JP2014180287A - Biological information detector - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a biological information detector and the like which can detect proper biological information when a contact condition of a contact surface with a subject changes or the like.SOLUTION: A biological information detector includes: a detecting part which has a light receiving part 140 for receiving light from a subject; a translucent member 30 which is provided at a case surface side that comes in contact with the subject of the biological information detector, transmits light from the subject, and comes in contact with the subject when measuring biological information of the subject; and diaphragm parts 80 and 82 which are provided between the translucent member 30 and the detecting part, between the translucent member 30 and the subject, or in the translucent member 30, and narrow the light from the subject in an optical path between the subject and the detecting part.

Description

  The present invention relates to a biological information detection device and the like.

  2. Description of the Related Art Conventionally, a biological information detection apparatus that detects biological information such as a human pulse wave is known. Patent Documents 1 and 2 disclose conventional techniques of a pulse meter which is an example of such a biological information detection apparatus. The pulse meter is attached to, for example, an arm, a wrist, a finger, or the like, and detects a pulsation derived from a heartbeat of a human body to measure a pulse rate.

  The pulsometers disclosed in Patent Documents 1 and 2 are photoelectric pulsometers, and the detection unit (pulse wave sensor) includes a light emitting unit that emits light toward a subject (detection site), and a target. A light receiving unit that receives light from the specimen (light having biological information) is included. In this pulse meter, a pulse wave is detected by detecting a change in blood flow as a change in the amount of received light. Patent Document 1 discloses a pulse meter that is worn on the wrist, and Patent Document 2 discloses a pulse meter that is worn on a finger.

JP2011-139725A JP 2009-201919 A

  In these conventional techniques, a translucent member that transmits light from the light emitting unit and light from the subject is provided, and this translucent member has a contact surface with the subject (such as the wrist or finger skin). ing. Then, due to the change in the contact state of the contact surface with the subject or the like, the signal quality of the detection signal of the biological information is reduced, and the reliability and detection accuracy of the biological information is reduced.

  According to some aspects of the present invention, it is possible to provide a biological information detection apparatus and the like that can detect appropriate biological information even when there is a change in the contact state of the contact surface with the subject.

  One embodiment of the present invention is provided on a body surface side of a biological information detection device that contacts a subject, and having a light receiving unit that receives light from the subject, and transmits light from the subject. And a translucent member that contacts the subject at the time of measuring biological information of the subject, and between the translucent member and the detection unit, between the translucent member and the subject, or in the translucent member And a biological information detection apparatus including a diaphragm unit that squeezes light from the subject in an optical path between the subject and the detection unit.

  According to one aspect of the present invention, a light-transmitting member comes into contact with a subject at the time of measuring biological information of the subject, and the light-receiving unit of the detection unit receives light passing through the light-transmitting member. Biometric information is detected. In one aspect of the present invention, a diaphragm unit for narrowing the light from the subject is provided in the optical path between the subject and the detection unit. In this way, even when stray light is generated due to a change in the contact state of the contact surface with the subject, the stray light can be prevented from being incident on the light receiving unit. Biometric information can be detected.

  In one aspect of the present invention, the detection unit includes a light emitting unit that emits light to the subject, the translucent member transmits light from the light emitting unit, and the diaphragm unit includes the light emitting unit. In the optical path between the subject and the detection unit, the light from the light emitting unit may be narrowed down.

  In this way, it is possible to suppress a situation in which light from the light emitting unit becomes stray light and proper biological information cannot be detected.

  In one embodiment of the present invention, the diaphragm unit may include a first diaphragm unit provided on the light receiving unit side and a second diaphragm unit provided on the light emitting unit side.

  In this way, the stray light is prevented from being incident on the light receiving unit, for example, by the first diaphragm unit, or the light from the light emitting unit is prevented from becoming stray light, for example, by the second diaphragm unit. It becomes possible.

  In one embodiment of the present invention, the area of the opening of the second diaphragm provided on the light emitting unit side is larger than the area of the opening of the first diaphragm provided on the light receiving unit side. It may be smaller.

  In this way, the area of the opening of the first and second apertures can be set to an area suitable for improving optical efficiency and performance, improving product yield, and the like.

  In one embodiment of the present invention, the first end of the translucent region of the translucent member and the end of the translucent region farther from the first end of the two ends of the light receiving unit. The angle between the line connecting the second end portion and the optical axis of the light receiving portion is θr, and the second end portion of the light receiving portion and the end portion on the opening side of the aperture portion are When the angle formed between the connecting line and the optical axis is θa, θa <θr may be satisfied.

  If the relationship of θa <θr is established in this way, for example, light from the first end of the light transmitting region of the light transmitting member can be blocked by the diaphragm so that it does not enter the light receiving unit. Become.

  In one embodiment of the present invention, the first end of the translucent region of the translucent member and the end of the two portions of the light receiving unit that are closer to the first end of the translucent region. On the line connecting the first end portion and the second end portion of the translucent region of the translucent region of the translucent member and the second end portion of the translucent region of the two end portions of the light receiving portion. The aperture portion may be arranged and set so that the aperture portion is located on a line connecting the second end portion which is the near end portion.

  In this way, it becomes possible to ensure that stray light from the first and second end portions of the translucent member is blocked by the aperture portion.

  In one embodiment of the present invention, the second end of the translucent area of the translucent member and the end of the translucent area farther from the second end of the two ends of the light emitting section. The angle between the line connecting the first end portion and the optical axis of the light emitting portion is θt, and the first end portion of the light emitting portion and the end portion on the opening side of the aperture portion are If the angle between the connecting line and the optical axis is θb, θb <θt may be satisfied.

