired value. Although it was difficult to change the value to a value, according to the present embodiment, the two rigid pressing legs 68 and 72 are used to depress the soft surfaces on both sides of the radial artery 100, so that the pressure detecting device 80 It is easy to change the initial pressure applied to the radial artery 100 at the contact portion 86 to a desired value. That is, in the present embodiment, the contact portion 86 of the pressure detecting device 80 not only serves to transmit a stress change to the piezoelectric element 82 but also changes the initial pressure on the radial artery 100 by being lowered by the micrometer head 28. It also has a role to do.

Now, as described above, the pressure leg portions 68, 72 are lowered to a predetermined depth, and once a pulse wave is diagnosed, the micrometer head 28 is operated again to further push the pressure leg portions 68, 72 and the contact portion 86. Lower deeply. This is to change the initial pressure applied to the radial artery 100 in advance. As described above, it is known that the pattern of the detected pulse wave may be different depending on the initial pressure applied to the blood vessel to be measured (see FIG. 22). It is possible to know in detail. FIG. 7 shows a case where the descending degree of the pressing leg portions 68 and 72 and the contact portion 86 is small, and FIG. 2 (A) shows a case where the descending degree is large.
Here, when the contact portion 86 is lowered, the initial pressure applied to the pressure detection device 80 increases. However, simply lowering the contact portion 86 causes the skin to be pulled by the pressing legs 68 and 72, so that the skin tension T shown in FIG. 8 fluctuates slightly compared to before the lowering. The pressure P detected by the pressure detection device 80 is affected by not only the internal pressure D of the radial artery 100 but also the skin tension T. Therefore, strictly, the initial pressure on the radial artery 100 is not uniquely determined.

FIG. 9 is a graph showing the relationship between the vertical displacement of the pressing legs 68 and 72 and the skin tension T when the interval between the pressing legs 68 and 72 is constant. Note that the horizontal axis represents the absolute value of the downward displacement of the first pressing leg 68 when the position where the first pressing leg 68 is in contact with the skin is set to 0. As shown in FIG. 9, the lower the first pressing leg 68 is, that is, the higher the initial pressure is due to the lowering of the contact portion 86, the greater the skin tension T is.
Therefore, the relationship between the vertical displacement of the pressing legs 68, 72 and the skin tension T when the interval between the pressing legs 68, 72 is fixed in advance, or the vertical direction of the pressing legs 68, 72. The relationship between the interval between the pressing legs 68 and 72 and the skin tension T when the displacement is constant is examined in advance, and after the pressing legs 68 and 72 are lowered, the micrometer is determined based on the investigation result. The head 57 may be operated to adjust the distance between the pressing legs 68 and 72 so as to eliminate the influence of the skin tension T. That is, the skin tension T is kept constant at any measurement time. In this way, it is possible to change the initial pressure on the radial artery 100 very precisely to the desired value. The change of the initial pressure is performed for any of the three pulse wave detection units 3, and under the changed initial pressure, the output signals from the total of twelve piezoelectric elements 82 are used again for 12 points. Diagnose the pulse wave.

In oriental medicine pulse diagnosis, the subject's pulse is identified from more than ten types of qualitatively and quantitatively obtained pulses. Is required. For example, for a subject having a characteristic that a sufficient pressure is not applied to the vascular wall of the radial artery unless a large pressure is applied, the pulsation chart must be specified by subtracting that amount. Therefore, it is difficult for an unskilled physician to identify the optimal image.
On the other hand, in the above-described embodiment, since the initial pressure can be adjusted objectively, the diagnostician can quantitatively and qualitatively acquire the biological characteristics of the subject. In other words, if the present embodiment is used for pulse diagnosis, it is possible to objectively obtain biological characteristics that the diagnostician had to estimate based on his / her own sense, thereby reducing the burden on the diagnostician. It is also useful for handing down pulse detection techniques.

<1-3. Modification Example of First Embodiment>
In the above embodiment, by using the micrometer head 57 to move the second horizontal slide plate 47 with respect to the first horizontal slide plate 44, the second pressing leg 72 is moved to the first pressing position. Although the first pressing leg 68 is movable relative to the second pressing leg 72, the first pressing leg 68 may be movable relative to the second pressing leg 72. Further, both the pressing legs 68 and 72 may be movable. The above change can be similarly applied to the second to fourth embodiments described later.
Further, a pressure sensor such as a strain gauge can be used instead of the piezoelectric element 82.
Furthermore, the beam body 81 is supported in a cantilever shape. However, if the relationship between the load applied to the contact portion 86 and the strain generated in the pressure sensor is uniquely determined, other supporting members such as a two-sided support beam shape can be used. You may support a beam body in a state.

<2. Second Embodiment>
<2-1. Configuration and Function of Pulse Wave Detection Device of Second Embodiment>
Next, a second embodiment according to the present invention will be described. FIG. 10 shows a main part of a pulse wave detection device according to the second embodiment. This pulse wave detection device also includes three pulse wave detection units 3 similar to those shown in FIG. 1, and each pulse wave detection unit 3 is provided with a support 10. The type of the pulsation detection sensor provided on the support 10 is different from that of the first embodiment. Illustration of components common to the first embodiment is omitted.

As shown in FIG. 10, a beam 110 is fixed to the horizontal portion 67 of the first pressing plate 65 of the support 10 in the same fixing method as the beam 81 of the first embodiment. The beam body 110 is a substantially L-shaped member including a planar supported portion 111 fixed to the horizontal portion 67 and a bent portion 112 that bends vertically from the supported portion 111. The beam body 110 may not be branched like the beam body 81 of the first embodiment, but in this embodiment, the beam body 110 is branched like the beam body 81 and a plurality of bent portions 112 are provided. (See FIGS. 6B and 6C).
The bent portion 112 of the beam 110 is arranged in a space between the first pressing leg 68 and the second pressing leg 72 facing each other. In other words, the pressing legs 68 and 72 are disposed on both sides of the bent portion 112. The tip of the bent portion 112 is directed downward, and an optical beat detection sensor 113 is attached to the lowermost surface of each bent portion 112. Then, the optical pulsation detection sensor 113 is brought into contact with the surface of the arm 7 of the subject just above the radial artery 100. The optical pulsation detection sensor 113 is located above the tips of the pressing legs 68 and 72, that is, on the opposite side of the direction in which the tips are directed. With no stress applied to the beam 110, the optical pulsation detection sensor 113 is preferably 0.5 to 2 mm above the tips of the pressing legs 68, 72, and more preferably 0.9. １．１1.1 mm above.