  If the relationship of θb <θt is established in this way, appropriate biological information can be detected, for example, by blocking the light traveling from the light emitting portion to the second end portion of the light transmitting region of the light transmitting member by the aperture portion. It becomes like this.

  In one embodiment of the present invention, the first end portion of the light-transmitting region of the light-transmitting member and the end portion on the side close to the first end portion of the light-transmitting region among the two end portions of the light-emitting portion. On the line connecting the first end portion, the second end portion of the light transmitting region of the light transmitting member, and the second end portion of the light transmitting portion of the two end portions of the light emitting portion. The aperture portion may be arranged and set so that the aperture portion is located on a line connecting the second end portion which is the near end portion.

  In this way, it is possible to ensure that the light traveling from the light emitting portion toward the first and second end portions of the light transmitting region of the light transmitting member is blocked by the aperture portion.

  In one embodiment of the present invention, the area of the aperture region of the aperture section may be smaller than the area of the light transmitting region of the light transmitting member.

  If it does in this way, it will become possible to block the light which passes the predetermined field of a translucent member by a diaphragm part.

  In the aspect of the invention, the diaphragm may block light that passes through a peripheral region of the translucent member.

  If it does in this way, the situation which becomes impossible for detection of proper living body information due to the light which passes through the peripheral field of a translucent member can be controlled.

  In one embodiment of the present invention, the translucent member has a convex portion that contacts and presses the subject when measuring biological information of the subject, and the diaphragm portion is a peripheral region of the convex portion. The light passing through may be shielded.

  In this way, when a convex portion for applying an appropriate pressure to the subject is provided on the translucent member, the appropriate biological information is caused by the light passing through the peripheral area of the convex portion. It is possible to suppress the situation where it becomes impossible to detect this.

  Moreover, in one mode of the present invention, it may include a press suppressing unit that is provided so as to surround the convex part and suppresses the press applied to the subject by the convex part.

  If it does in this way, the press which a convex part gives to a subject will be controlled by a press control part, and it will become possible to reduce pressure fluctuation.

  Moreover, in one aspect of the present invention, when the amount of change in pressing of the convex portion with respect to the load by the load mechanism that generates pressing of the convex portion is defined as the amount of pressing change, the pressing suppression portion is configured so that the load of the load mechanism is The convex change amount is reduced so that the pressure change amount in the second load range in which the load of the load mechanism is larger than FL1 is smaller than the pressure change amount in the first load range of 0 to FL1. You may suppress the press which a part gives to the said test object.

  In this way, it is possible to reduce the pressure fluctuation by suppressing the pressure applied to the subject by the convex portion by the press suppressing portion while applying an appropriate initial pressure to the subject by the convex portion.

  In the aspect of the invention, the diaphragm may be provided between the translucent member and the detection unit.

  However, the arrangement setting of the diaphragm portion is not limited to such an arrangement setting.

  In the aspect of the invention, the shape of the stop region of the stop portion may be similar to the shape of the light-transmitting region of the light-transmitting member.

  In one embodiment of the present invention, a pulse wave may be detected as the biological information.

  However, the biological information to be detected by the biological information detection device is not limited to the pulse wave.

FIG. 1A and FIG. 1B are external views of the biological information detection apparatus of this embodiment. FIG. 2A to FIG. 2C are explanatory diagrams of a connecting portion of the biological information detecting device. The perspective view of the back cover part of the main-body part of a biometric information detection apparatus. Sectional drawing of a back cover part. FIG. 5A and FIG. 5B are explanatory diagrams of problems when the pressure of the translucent member against the subject changes. 6A and 6B are explanatory diagrams of Hertz's elastic contact theory. FIG. 7A and FIG. 7B are explanatory diagrams of the method of this embodiment. FIG. 8A and FIG. 8B are diagrams illustrating an arrangement configuration example of a diaphragm portion and a light shielding portion. FIG. 9A to FIG. 9C are explanatory diagrams of a method for setting the hole diameter of the aperture region. FIG. 10A and FIG. 10B are explanatory diagrams of the arrangement setting method of the apertures. FIG. 11A and FIG. 11B are also explanatory diagrams of the arrangement setting method of the diaphragm portion. FIGS. 12A to 12C are diagrams showing various examples of arrangement positions of the apertures. The perspective view of the 1st example of the member for light shielding which formed the aperture part and the light-shielding part integrally. FIGS. 14A and 14B are a top view and a cross-sectional view of a first example of a light shielding member in which a diaphragm portion and a light shielding portion are integrally formed. The perspective view of the 2nd example of the member for light shielding which integrally formed the aperture | diaphragm | squeeze part and the light-shielding part. FIGS. 16A and 16B are a top view and a cross-sectional view of a second example of a light shielding member in which a diaphragm portion and a light shielding portion are integrally formed. FIG. 17A and FIG. 17B are explanatory views of a convex portion and a pressure suppressing portion of the light transmitting member. 18A and 18B are diagrams showing the relationship between Δh and the MN ratio. The functional block diagram which shows the example of the whole structure of a biometric information detection apparatus.

  Hereinafter, this embodiment will be described. In addition, this embodiment demonstrated below does not unduly limit the content of this invention described in the claim. In addition, all the configurations described in the present embodiment are not necessarily essential configuration requirements of the present invention.

1. Biological Information Detection Device FIG. 1A is an external view showing an example of a biological information detection device (biological information measurement device) of the present embodiment. This biological information detection device is a watch-type pulse meter, and has a main body 300 and bands 320 and 322 (wrist bands) for attaching the biological information detection device to a wrist 400 of a subject. The main body unit 300 which is a device main body is provided with a display unit 310 that displays various types of information, a pulse wave sensor (a sensor configured by a detection unit, a translucent member, etc.), a processing unit that performs various types of processing, and the like. It is done. The display unit 310 displays the measured pulse rate and time. In FIG. 1A, the circumferential direction of the wrist 400 (or arm) is defined as a first direction DR1, and the direction from the hand 410 toward the lower arm 420 is defined as a second direction DR2.

  FIG. 1B is an external view illustrating a detailed configuration example of the biological information detection apparatus. The bands 320 and 322 are connected to the main body 300 via the stretchable parts 330 and 332. The stretchable parts 330 and 332 can be deformed along the first direction DR1 and the second direction DR2 in FIG. A connecting portion 340 is connected to one end of the band 320. The connecting portion 340 corresponds to a buckle in a timepiece, and a band hole portion into which a buckle bar portion is inserted is formed in a band 322 on the opposite side.

  As shown in FIG. 2A, the connecting portion 340 includes a fixing member 342 fixed to the band 320, a slide member 344, and springs 350 and 352 that are elastic members. As shown in FIGS. 2B and 2C, the slide member 344 is slidably attached to the fixed member 342 along the slide direction DRS, and the springs 350 and 352 are slid. Generates a pulling force in time. The load mechanism of this embodiment is realized by the springs 350 and 352, the expansion and contraction portions 330 and 332, the bands 320 and 322, and the like.

  The fixing member 342 is provided with an indicator 343, and the indicator 343 is provided with a scale for indicating an appropriate slide range. Specifically, the display 343 is provided with points P1 and P2 indicating an appropriate slide range (pressing range). If the end of the slide member 344 on the band 320 side is located within the range of these points P1 and P2, it is within the proper slide range (pressing range) and an appropriate tensile force is applied. It is guaranteed that The user inserts the rod portion of the connecting portion 340 that is a buckle into the band hole portion of the band 322 so as to be within the proper slide range, and attaches the biological information detection device to the wrist. By doing so, it is ensured to some extent that the pressure of the pulse wave sensor (the convex portion of the translucent member) on the subject is the appropriate pressure assumed. Details of the structure of the biological information detection apparatus shown in FIGS. 1A to 2C are disclosed in Japanese Patent Application Laid-Open No. 2012-90975.

  In addition, although FIG. 1 (A)-FIG.2 (C) demonstrated taking the case where the biometric information detection apparatus was a timepiece type | mold pulse meter with which a wrist is mounted | worn, this embodiment is not limited to this. For example, the biological information detection apparatus of the present embodiment may be mounted on a part other than the wrist (for example, finger, upper arm, chest, etc.) and detect (measure) biological information. Further, the biological information to be detected by the biological information detection device is not limited to the pulse wave (pulse rate), and the biological information detection device can detect biological information other than the pulse wave (for example, oxygen saturation in the blood, body temperature, A device that detects a heartbeat or the like may be used.

  FIG. 3 is a perspective view illustrating a configuration example of the back cover 10 provided on the back side of the main body 300 of the biological information detection apparatus, and FIG. 4 is a cross-sectional view taken along line A-A ′ of FIG. 3. The back cover part 10 is composed of a cover member 20 and a translucent member 30, and the back cover part 10 forms a housing surface 22 (back face) on the back side of the main body part 300.

  The translucent member 30 is provided on the side of the housing surface 22 that comes into contact with the subject of the biological information detecting device, and transmits light from the subject. The translucent member 30 contacts the subject when measuring the biological information of the subject. For example, the convex part 40 of the translucent member 30 contacts the subject. The surface shape of the convex portion 40 is desirably a curved surface shape (spherical shape), but is not limited to this, and various shapes can be adopted. Moreover, the translucent member 30 should just be transparent with respect to the wavelength of the light from a subject, and may use a transparent material and may use a colored material.

  As shown in FIG. 4, the cover member 20 is formed so as to cover the translucent member 30. Although the translucent member 30 has translucency, the cover member 20 does not have translucency and is a non-translucent member. For example, the translucent member 30 is formed of a transparent resin (plastic), and the cover member 20 is formed of a predetermined color resin such as black. In addition, non-light-transmissive means the material which does not permeate | transmit the light of the wavelength which a biological information detection apparatus can detect.

  As shown in FIGS. 3 and 4, a part of the translucent member 30 is exposed to the subject side from the opening of the cover member 20, and the convex portion 40 is formed on the exposed portion. Therefore, the convex part 40 formed in this exposed part contacts a subject (for example, skin of a user's wrist) at the time of measurement of biometric information. In FIG. 3 and FIG. 4, a detection window of the biological information detection device is configured by the convex portion 40 formed in the exposed portion. Here, in FIG. 4, the translucent member 30 is provided also in parts other than this detection window, ie, the back side part of the cover member 20 (pressing suppression part 60). However, this embodiment is not limited to this, You may provide the translucent member 30 only in the part of a detection window.

  In addition, as shown in FIG. 4, the groove part 42 for suppressing press fluctuation | variation etc. is provided in the circumference | surroundings of the convex part 40. As shown in FIG. Further, when the surface on the side where the convex portion 40 is provided in the translucent member 30 is the first surface, the translucent member 30 corresponds to the convex portion 40 on the second surface on the back side of the first surface. A recessed portion 32 is provided at a position to be used. The back cover 10 is also provided with a screw hole 24 for screwing the back cover 10 and a terminal hole 26 for connecting a terminal for signal transmission and power supply.