Under the above configuration, by lowering the beam 110 by operating the micrometer head 27 (see FIG. 2A and the like), the bent portion 112 of the beam 110 It presses the epidermis just above the artery 100 to apply initial pressure to the radial artery 100. That is, the bent part 112 and the optical pulsation detection sensor 113 constitute a blood vessel pressing part or a detection target part pressing part.

Although not shown, each optical pulsation detection sensor 113 includes a light emitting element (emission means) and a light receiving element (receiving means) on its lower end surface. Be able to point to the upper skin. Then, the light emitting element emits light toward the radial artery 100, and the light reflected from the radial artery 100 is received by the light receiving element.
The light receiving element outputs a pulse wave signal (pulsation signal) corresponding to the amount of received light, and the pulse wave signal is amplified by an amplifier (not shown) and then supplied to an external analog / digital converter (not shown) having 12 channels. The data is converted into a digital signal and supplied to a computer (not shown). The computer diagnoses the subject according to a predetermined program based on signals of a total of 12 channels.

The principle of pulse wave detection by the optical pulsation detection sensor 113 is as follows.
When light is applied to a thin film, transmitted light decreases relative to incident light by an amount proportional to the concentration of the substance and the optical path length. This is well known as Lambert-Beer's law.
With reference to FIGS. 11A and 11B, Lambert-Beer's law will be described. As shown in FIG. 11A, assuming that the concentration of the substance M is C, the minute optical path length is ΔL, the amount of incident light is Iin, the amount of transmitted light is Iout, and the extinction coefficient of the substance M is k, the following equation is obtained. To establish.
Iout / Iin = 1−kCΔL (1)
Here, as shown in FIG. 11 (B), when the optical path length is increased by a factor of 5, the relationship of equation (1) changes as follows.
Iout / Iin = (1−kCΔL) ⁵ (2)
This is because, for example, when the incident light amount Iin shown in FIG. 11A is 10 and the transmitted light amount is 9, in the case shown in FIG. There can be 5.9, i.e., is that the Iout / Iin = 0.9 ^5.
Therefore, the relationship between the amount of incident light and the amount of transmitted light for an arbitrary distance L is obtained by integrating Expression (1),
log (Iout / Iin) = (− kCL) (3)
It becomes. By transforming this equation (3),
Iout = Iin × exp (−kCL) (4)
It becomes.

判 As can be seen from this, if the incident light amount Iin, the extinction coefficient k and the optical path length L are constant, the change in the concentration of the substance M can be measured by measuring the transmitted light amount Iout. Further, even if the reflected light reflected by the substance M is measured instead of the transmitted light amount, the change in the concentration of the substance M can be measured on the same principle as in the case described above. When the substance M is blood, measuring the change in concentration means measuring pulsation of blood, that is, measuring pulse.

FIG. 12 is a graph showing an example of a change over time in absorbance when light including a human blood vessel is irradiated from the outside to the vicinity thereof. In this figure, the absorbance component I ₄ due to arterial blood whereas changes, light absorption component I ₂ by tissue is constant because the tissue concentration does not change. Moreover, absorption component I ₃ due to venous blood is also constant. This is because there is no pulsation in the vein and no change in concentration.
FIG. 13 is a graph showing an example of a blood pressure distribution in each part of the body. As can be seen from this figure, the pulsation of the blood pumped from the heart gradually disappears as it travels through the body, and disappears completely in the veins. On the other hand, the absorbance of the light absorption component I ₄ (see FIG. 12) due to arterial blood changes because there is a concentration change corresponding to the pulse. Thus, the blood vessel, for example by irradiating light to the radial artery 100, when measuring the light intensity of the transmitted or reflected light, there would each component I ₂ ~I ₄ affects. If the sum of the absorption component _{I 4} due to absorption component _{I 3} and arterial by venous blood is 100%, the proportion of the absorption component _{I 4} due to arterial blood occupied there is 1% to 2%, the remaining 98% to 99% is absorption component I ₃ due to venous blood.

Using the above principle, the optical pulsation detection sensor 113 can detect a pulse wave by receiving reflected light from the vicinity including the radial artery 100. Then, the highly elastic (soft) surfaces on both sides of the radial artery 100 are depressed by the pressing legs 68 and 72, and the four contact portions 86 of the pressure detection device 80 are easily positioned directly above the radial artery 100. Is possible. Moreover, since the distal end of the contact portion 86 is located higher than the distal ends of the pressing legs 68 and 72, the radial artery 100 having a lower elasticity (harder) than the other tissues is pressed by the pressing legs 68 and 72. It is designed to be easily positioned between 72. In other words, according to the present embodiment, the four optical pulsation detection sensors 113 can easily detect the radial artery 100 without the subject moving the arm 7 or the diagnostician tilting the support 10. It is possible to position directly above.
Furthermore, the two rigid pressing legs 68 and 72 dent the soft surfaces on both sides of the radial artery 100, so that the initial pressure applied from the beam 110 to the radial artery 100 via the optical pulsation detection sensor 113. Can be easily changed to a desired value.

<2-2. Modification Example of Second Embodiment>
FIG. 14 shows a modification of the second embodiment. Here, the light emitting portion 113a and the light receiving portion 113b of the optical beat detection sensor 113 are separated, and the light emitting portion 113a is attached to the lower end surface of the bent portion 112 of the beam 110. On the other hand, the light receiving portion 113b is arranged in the concave portion 5b (see FIG. 1) of the arm support base 5. Instead, the light receiving unit 113 b may be suspended from the support 10.
The light emitting unit 113a includes the above light emitting element, and the light receiving unit 113b includes the light receiving element. In this modified example, the light receiving section 113b receives light transmitted through the radial artery 100.
In the above-described embodiment, the optical pulsation detection sensor 113 is used. However, the ultrasonic pulsation detection device includes a transmitting ultrasonic vibrator and a receiving ultrasonic vibrator that oscillate highly directional ultrasonic waves. Using the sensor, the ultrasonic wave reflected from the radial artery 100 may be received by the receiving ultrasonic transducer, and the change in the amplitude of the received ultrasonic wave with respect to the transmitted ultrasonic wave may be detected.