  As shown in FIG. 3, when the body surface 22 (back surface) of the biological information detection device is partitioned into a first region RG1 and a second region RG2 by a center line CL along the first direction DR1, The convex portion 40 is provided in the first region RG1. Taking a biological information detection device of the type worn on the wrist as shown in FIG. 1A as an example, the first region RG1 is a hand side (3 o'clock direction in the watch) region, and the second region RG2 Is an area on the lower arm side (9 o'clock direction on the watch). Thus, the convex part 40 of the translucent member 30 is provided in the first region RG1 on the side close to the hand on the housing surface 22. By doing so, the convex portion 40 is arranged at a place where the change in the diameter of the arm is small, so that the pressure fluctuation and the like can be suppressed.

  And the convex part 40 contacts a subject at the time of the measurement of the biological information of a subject, and gives a press (pressing force). Specifically, when the user wears the biological information detection device on the wrist and detects biological information such as a pulse wave, the convex portion 40 comes into contact with the skin of the user's wrist and gives pressure. This pressing is generated by the load by the load mechanism described with reference to FIGS. 1 (A) to 2 (C).

  In addition, the housing surface 22 of the biological information detection device is provided with a pressure suppression unit 60 that suppresses the pressure applied by the convex portion 40 to the subject (the wrist skin). 3 and 4, the pressing suppression unit 60 is provided on the housing surface 22 so as to surround the convex portion 40 of the translucent member 30. The surface of the cover member 20 functions as the pressing suppression unit 60. That is, the pressing suppression part 60 is formed by molding the surface of the cover member 20 into a bank shape. As shown in FIG. 4, the pressure suppression surface of the pressure suppression unit 60 is inclined so as to become lower from the position of the convex portion 40 toward the second direction DR2 (the direction from the wrist to the lower arm). . That is, the height in the direction DRH orthogonal to the housing surface 22 is inclined so as to become lower in the second direction DR2.

  3 and 4, the detection unit 130 and the convex portion 40 (detection window) are provided in the first region RG1 on the hand side (3 o'clock direction) of the housing surface 22 (back surface). The embodiment is not limited to this. For example, the detection part 130 and the convex part 40 (detection window) may be provided in the center part area | region (area | region where the centerline CL passes) of the housing surface 22, etc., and the press suppression part 60 may be provided in the periphery.

  As shown in FIG. 4, a detection unit 130 is provided below the convex portion 40 of the translucent member 30. Here, the upper direction is the direction DRH, and the lower direction is the direction opposite to the direction DRH. In other words, the downward direction is a direction from the back surface (the surface on the side in contact with the subject) of the main body 300 of the biological information detection apparatus to the front surface (the surface on the side not in contact with the subject). The pulse wave sensor in the present embodiment is a sensor unit including such a light transmitting member 30, the detection unit 130, and the like.

  The detection unit 130 includes a light receiving unit 140 and a light emitting unit 150. The light receiving unit 140 and the light emitting unit 150 are mounted on the substrate 160. The light receiving unit 140 receives light (reflected light, transmitted light, etc.) from the subject. The light emitting unit 150 emits light to the subject. For example, when the light emitting unit 150 emits light to the subject and the light is reflected by the subject (blood vessel), the light receiving unit 140 receives and detects the reflected light. The light receiving unit 140 can be realized by a light receiving element such as a photodiode. The light emitting unit 150 can be realized by a light emitting element such as an LED. For example, the light receiving unit 140 can be realized by a PN junction diode element or the like formed on a semiconductor substrate. In this case, an angle limiting filter for narrowing the light receiving angle and a wavelength limiting filter for limiting the wavelength of light incident on the light receiving element may be formed on the diode element.

  Taking a pulse meter as an example, the light from the light emitting unit 150 travels inside the subject and diffuses or scatters in the epidermis, dermis, subcutaneous tissue, and the like. Thereafter, this light reaches the blood vessel (detected site) and is reflected. At this time, part of the light is absorbed by the blood vessels. Then, the light absorption rate in the blood vessel changes due to the influence of the pulse, and the amount of reflected light also changes. Therefore, the light receiving unit 140 receives this reflected light and detects the change in the amount of light, thereby detecting biological information. It becomes possible to detect the pulse rate and the like.

  In FIG. 4, both the light receiving unit 140 and the light emitting unit 150 are provided as the detecting unit 130. However, for example, only the light receiving unit 140 may be provided. In this case, for example, the light receiving unit 140 receives transmitted light from the subject. For example, when light from the light emitting unit 150 provided on the back side of the subject passes through the subject, the light receiving unit 140 receives and detects the transmitted light.

  And in this embodiment, as shown in FIG. 4, the aperture | diaphragm | squeeze parts 80 and 82 are provided. When the light receiving unit 140 is provided as the detection unit 130, the diaphragm units 80 and 82 throttle light from the subject in the optical path between the subject and the detection unit 130. When the light emitting unit 150 is provided as the detection unit 130, the diaphragm units 80 and 82 condense the light from the light emitting unit 150 in the optical path between the subject and the detection unit 130. In FIG. 4, the aperture portions 80 and 82 are provided between the translucent member 30 and the detection unit 130. However, the diaphragms 80 and 82 may be provided between the translucent member 30 and the subject or in the translucent member 30. For example, the diaphragm portions 80 and 82 are disposed in proximity to the translucent member 30.

  In FIG. 4, the light shielding unit 100 is provided between the light receiving unit 140 and the light emitting unit 150. When both the light receiving unit 140 and the light emitting unit 150 are provided as the detecting unit 130, the light shielding unit 100 shields light from the light emitting unit 150 from being directly incident on the light receiving unit 140, for example.

2. In the living body information detection apparatus as in the present embodiment, the surface of the translucent member 30 that comes into contact with the skin that is the subject is a finite area contact surface. In this embodiment, for example, a relatively soft material such as skin is brought into contact with the contact surface of the light-transmitting member 30 of a hard material formed of resin, glass, or the like. Then, from the viewpoint of elastic mechanics, a region that is not in contact with the skin and a region where the contact pressure is weak are generated in the vicinity of the peripheral portion (outer peripheral portion) of the translucent member 30. In addition, even when an external force is applied to the device of the biological information detection apparatus and a moment is generated in the device, the region near the peripheral edge of the contact surface is most likely to float.

  The light passing between the light emitting unit 150, the skin, and the light receiving unit 140 via such a region is likely to generate optical intensity due to a dynamic change in contact state. If such light is incident on the light receiving unit 140, the noise has no correlation with the pulse component.

  Even in a static contact state, signal quality can be degraded. If the skin is not properly in contact, external light that does not originate from the light emitting unit 150 may enter the light receiving unit 140. On the other hand, when the contact pressure is excessive, the pulsating component is less likely to enter the light that has passed through this region by crushing the subcutaneous blood vessel.

  The greater the noise is superimposed, the lower the signal quality of the pulse wave detection signal, and the reliability of measurement data decreases in various biological measurements such as pulse measurement.

  For example, FIG. 5 (A) shows a case where the convex portion 40 (contact surface) of the translucent member 30 gives a small pressure to the skin 2 as the subject, and FIG. 5 (B) shows a case where the pressure is large. ing. When attention is paid to the locations indicated by A1 and A2 in FIGS. 5A and 5B, the contact state between the skin 2 and the convex portion 40 changes due to the change in the pressure. For example, in FIG. 5A, the skin 2 and the convex portion 40 are in a non-contact state or weak contact state at locations A1 and A2, but in FIG. 5B, they are in a contact state. Therefore, the intensity of light emitted from the light emitting unit 150 and returning to the light receiving unit 140 changes between FIG. 5A and FIG. 5B, and the reliability of measurement data decreases. 5A and 5B may be interpreted as an enlarged view of the periphery of the recess 32 in the AA ′ cross-sectional view of the biological information detecting device shown in FIG. 3, and with respect to the direction DRH. You may interpret as the projection figure or the layout figure which projected the component parts around the recessed part 32 from the perpendicular direction. Hereinafter, the present embodiment will be described with reference to the similar diagrams in FIGS. 5A and 5B. However, it is assumed that both diagrams can be similarly interpreted.

  For example, FIGS. 6A and 6B are diagrams for explaining Hertz's elastic contact theory. E is the skin Young's modulus, v is the skin Poisson's ratio, F is the maximum force applied, r is the spherical radius, α is the radius of the contact circle, and σ is the displacement. By substituting predetermined values for these parameters and calculating the pressure against the distance from the center of the contact surface based on Hertz's elastic contact theory, a result such as that shown in FIG. 6B is obtained. As shown in FIG. 6 (B), when the distance is away from the center of the contact surface, the pressure decreases, and for example, in the portions indicated by B1 and B2, the pressure rapidly decreases. Therefore, at the locations indicated by A1 and A2 in FIG. 5 (A) and FIG. 5 (B), the pressure on the contact surface changes abruptly due to slight changes in the load, and the reliability of the measurement data is significantly reduced. To do.

  For example, in FIG. 5 (A) and FIG. 5 (B), the contact surface of the translucent member 30 that comes into contact with the skin of the human body is constituted by a curved convex shape (convex portion). By doing in this way, since the close_contact | adherence degree of the translucent member 30 with respect to the skin surface improves, invasion of noise lights, such as the reflected light amount from a skin surface, and disturbance light, can be prevented.

  However, as is clear from FIG. 6A and FIG. 6B, the contact pressure with the skin is relatively lowered with respect to the central portion at the convex peripheral portion (outer peripheral portion).

  In this case, if the contact pressure at the central portion is optimized, the contact pressure at the peripheral portion is less than the optimum range. On the other hand, if the contact pressure at the peripheral edge is optimized, the contact pressure at the center is excessive with respect to the optimum range.

  When the contact pressure is less than the optimum range, the pulse wave sensor detects if the pulse wave sensor comes in contact with or away from the skin due to the shaking of the device, or the pulse wave sensor does not crush the veins even if it remains in contact. Body motion noise is superimposed on the signal. If this noise component is reduced, a pulse wave detection signal having a higher M / N ratio (S / N ratio) can be obtained. Here, M represents the signal level of the pulse wave detection signal, and N represents the noise level.