<3. Third embodiment>
FIG. 15 shows a third embodiment according to the present invention. In this embodiment, the wristbands 121a and 121b of the wristwatch 120 are used as a support. The wristbands 121a and 121b are attached to both ends of the clock side 120a, respectively, are wrapped around the wrist of the subject, and are fastened to each other by a known hook 122. The hook 122 allows the circumference of the wristwatch 120 to be adjusted, that is, the tightening force on the wrist can be adjusted.

An optical pulsation detection sensor 113 is fixed to the back surface (the surface facing the wrist) of the wristband 121a. Instead, a pressure detection sensor may be used. The optical pulsation detection sensor 113 or the pressure detection sensor receives the tightening force of the wristbands 121a and 121b and presses the epidermis just above the radial artery 100.
Pressing legs 68, 72 projecting to the back side are attached to the wristband 121, and at least one of the pressing legs 68, 72 is movable along the circumferential direction of the wristband 121a and stops at the moved position. It has been made possible. Means for moving the pressing legs 68 and 72 can be provided using screws or hooks, although not shown.
The optical pulsation detection sensor 113 or the pressure detection sensor is located on the side opposite to the direction in which these tips are directed, rather than the tips of the pressing legs 68, 72. Thus, the blood vessel enters between the pressing legs 68, 72, and the sensor is easily positioned directly above the blood vessel. In this embodiment, the weight of the detection device can be significantly reduced.

<4. Fourth embodiment>
FIG. 16 shows a fourth embodiment. In this embodiment, a collar 130 made of an elastic body and curved in an arc shape is used as a support. This collar 130 is placed inside the collar 131 of the garment and wrapped around the subject's neck. In addition, the circumference of the collar 130 is adjustable, so that the tightening force on the neck is adjusted.
An optical pulsation detection sensor 113 or a pressure detection sensor is fixed to the back surface (inner surface) of the collar 130, and the optical pulsation detection sensor 113 or the pressure detection sensor presses the epidermis just above the carotid artery. Pressing legs 68, 72 projecting to the rear side are attached to the collar 130, and at least one of the pressing legs 68, 72 can move along the circumferential direction of the collar 130 and can stop at the moved position. Has been done.
The optical pulsation detection sensor 113 or the pressure detection sensor is located on the side opposite to the direction in which these tips are directed, rather than the tips of the pressing legs 68, 72. Thus, the blood vessel enters between the pressing legs 68, 72, and the sensor is easily positioned directly above the blood vessel.

<5. Fifth Embodiment>
<5-1. Configuration of Pulse Wave Detection Device of Fifth Embodiment>
First, FIG. 23 is a perspective view showing a pulse wave detection device 201 according to the fifth embodiment of the present invention, and FIG. 24 is a side view of the pulse wave detection device 201. As shown in FIG. 23 and FIG. 24, the pulse wave detection device 201 includes a holder 202 mounted on the arm of the subject, two support members 203 having both ends fixed to the holder 202, A left and right sliding member 204 disposed above the body 203, an up and down sliding member 205 provided to be vertically movable with respect to the left and right sliding member 204, and a strain gauge ( (Detection means) 206.

FIG. 25 is a view taken along line XXV-XXV in FIG. As shown in FIGS. 23, 24 and 25, when the holder 202 is mounted, the holder 202 has a bottom plate portion 202 a having a concave upper surface, a cushion portion 202 b disposed on the bottom plate portion 202 a, and the holder 202. A finger insertion portion 202c into which the second to fifth fingers of the subject are inserted, and a band portion 202d that is loosely wound around the arm. With this configuration, when the subject wears the holder 202, the subject's arm is not tightened, and the epidermis on the radial artery to be detected is directed substantially upward.

ゴ ム Besides the above-mentioned holding tool 202, a loosely-tightened rubber band 212 as shown in FIG. 26 or a holding tool 222 as shown in FIG. 27 can also be used. The holding tool 222 has a cushion member 224 provided on the inner surface of a U-shaped holding member 223. The arm of the subject is put in the U-shaped cushion member 224, and the arm is fixed by the holding band 225. It is supposed to. Further, the holding tool is not limited to these, and any tool may be used as long as the arm of the subject is not tightly tightened and the epidermis on the radial artery faces substantially upward.

As shown in FIG. 25, the support 203 includes a leg 2031 attached to the bottom plate 202a of the holder 202 with an adhesive, and a support 2032 whose both ends are supported by each leg 2031. Have been. However, the method of attaching the leg 2031 to the holder 202 is not limited to a method using an adhesive, and may be any method that can fix the leg 2031 to the holder 202. As shown in FIG. 28, a projection 2032a projecting in the left-right direction in the figure is formed on an upper portion of the support portion 2032, and a zigzag uneven portion 2033 is formed on the upper surface of the projection 2032a and the support portion 2032. Have been.

凹 As shown in FIG. 24, concave grooves 2040 that open downward are formed on both left and right ends of the lower surface of the left and right sliding member 204, respectively. At the left and right side edges of the concave groove 2040 in FIG. In addition, a zigzag uneven portion 2041 that meshes with the uneven portion 2033 formed on the support 203 is formed on the bottom surface of the concave groove 2040. The support portion 2032 of the support 203 is fitted into the concave groove 2040 of the left and right slide member 204 so that the left and right slide member 204 can slide in the left and right direction (perpendicular to the paper surface) with respect to the support 203. In addition, the movement of the left and right sliding member 204 in the vertical direction is restricted. Further, as shown in FIGS. 24 and 25, a through hole 2042 penetrating in the vertical direction is formed in the left and right sliding member 204. Further, zigzag-shaped uneven portions 2043 are formed on the left and right inner surfaces of the through hole 2042 in FIG.