  In order to solve the problems as described above, as shown in FIGS. 4, 7A, and 7B, the biological information detection apparatus of the present embodiment uses light from a subject (skin etc.). It has the detection part 130 which has the light-receiving part 140 which light-receives, the translucent member 30, and the aperture parts 80 and 82 (aperture). The translucent member 30 is provided on the side of the housing 22 that contacts the subject of the biological information detecting device, transmits light from the subject, and contacts the subject when measuring the biological information of the subject. The diaphragms 80 and 82 squeeze light from the subject in the optical path between the subject and the detection unit 130. In FIG. 4 and the like, the detection unit 130 includes a light emitting unit 150 that emits light to the subject, and the translucent member 30 transmits light from the light emitting unit 150. The diaphragms 80 and 82 squeeze the light from the light emitting unit 150 in the optical path between the subject and the detection unit 130. The reflector 152 is for reflecting the light emitted from the light emitting unit 150 to increase the light use efficiency.

  As described above, in this embodiment, the diaphragm portions 80 and 82 are provided so that light (stray light) is not detected at the locations indicated by A1 and A2 in FIGS. 7A and 7B. Squeezed. For example, the light passing through the central portion (for example, the apex of the convex portion) of the light-transmitting region of the light-transmitting member 30 that has been optimally pressed is transmitted without blocking as much as possible, while the light-transmitting region ( For example, light passing through the vicinity of the peripheral edge of the convex portion is blocked. For example, in FIGS. 7A and 7B, by providing the diaphragm portion 80, light at a location indicated by A1 that is the peripheral portion is not incident on the light receiving portion 140. In addition, by providing the diaphragm unit 82, the light from the light emitting unit 150 is prevented from being emitted to the place indicated by A2. That is, in this embodiment, light is focused at a place where the contact state changes due to a change in pressure (load). In this way, even when the contact state changes at the locations indicated by A1 and A2 as shown in FIGS. 7A and 7B, the light state at the locations indicated by A1 and A2 is received. The result will not be affected. Therefore, the reliability of measurement data can be improved.

  Further, in FIGS. 4, 7 </ b> A, 7 </ b> B, etc., a light shielding unit 100 (light shielding wall) is provided between the light receiving unit 140 and the light emitting unit 150. The light shielding portion 100 is, for example, a light shielding wall formed to extend in a direction DRH orthogonal to the housing surface 22 (see FIGS. 3 and 4). Specifically, for example, the light shielding unit 100 having a wall surface along a direction intersecting (orthogonal) with respect to a line segment connecting the center position of the light receiving unit 140 and the center position of the light emitting unit 150 is provided. By providing such a light shielding unit 100, direct light from the light emitting unit 150 is prevented from entering the light receiving unit 140, and the reliability of measurement data and the like can be further improved.

  That is, the closer the distance between the light receiving unit 140 and the light emitting unit 150 is, the more optical efficiency and performance is improved. For example, optical efficiency and performance deteriorate in inverse proportion to the square of the distance. Therefore, it is desirable to make the distance between the light receiving unit 140 and the light emitting unit 150 as close as possible.

  However, when the distance between the light receiving unit 140 and the light emitting unit 150 is reduced, the possibility that the direct light from the light emitting unit 150 is incident on the light receiving unit 140 and the performance deteriorates increases.

  Therefore, the light shielding unit 100 is provided between the light receiving unit 140 and the light emitting unit 150 to prevent direct light from the light emitting unit 150 from entering the light receiving unit 140. In other words, in the present embodiment, as described above, the diaphragm portions 80 and 82 are provided in order to remove an adverse optical effect from the path where the contact state of the contact surface with the subject becomes unstable. On the other hand, the light shielding unit 100 removes adverse effects of the light emitting unit 150 caused by direct light. In this way, the optical parts of the photoelectric pulse wave sensor are configured by the diaphragm portions 80 and 82 that remove noise due to the change in the contact state of the contact surface with the subject, and the light shielding portion 100 that removes direct light from the light emitting portion 150. It is possible to ensure a stable stability. In addition, about the light-shielding part 100, it can also be set as the structure which does not provide this.

  As described above, as shown in FIG. 8A, the case where the translucent member 30 has the convex portion 40 has been described. However, the biological information detection apparatus of the present embodiment is not limited to this. For example, as shown in FIG. 8B, even when the translucent member 30 does not have a convex portion 40 such as a curved surface shape, by providing the diaphragm portions 80 and 82 and the light shielding portion 100, the reliability of measurement data due to stray light is improved. The fall of property etc. can be controlled. For example, the translucent member 30 has a three-dimensional shape that comes into contact with the object at a non-planar portion, and the diaphragm portions 80 and 82 are installed so as to shield a relatively low portion of the three-dimensional shape. Become.

  8A and 8B, RTR represents a light-transmitting region (light-transmitting region) of the light-transmitting member 30, and RAP represents a diaphragm region (region for condensing light) of the aperture portions 80 and 82. ). STR represents the area of the translucent region RTR, and SAP represents the area of the aperture region RAP. For example, in FIG. 3, the translucent member 30 that is not covered with the cover member 20 and is exposed to the subject side is the translucent region RTR. The aperture region RAP is an aperture region of the aperture portions 80 and 82. The stop area RAP of the stop portions 80 and 82 is an area surrounded by the translucent area RTR in a plan view, for example.

  Specifically, as shown in FIGS. 8A and 8B, the area SAP of the aperture region RAP (opening region) of the aperture portions 80 and 82 is the area STR of the translucent region RTR of the translucent member 30. Is smaller than That is, the diaphragm portions 80 and 82 block light passing through the peripheral region (outer peripheral region) of the translucent member 30, and the area SAP is smaller than the area STR by at least the area of the peripheral region. .