ジ As shown in FIG. 24, zigzag uneven portions 2051 meshing with the uneven portions 2043 formed on the inner surface of the through hole 2042 are formed on the left and right side surfaces of the vertical sliding member 205. A vertical sliding member 205 is fitted into the through hole 2042 so that the concave and convex portions 2051 and the concave and convex portions 2043 mesh with each other, and the vertical sliding member 205 is slidable up and down with respect to the left and right sliding member 204. ing. Further, protrusions (hook portions) 2052 to which fingers can be hooked are respectively provided on the left and right side surfaces in FIG.

The strain gauge 206 utilizes a piezoresistive effect in which the resistance value changes when a strain is applied to a metal or semiconductor resistor. The strain gauge 206 can contact the epidermis just above the radial artery 100 of the human arm shown in FIG. 25 by the sliding of the sliding member described above, and a pulse wave accompanying the pulsation of the radial artery 100 is generated by the strain gauge 206. It is transmitted to 206. Therefore, the pulse wave can be measured by measuring the resistance value of the strain gauge 206. However, in addition to the strain gauge 206, a sensor capable of measuring a change in strain due to pulsation by converting strain into an electric signal represented by electric energy, electric resistance or capacitance, for example, a pressure sensor made of a piezoelectric element Etc. can also be used. FIG. 25 shows a cross section of a human arm. In particular, the radial artery 100, the radius 101, the ulna 102, the brachioradialis tendon 103, and the radial carpal flexor tendon 104 are clearly shown.

The signal detected by the strain gauge of the pulse wave detecting device 201 is input to the A / D converter 502 shown in FIG. 29, and is converted into a digital signal every predetermined sampling rate cycle. The microcomputer 503 fetches the converted digital signal into the A / D converter 502 and outputs a pulse wave waveform to the monitor 504. Thus, the waveform of the pulse wave detected by the pulse wave detection device 201 can be visually obtained.

<5-2. Method of Using Pulse Wave Detector of Fifth Embodiment>
Next, a method of using the pulse wave detection device 201 according to the above embodiment will be described. Here, as an example, a case will be described in which a pulse wave of the radial artery of a human is detected. However, the detection target is not limited to a human and can be used for other animals.
First, as shown in FIG. 23, the pulse wave detecting device 201 is mounted on the forearm of the subject. Then, the measurer adjusts the position by sliding the left and right sliding member 204 left and right with respect to the support body 203 so that the strain gauge 206 is almost directly above the radial artery. At this time, since the uneven portion 2033 formed on the support 203 and the uneven portion 2041 formed on the left and right sliding member 204 are engaged with each other, there is some resistance in sliding, but a little force is applied in advance. If the concave and convex portions 2033 and 2041 are formed in a shape that can be moved by pushing with a finger, the position adjustment operation is easy.

The measurer adjusts the position of the left and right sliding member 204 by an operation such as pressing with a finger or pinching with a plurality of fingers, and then slides the upper and lower sliding member 205 downward to apply an appropriate pressing force to the radial artery. The strain gauge 206 is moved to the position. At this time, the uneven portion 2043 and the uneven portion 2051 are formed so that the vertical sliding member 205 does not move with respect to the left and right sliding member 204 even when receiving a force due to pulsation when detecting a pulse wave. Specifically, although there is an individual difference in the force due to the pulsation, it is preferable to form the uneven portion 2043 and the uneven portion 2051 so as to slide when receiving a force of about 300 g or more. With this level of resistance, the vertical sliding member 205 can be easily moved down. Therefore, as shown in FIG. 30, the measurer can adjust the strain gauge 206 to an appropriate height with one hand and with a simple operation. In addition, the measurer can easily pull up the vertical sliding member 205 upward by hooking two fingers on the protrusion 2052. Such a strain gauge 206 is positioned while relying on the visual sense of the measurer, and by actually performing measurement at a plurality of locations, a waveform having the largest amplitude is obtained from the pulse waveform output to the monitor 504 shown in FIG. The strain gauge 206 is moved to the position where is obtained.

位置 決 め The positioning of the strain gauge 206 to the optimum measurement position is thus performed, and the measurement of the pulse wave is started. At this time, the concave and convex portions 2043 and 2051 formed on the left and right sliding member 204 and the vertical sliding member 205, and the concave and convex portions 2033 and 2041 formed on the support 203 and the left and right sliding member 204 mesh with each other. Therefore, the position of the strain gauge 206 does not change even if a force of about pulsation is received. Therefore, it is possible to maintain a state in which an appropriate pressing force is applied to the radial artery, which has been difficult when performing measurement with a conventional pen-shaped sensor or the like, and to obtain a more accurate measurement result. In addition, since the pulse wave detection device 201 has a structure in which the position is adjusted by a manual operation of a measurer, a driving device or the like is not required and the configuration is simple.

<5-3. Modification of Fifth Embodiment>
Next, a modification of the above embodiment will be described with reference to FIG. In FIG. 31, the same components as those in the fifth embodiment are denoted by the same reference numerals, and description thereof will be omitted.
As shown in FIG. 31, in this pulse wave detection device, a support 207 is attached to a holder 202. The support 207 includes four legs 2071 attached to the holder 202, and a support 2072 whose ends are supported by the legs 2071. A through hole 2073 is formed in the support portion 2072 in the vertical direction. On the left and right inner surfaces of the through hole 2073 in the drawing, an uneven portion 2074 having a shape meshing with the uneven portion 2051 formed on the vertical sliding member 205 is formed. The vertical sliding member 205 is slidably fitted in the through-hole 2073 so that the uneven portion 2074 and the uneven portion 2051 mesh with each other.
According to this configuration, the position of the strain gauge 206 can be adjusted up and down. The adjustment method at this time can be performed by a simple operation as in the fifth embodiment. Further, when the measurement is started, the position of the strain gauge 206 does not change with the force of the pulsation, and an accurate measurement result can be obtained as in the fifth embodiment.