  8A and 8B, the shape of the stop region RAP of the stop portions 80 and 82 is similar to the shape of the light transmitting region RTR of the light transmitting member 30 (including a substantially similar shape). ing. When the translucent member 30 has the convex portion 40 as shown in FIG. 8A, the shape of the translucent region RTR is, for example, similar to the planar projection shape of the convex portion 40 (substantially similar). For example, in FIGS. 8A and 8B, the translucent region RTR and the aperture region RAP are both circular and similar in shape. For example, when the translucent region RTR has a quadrangular shape, the shape of the aperture region RAP may be a similar quadrangular shape. However, the similar shape mentioned here does not need to be a complete similar shape, and may be a substantially similar shape (similar shape as a type of figure). Further, the shape of the light transmitting region RTR and the shape of the aperture region RAP may not be similar.

  8A and 8B, the height of the light-shielding part 100 in the direction DRH orthogonal to the housing surface 22 in FIGS. 3 and 4 is H1, and the diaphragm parts 80 and 82 are located on the detection part side. Assuming that the height of the lower surface which is a surface is H2, the relationship of H1> H2 is established. By doing so, it is possible to suppress a situation in which light from the light emitting unit 150 is reflected by the diaphragm units 80 and 82 and is incident on the light receiving unit 140.

  9A to 9C are explanatory diagrams of a method for setting the hole diameter of the aperture region RAP. In FIG. 9A, ARR represents the light receiving area of the light receiving unit 140, and ART represents the light irradiation area of the light emitting unit 150. The light receiving area ARR and the light irradiation area ART are areas set by the half-value width of the light intensity. The aperture area RAP can be determined by the light receiving area ARR and the light irradiation area ART. For example, the aperture region RAP is a region including at least the area on the light shielding unit 100 side (center side) of the light receiving area ARR and the light irradiation area ART.

  FIG. 9B is a diagram showing the relationship between the hole diameter (transmission hole diameter) of the aperture region RAP and the average pulse wave DC value. As shown in FIG. 9B, the larger the hole diameter of the aperture region RAP, the larger the transmitted light increases, so the average pulse wave DC value increases. However, the increase in the average pulse wave DC value with respect to the increase in the hole diameter of the throttle region RAP is saturated. For example, in FIG. 9B, the aperture is saturated when the diameter of the aperture region RAP reaches about 4 mm.

  FIG. 9C is a diagram showing the relationship between the hole diameter (aperture diameter) of the aperture region RAP and the M and N powers. Here, M represents the signal level of the pulse wave signal, and N represents the noise level. As shown in FIG. 9C, when the hole diameter is larger than 5 mm, the noise level increases rapidly. This is because, as described with reference to FIGS. 5A and 5B, when the hole diameter increases, stray light in the peripheral region of the translucent member 30 enters the light receiving unit 140 and is detected as noise. It is.

  Thus, if the hole diameter of the aperture region RAP becomes too small, the amount of received light decreases, and the level of the pulse wave detection signal decreases. Due to stray light or the like in the peripheral region of the optical member 30, the noise component increases. Therefore, the hole diameter of the aperture region RAP is within a range in which the level of the pulse wave detection signal can be sufficiently secured, and the influence due to the change in the contact state with the subject (skin, skin) (that is, noise) can be minimized. It is desirable to set it to a value. For example, in the case of FIGS. 9A to 9C, the hole diameter is set to about 4 mm (φ4).

  FIG. 10A to FIG. 11B are explanatory diagrams of the arrangement setting method of the apertures.

  For example, in FIG. 10A, the first end ED1 (the end on the light receiving unit side) of the light transmitting region of the translucent member 30 and the second end ER2 (the right end) of the light receiving unit 140 are arranged. The connecting line is LN1. The second end ER2 is an end on the side farther from the first end ED1 of the light-transmitting region among the two ends ER1 and ER2 of the light receiving unit 140. A line connecting the second end ER2 of the light receiving unit 140 and the end EA1 on the opening side of the diaphragm 80 is denoted as LN2. An angle formed between the line LN1 and the optical axis AXR (axis perpendicular to the light receiving surface) of the light receiving unit 140 is θr, and an angle formed between the line LN2 and the optical axis AXR is θa.

  In this case, θa <θr in FIG. That is, the aperture 80 on the light receiving unit 140 side is arranged and set so that θa <θr.

  If the relationship of θa <θr is established in this way, the light from the first end ED1 of the light-transmitting region of the light-transmitting member 30 is blocked by the aperture 80, as is apparent from FIG. Thus, the light is not incident on the light receiving unit 140.

  For example, since the light receiving unit 140 detects the amount of light received by the entire light receiving surface, even the light incident on the second end ER2 is detected as the total amount of received light. Therefore, when the state of light incident on the second end ER2 of the light receiving unit 140 from the first end ED1 of the translucent member 30 changes due to a change in the contact state or the like, this is superimposed as noise, There arises a situation in which the reliability of measurement data decreases.

  In this regard, if the relationship of θa <θr is established as shown in FIG. 10A, the light from the first end ED1 of the light-transmitting region of the light-transmitting member 30 is blocked by the aperture 80, and thus the above-mentioned Such a situation can be effectively deterred.

  10B, the second end ED2 (end on the light emitting unit side) of the light transmitting region of the translucent member 30 and the first end ET1 (left end) of the light emitting unit 150 are provided. The connecting line is LN3. The first end ET1 is an end of the two ends ET1 and ET2 of the light emitting unit 150 that is farther from the second end ED2 of the translucent region. A line connecting the first end ET1 of the light emitting unit 150 and the end EA2 on the opening side of the diaphragm 82 is denoted as LN4. An angle formed between the line LN3 and the optical axis AXT (axis perpendicular to the light emitting surface) of the light emitting unit 150 is θt, and an angle formed between the line LN4 and the optical axis AXT is θb.