Next, another modified example of the above embodiment will be described with reference to FIG. In FIG. 32, the same components as those in the fifth embodiment are denoted by the same reference numerals, and description thereof will be omitted. As shown in FIG. 32, this pulse wave detection device includes a holder 202, a support 208, a vertical sliding member 209, a left and right sliding member 210, and a strain gauge 206.
Two supports 208 are attached to the holder 202. Concavo-convex portions 2081 are formed on opposing side surfaces of the support 208. At the left and right ends of the vertical sliding member 209 in the drawing, an uneven portion 2091 having a shape meshing with the uneven portion 2081 is formed. The vertical sliding member 209 is sandwiched between the two supports 208 so as to be slidable up and down. Further, on the upper surface of the upper and lower sliding member 209, concave and convex portions 2092 are formed at both left and right ends. The vertical sliding member 209 has a through hole 2093 penetrating in the vertical direction. A string (hook) 2104 formed in a loop shape is attached to the upper and lower sliding members 209. The measurer can hook his / her finger on the string 2104 and slide the vertical sliding member 209 upward.

At the left and right ends of the lower surface of the left and right sliding member 210, concave grooves 2101 that are opened downward respectively are formed, and the bottom surface of the concave groove 2101 is shaped to engage with the uneven portion 2092 formed on the vertical sliding member 209. Are formed. The concave / convex portion 2092 of the vertical sliding member 209 is fitted into the concave groove 2101 of the horizontal sliding member 210, so that the horizontal sliding member 210 slides in the horizontal direction (perpendicular to the paper plane) with respect to the vertical sliding member 209. In addition, the movement of the left and right sliding member 210 in the vertical direction is restricted.
A protrusion 2103 is provided on the lower surface of the left and right sliding member 210 so as to protrude downward, and the protrusion 2103 is inserted into a through hole 2093 formed in the upper and lower sliding member 209. Further, a strain gauge 206 is attached to the lower end of the protrusion 2103.
According to this configuration, it is possible to adjust the position of the strain gauge 206 up, down, left, and right as in the fifth embodiment. Further, when the measurement is started, the position of the strain gauge 206 does not change with the force of the pulsation, and an accurate measurement result can be obtained as in the fifth embodiment.

As a further modification of the fifth embodiment, an insertion hole 2053 into which the finger of the measurer is inserted may be formed in the vertical sliding member 205 as shown in FIG. According to this configuration, the measurer can lower the vertical sliding member 205 by inserting a finger into the insertion hole 2053 and pressing it down, so that the position adjustment of the strain gauge 206 is easy. Further, it is also possible for the measurer to insert a finger into the insertion hole 2053 and to lift the vertical sliding member 205 with the inserted finger and another finger. Further, a similar insertion hole may be provided in the pulse wave detector shown in FIGS. 31 and 32.

<6. Sixth embodiment>
<6-1. Configuration of Pulse Wave Detection Device of Sixth Embodiment>
Next, a pulse wave detection device according to a sixth embodiment, which is more preferable than the fifth embodiment, will be described with reference to FIGS. 34 and 35, the same components as those in the fifth embodiment are denoted by the same reference numerals, and description thereof will be omitted.
In the pulse wave detection device 2200 shown in FIG. 34, left and right sliding members 2201 are arranged on the upper surfaces of the two supports 2203 so as to be slidable in the left and right (perpendicular to the paper). Concavo-convex portions 2202 are formed on the mutually facing side surfaces of the two left and right sliding members 2201, respectively. An upper and lower sliding member 2203 is sandwiched between the two left and right sliding members 2201 so as to be vertically slidable. On the left and right side surfaces in the drawing of the vertical sliding member 2203, an uneven portion 2204 meshing with the uneven portion 2202 is formed.

貫通 A through-hole 2205 is formed in the up-down sliding member 2203 so as to penetrate in the up-down direction, and the finger insertion member 2206 is rotatably fitted into the through-hole 2205. Here, a peripheral groove 2207 is formed on the inner peripheral surface of the through hole 2205, and a ridge 2208 that fits into the peripheral groove 2207 is formed on the outer peripheral surface of the finger insertion member 2206. The movement of the finger insertion member 2206 in the vertical direction is restricted. Also, an L-shaped hooking member 2252 capable of hooking a finger is attached to the vertical sliding member 2203.

As shown in FIG. 35, the finger insertion member 2206 is bent at about 45 ° with respect to a vertical line to a tangent plane of the epidermis. An insertion hole 2210 is formed in the finger insertion member 2206, and the finger of the measurer is inserted into the insertion hole 2210. An elastic film 2211 is provided in an opening 2235 of the insertion hole 2210 at the lower end of the finger insertion member 2206. Further, a groove 2212 is formed in the elastic film 2211, and when measuring a pulse wave, the soft epidermis on both sides of the radial artery is dented, so that the epidermis on the radial artery easily fits into the groove 2212. ing.
Here, FIG. 36 is a view of the finger insertion member 2206 shown in FIG. 35 as viewed along the line XXXVI-XXXVI. As shown in the figure, a strain gauge 206 is attached to the lower surface of the finger insertion member 2206, which is the periphery of the opening 2235, so as to be on the same line as the groove 2212 formed in the elastic film 2211. Since the position of the strain gauge 206 is collinear with the groove 2212 of the elastic film 2211, the strain gauge 206 is positioned on the radial artery 100 when the epidermis on the radial artery 100 fits into the groove 2212. I have.

<6-2. Method of Using Pulse Wave Detector of Sixth Embodiment>
Next, a method of using the pulse wave detection device 2200 according to the sixth embodiment will be described. Here, as an example, a case will be described in which a pulse wave of the radial artery of a human is detected. However, the detection target is not limited to a human and can be used for other animals.
First, as shown in FIGS. 34 and 35, the pulse wave detection device 2200 is mounted on the forearm of the subject. Next, the measurer inserts a finger into insertion hole 2210. Then, similarly to the fifth embodiment, the left and right sliding members 2201 are slid, and the position is adjusted so that the strain gauge 206 is almost directly above the radial artery 100.
After adjusting the position of the left and right sliding members 2201, while the finger is being inserted into the insertion hole 2210, the upper and lower sliding members 2203 are slid downward, and the strain gauge 206 is placed at a position where an appropriate pressing force is applied to the radial artery. Move. At this time, the measurer can search for the position of the strain gauge 206 for applying an appropriate pressing force to the radial artery via the elastic film 2211 with the finger. That is, the strain gauge 206 can be arranged at an appropriate position using the tactile sense of the measurer. Therefore, it is possible to accurately and easily arrange the strain gauge 206 at an appropriate position as compared with the positioning based on the visual sense of the measurer as in the fifth embodiment.
In addition, since the insertion hole 2210 is formed to be inclined by about 45 °, when a finger is inserted into the insertion hole 2210, the manner in which the finger is tilted, indirectly bent, and the state of contact of the finger with the epidermis are normal. The state becomes the same as the pulse diagnosis, and the position of the strain gauge 206 can be adjusted more accurately. In addition, as shown in FIG. 37, the measurer can lift the second finger and the fourth finger by hooking the second finger and the fourth finger on the hook member 2252 in a state where the third finger is inserted into the insertion hole 2210. . Therefore, the position can be adjusted while searching for an appropriate position of the strain gauge 206 with a finger.

The positioning of the strain gauge 206 is performed in this manner, and measurement of a pulse wave is started. At this time, the concave and convex portions 2202 and 2204 formed on the left and right sliding member 2201 and the vertical sliding member 2203 respectively, and the concave and convex portions 2033 and 2041 formed on the support 2203 and the left and right sliding member 2201 respectively. Due to the meshing, the position of the strain gauge 206 does not change even if a force of about pulsation is received. Further, the finger insertion member 2206 can be rotated to facilitate the groove 2212 to fit into the epidermis above the radial artery of the subject. At this time, if the direction of the insertion hole 2210 is adjusted to a position where a finger can be inserted from a direction perpendicular to the subject's arm when viewed from above (the state shown in FIG. 35), the groove 2212 is formed in substantially the same direction as the radial artery It has become. That is, when the measurer inserts his / her finger from a direction in which the position of the pulse can be easily detected, the epidermis on the radial artery easily fits in the groove 2212.
In this manner, the radial artery 100 is fixed in the groove 2212, and the lateral displacement of the strain gauge 206 is prevented, and the adjustment of the pressing force applied to the blood vessel is facilitated. As a result, a state where an appropriate pressing force is applied to the radial artery can be maintained, and a pulse wave waveform is output from the signal detected by the strain gauge 206 to the monitor 504 shown in FIG. The result can be obtained. Furthermore, since the finger insertion member 2206 is rotatably fitted into the through hole 2205, the measurer rotates the finger insertion member 2206 by 180 ° so that the measurer can use the natural finger of both the left and right arms of the subject. You can touch it by placing it.

<7. Seventh embodiment>
<7-1. Configuration of Pulse Wave Detector of Seventh Embodiment>
Next, a pulse wave detection device according to a seventh embodiment of the present invention will be described with reference to FIGS. 38 and 39, the same components as those in the fifth embodiment and the sixth embodiment are denoted by the same reference numerals, and description thereof will be omitted.
As shown in FIGS. 38 and 39, in the pulse wave detecting device 2300, a screw hole 2301 penetrating vertically is formed in the left and right sliding member 204. A hollow bolt 2305 is screwed into the screw hole 2301. A finger insertion member 2302 is rotatably fitted in the internal space of the hollow bolt 2305. Here, the protrusion 2307 formed on the outer peripheral surface of the finger insertion member 2302 is fitted into the circumferential groove 2306 formed on the inner peripheral surface of the hollow bolt 2305, so that the finger insertion member 2302 is Movement is regulated.
As shown in FIG. 39, an insertion hole 2310 inclined at about 45 ° is formed in the finger insertion member 2302, and a finger of a measurer is inserted into the insertion hole 2310. An elastic film 2211 is provided in an opening 2235 of the insertion hole 2310 at the lower end of the finger insertion member 2302. A groove 2212 is formed in the elastic film 2211, and when measuring a pulse wave, the soft epidermis on both sides of the radial artery 100 is dented, so that the epidermis on the radial artery 100 easily fits into the groove 2212. ing. Further, a strain gauge 206 is attached to the lower surface of the finger insertion member 2302 as in the sixth embodiment (see FIG. 36).

<7-2. Method of Using Pulse Wave Detection Method of Seventh Embodiment>
Next, a method of using the pulse wave detection device 2300 according to the seventh embodiment will be described. Here, as an example, a case will be described in which a pulse wave of the radial artery of a human is detected. However, the detection target is not limited to a human and can be used for other animals.
First, as shown in FIG. 38, the pulse wave detection device 2300 is attached to the subject's forearm. Then, as in the fifth embodiment, the left and right sliding members 204 are slid left and right, and the position is adjusted so that the strain gauge 206 is almost directly above the radial artery 100.

After adjusting the position of the left and right sliding member 204, the finger insertion member 2302 is moved downward by rotating the hollow bolt 2305 while the finger is inserted in the insertion hole 2310, and an appropriate pressing force is applied to the radial artery 100. The strain gauge 206 is moved to the position to be given. At this time, the position of the strain gauge 206 for applying an appropriate pressing force to the radial artery 100 can be searched by the finger via the elastic film 2211. That is, the strain gauge 206 can be arranged at an appropriate position using the tactile sense of the measurer. Therefore, as in the sixth embodiment, the strain gauge 206 can be accurately and easily positioned as compared with the fifth embodiment. At this time, with the third finger inserted into the insertion hole 2310, an operation of rotating the hollow bolt 2305 with another finger to move it up and down is possible. Therefore, the position can be adjusted while searching for an appropriate position of the strain gauge 206 with a finger.

位置 決 め The positioning of the strain gauge 206 is thus performed, and the measurement of the pulse wave is started. At this time, since the finger insertion member hollow bolt 2305 is screwed into the screw hole 2301 of the left and right sliding member 204, the position of the strain gauge 206 does not change even if it receives a pulsating force. Further, the finger insertion member 2302 can be rotated so that the groove 2212 fits into the epidermis on the radial artery of the subject as in the sixth embodiment. Thereby, the radial artery 100 is fixed in the groove 2212, the lateral displacement of the strain gauge 206 is prevented, and the adjustment of the pressing force applied to the blood vessel is facilitated. As a result, a state in which an appropriate pressing force is applied to the radial artery 100 can be maintained, and a pulse wave waveform is output from the signal detected by the strain gauge 206 to the monitor 504 shown in FIG. Measurement results can be obtained. Furthermore, since the finger insertion member 2302 is rotatably fitted into the hollow bolt 2305, the measurer rotates the finger insertion member 2302 by 180 ° so that the measurer can use a natural finger on both the left and right arms of the subject. You can touch it by placing it.

<8. Modification>
FIG. 40 shows a modification of the finger insertion member applicable to the sixth and seventh embodiments. As shown in FIG. 40, on the lower surface of the finger insertion member 2206 or 2302, a plurality of strain gauges 2150 are juxtaposed in the left-right direction on the periphery of the opening 2235. The center one of the strain gauges 2150 is on the same line as the groove 2212 of the elastic film 2211.
In this configuration, since the positional relationship between each of the strain gauges 2150 and the blood vessel is determined almost univocally in advance at the time of positioning, the pulse wave obtained from each strain gauge 2150 is analyzed to determine the stroke of the blood vessel. It is possible to measure the accompanying change in the thickness direction of the blood vessel and the like.

FIG. 41 shows another modification of the finger insertion member applicable to the sixth and seventh embodiments. As shown in FIG. 41, in the finger insertion member 2206 or 2302, strain gauges 206 are disposed at two positions with the elastic film 2211 interposed therebetween. In other words, the strain gauges 206 are provided at two positions in the blood vessel extending direction (vertical direction in the figure) at the time of measurement, and thus two pulse waveforms having a time difference can be obtained. . However, the number of strain gauges 206 to be attached is not limited to two, and a plurality (three or more) may be provided along the radial artery. Further, it is also possible to combine with the above-described first modification, that is, a plurality of strain gauges 2150 (see FIG. 40) may be arranged in parallel at two positions sandwiching the elastic film 2211.

FIG. 42 shows still another modification of the finger insertion member applicable to the sixth and seventh embodiments. As shown in FIG. 42, in this finger insertion member 2206 or 2302, a ring-shaped strain gauge 206 surrounding the elastic film 2211 is attached to the periphery of the opening 2235. According to this configuration, if the measurer detects the radial artery with the finger via the elastic membrane 2211, the ring-shaped strain gauge 206 is always in close contact with the epidermis on the radial artery, so that the direction of the finger insertion member 2206 or 2302 Regardless of this, the strain gauge 206 can be brought into close contact with the epidermis above the radial artery. That is, it is not necessary to position the strain gauge 206 on the radial artery using the groove 2212.

As still another modification of the finger insertion member applicable to the sixth and seventh embodiments, a finger insertion member 2206 or 2302 shown in FIG. 43 may be employed. As shown in FIG. 43, in this modification, the elastic film 2211 is not provided in the opening 2235 below the insertion hole 2210 or 2310. That is, the insertion hole 2210 or 2310 penetrates in the up-down direction, and the fingertip of the measurer can be put out from the opening 2235. According to this configuration, as shown in FIG. 44, it is possible to adjust the strain gauge 206 to an appropriate position by directly touching the epidermis on the radial artery with a finger, thereby obtaining a more accurate measurement result. Can be.
The insertion holes 2210 and 2310 are not limited to the shapes described above, and may be any shape that allows the detection target to be detected by the inserted finger. For example, the insertion holes 2210 and 2310 may have a shape that allows a plurality of fingers to be inserted. Further, a plurality of finger insertion members 2206 or 2302 may be provided along the shape of the radial artery of the subject.

As a modified example of the holder 202 applicable to the fifth to seventh embodiments, as shown in FIG. 45, the support portion 2032 of the support 203 of the holder 202 is not linear, but the right and left ends are curved. May be provided. Alternatively, as shown in FIG. 46, instead of the support portion 2032, a support portion 2032c that curves with the convex portion on the upper side may be provided.
According to the configuration shown in FIGS. 45 and 46, the position of strain gauge 206 can be moved along the skin of the arm. Therefore, regardless of where the strain gauge 206 is moved, the strain gauge 206 can be pressed from a direction substantially perpendicular to the tangent plane of the epidermis on the radial artery, and more accurate measurement can be performed. .

Furthermore, the biological condition measuring device disclosed in International Publication No. WO97 / 16114 for measuring the condition on the central side from the pulse wave on the peripheral side of the living body is described in any of the fifth to seventh embodiments described above. It is also possible to use a pulse wave detection device. According to this biological condition measuring device, a more accurate peripheral-side pulse wave waveform can be obtained by the pulse wave detecting device according to the fifth to seventh embodiments, so that a more accurate central-side state can be measured. It is possible to do.

In any of the above embodiments, the blood vessel to be measured is the radial artery of a human arm, but the present invention is not limited to this. It is also possible to detect a pulse wave. FIG. 17 shows human arteries and veins. According to the present invention, it is possible to detect pulse waves of various arteries shown here. It is also possible to detect pulse waves of animals other than humans.
Furthermore, not only blood vessels of a living body but also other articles that cause pulsation can be measured.
Further, the pressure detecting device 80 of the first embodiment can be used for purposes other than detecting the pulsation of the measurement object.

It is a perspective view showing the pulse wave detecting device concerning a 1st embodiment. (A) is a front view which shows the pulse-wave detection unit provided in the said pulse-wave detection apparatus, (B) is the left view. FIG. 3 is a rear view showing the pulse wave detection unit shown in FIG. FIG. 3 is a perspective view showing the pulse wave detection unit shown in FIG. FIG. 3 is a perspective view of the pulse wave detection unit shown in FIG. 2A as viewed from below. 2A is a front view showing a pressure detection device used in the pulse wave detection unit shown in FIG. 2A, FIG. 2B is a left side view thereof, and FIG. 2C is a bottom view thereof. It is. FIG. 3 is a front view showing a state in which a pressing leg portion, which is a blood vessel peripheral pressing portion, of the pulse wave detection unit shown in FIG. 2A is lightly brought into contact with a subject's arm. FIG. 3 is a front view showing a state in which a force is applied to a contact part, which is a blood vessel pressing part, of the pulse wave detection unit shown in FIG. 3 is a graph showing a relationship between a downward displacement of a pressing leg of the pulse wave detection unit shown in FIG. 2A and a tension on a subject's arm. It is a front view showing the principal part of the pulse wave detector concerning a 2nd embodiment of the present invention. (A) is a diagram showing the relationship between the amount of incident light and the amount of transmitted light according to Lambert-Beer's law when the minute optical path length is ΔL, and (B) is a diagram showing Lambert-Beer's law when the minute optical path length is 5ΔL. FIG. 4 is a diagram showing a relationship between an incident light amount and a transmitted light amount according to FIG. It is a graph which shows an example of a temporal change of the absorbance at the time of irradiating light to the blood vessel part of a person from the outside. It is a graph which shows an example of distribution of the blood pressure in each part of a human body. It is a front view showing the principal part of the pulse wave detector concerning a modification of a 2nd embodiment of the present invention. It is a side view showing the composition of a 3rd embodiment concerning the present invention. It is a front view showing composition of a 4th embodiment concerning the present invention. 1 is a human body diagram showing arteries and veins. FIG. 3 is a circuit diagram showing an output circuit of a pressure sensor in each pulse wave detection unit of the first embodiment shown in FIG. 2 (A). 19 is a graph showing a pulse wave detected by the pressure sensor shown in FIG. It is sectional drawing of the said pressure detection apparatus seen along the XX-XX line of FIG. 6 (A). FIG. 7 is a graph showing a change in an electromechanical coupling coefficient of the pressure detection device with respect to a relative thickness of a thin portion of a beam in the pressure detection device shown in FIG. It is a change curve (trend curve) of the pulse width according to the change of the pressing force on the human skin, where (A) shows a flat pulse, (B) shows a floating pulse, and (C) shows a sink pulse. It is a perspective view showing a pulse wave detecting device concerning a 5th embodiment of the present invention. It is a side view of the said pulse-wave detection apparatus shown in FIG. FIG. 25 is a front view as viewed along the line XXV-XXV in FIG. 24. It is a perspective view showing the modification of the holder of the above-mentioned pulse wave detecting device concerning a 5th embodiment. It is a perspective view showing other modifications of the holder of the above-mentioned pulse wave detecting device concerning a 5th embodiment. It is an enlarged side view which shows the fitting part of the support of the said pulse wave detection apparatus which concerns on 5th Embodiment, and a left-right sliding member. It is a block diagram showing composition of a device which outputs a pulse wave waveform from a signal detected by the above-mentioned pulse wave detecting device concerning a 5th embodiment to a monitor. It is a figure showing signs that measurement is performed using the above-mentioned pulse wave detecting device. It is a side view which shows the pulse-wave detection apparatus of the modification of 5th Embodiment. It is a side view which shows the pulse-wave detection apparatus of other modification of 5th Embodiment. It is a side view which shows the pulse-wave detection apparatus of another modification of 5th Embodiment. It is a side view showing the pulse wave detector concerning a 6th embodiment of the present invention. FIG. 35 is a front view as viewed along the line XXXV-XXXV in FIG. 34. FIG. 36 is a bottom view as viewed along the line XXXVI-XXXVI of FIG. 35. FIG. 35 is a side view showing a state where a measurer is adjusting the position of the pulse wave detection device shown in FIG. 34. It is a side view showing the pulse wave detector concerning a 7th embodiment of the present invention. FIG. 39 is a front view as viewed along the line XXXIX-XXXIX of FIG. 38. It is a bottom view showing a modification of a finger insertion member applicable to a 6th and a 7th embodiment. It is a bottom view showing other modifications of a finger insertion member applicable to a 6th and a 7th embodiment. It is a bottom view which shows the other modification of the finger insertion member applicable to 6th and 7th embodiment. It is a bottom view which shows the other modification of the finger insertion member applicable to 6th and 7th embodiment. FIG. 44 is a front view showing a manner in which a measurer searches for a detected position using the finger insertion member shown in FIG. 43. It is a front view which shows the modification of the holder which can be applied to the pulse-wave detection apparatus which concerns on 5th-7th embodiment. It is a front view showing other modifications of a holder which can be applied to a pulse wave detecting device concerning a 5th-a 7th embodiment.

Explanation of reference numerals

DESCRIPTION OF SYMBOLS 1 ... Pulse wave detection apparatus, 2 ... Stand, 3 ... Pulse wave detection unit, 5 ... Arm support, 10 ... Support, 28 ... Micrometer head, 68/72 ... Press leg, 81 ... Beam, 82 ... Piezoelectric element

Claims (2)

One beam body whose base end is supported by the support,
A detection target portion pressing portion provided on the beam body and pressed against a surface on the detection target portion,
A piezoelectric element mounted on the beam body, and a piezoelectric element that outputs an electric signal corresponding to a change in pressure applied through the detection target unit pressing unit,
In the beam, a thin portion thinner than other portions is formed between the base end portion and the detection target portion pressing portion,
The piezoelectric element is longer than the thin portion, and is mounted on the entire thin portion in the longitudinal direction of the beam, and on the base end side or the detection target portion pressing portion side of the thin portion. Pressure detection device characterized by being performed. One beam body whose base end is supported by the support,
A detection target portion pressing portion provided on the beam body and pressed against a surface on the detection target portion,
A piezoelectric element mounted on the beam body, and a piezoelectric element that outputs an electric signal corresponding to a change in pressure applied through the detection target unit pressing unit,
A pressure detecting device, wherein a ratio of a cross-sectional area of the beam to a total cross-sectional area of the beam and the piezoelectric element at a position where the piezoelectric element is mounted is 60% or less.

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