  In this case, θb <θt in FIG. That is, the diaphragm 82 on the light emitting unit 150 side is arranged and set so that θb <θt.

  If the relationship of θb <θt is established in this way, as is clear from FIG. 10B, the light traveling from the light emitting unit 150 to the second end ED2 of the light transmitting region of the light transmitting member 30 is reduced to the aperture unit. It will be interrupted by 82. Accordingly, it is possible to effectively suppress a situation such as reception of stray light at the second end ED2.

  Moreover, you may arrange | position arrangement | positioning of the aperture | diaphragm | squeeze parts 80 and 82 by a method as shown to FIG. 11 (A) and FIG. 11 (B).

  For example, in FIG. 11A, the first end ED1 (end on the light receiving unit side) of the translucent region of the translucent member 30 and the first end ER1 (left end) of the light receiving unit 140 are arranged. The connecting line is LN5. The first end ER1 is an end of the light receiving unit 140 on the side close to the first end ED1 of the light transmitting region. Further, a line connecting the second end ED2 (light emitting part side end) of the light transmitting region of the light transmitting member 30 and the second end ER2 (right side end) of the light receiving part 140 is LN6. . The second end ER2 is an end of the light receiving unit 140 on the side close to the second end ED2 of the translucent region among the two ends ER1 and ER2.

  In this case, in FIG. 11A, the aperture portions 80 and 82 are set so that the aperture portions 80 and 82 are positioned at least on the lines LN5 and LN6. That is, the diaphragm portions 80 and 82 are positioned on the optical paths of the lines LN5 and LN6.

  In this way, it is possible to ensure that stray light from the first and second end portions ED1 and ED2 of the light transmitting region of the light transmitting member 30 is blocked by the aperture portions 80 and 82. Accordingly, it is possible to effectively suppress a situation in which the reliability of measurement data is reduced due to stray light at the first and second end portions ED1 and ED2.

  In FIG. 11B, a line connecting the first end ED1 of the light-transmitting region of the light-transmitting member 30 and the first end ET1 (left-side end) of the light emitting unit 150 is denoted as LN7. The first end ET1 is an end on the side close to the first end ED1 of the light-transmitting region among the two ends ET1 and ET2 of the light emitting unit 150. A line connecting the second end ED2 of the light-transmitting region of the light-transmitting member 30 and the second end ET2 (right end) of the light-emitting unit 150 is denoted as LN8. The second end portion ET2 is an end portion of the two end portions ET1 and ET2 of the light emitting unit 150 on the side close to the second end portion ED2 of the light transmitting region.

  In this case, in FIG. 11B, the aperture portions 80 and 82 are set so that the aperture portions 80 and 82 are positioned at least on the lines LN7 and LN8. That is, the diaphragm portions 80 and 82 are located on the optical paths of the lines LN7 and LN8.

  In this way, it can be ensured that light from the light emitting unit 150 toward the first and second end portions ED1 and ED2 of the light transmitting region of the light transmitting member 30 is blocked by the aperture portions 80 and 82. become. Therefore, the situation where the light from the light emitting unit 150 becomes stray light at the first and second end portions ED1 and ED2 and the reliability of the measurement data decreases due to the stray light can be effectively suppressed. .

  In FIGS. 4, 7 </ b> A, 7 </ b> B, and the like, the diaphragm portions 80 and 82 are provided between the translucent member 30 and the detection unit 130 (the light receiving unit 140 and the light emitting unit 150). . For example, the diaphragms 80 and 82 are arranged and set at positions away from the translucent member 30 and the detection unit 130. As described above, if the apertures 80 and 82 are arranged between the light transmitting member 30 and the detection unit 130, stray light is effectively blocked by the apertures 80 and 82 on the optical path between the subject and the detection unit 130. Thus, it is possible to effectively suppress the situation where noise due to the stray light is superimposed on the measurement data. However, the arrangement forming method of the diaphragm portions 80 and 82 is not limited to this, and various modifications can be made. The diaphragm portions 80 and 82 are disposed between the light transmitting member 30 and the subject or the light transmitting member 30. It may be provided inside.

  For example, in FIG. 12A, the aperture portions 80 and 82 are provided between the translucent member 30 and the detector 130, but the aperture portions 80 and 82 are arranged so as to be in close contact with the translucent member 30. Is formed. In FIG. 12B, diaphragm portions 80 and 82 are disposed and formed in the translucent member 30 (in the material). In FIG. 12C, diaphragm portions 80 and 82 are disposed and formed between the subject and the translucent member 30. Thus, various modes can be envisaged as the arrangement forming method of the aperture portions 80 and 82.

  In addition, the manufacturing method of the aperture portions 80 and 82 is not limited to the method of forming the diaphragm members 80 and 82 separately from the translucent member 30 and the like as shown in FIGS. 4, 7A and 7B, and various methods can be used. Can be adopted. For example, when the aperture portions 80 and 82 are formed so as to be in close contact with the translucent member 30 as shown in FIGS. 12A and 12C, the aperture portions 80 and 82 are applied by a technique such as painting, vapor deposition, or printing. May be formed. Alternatively, when the aperture portions 80 and 82 are formed in the translucent member 30 as shown in FIG. 12B, the aperture portions 80 and 82 may be formed by a technique such as insert molding.

  Further, the shape of the aperture regions (apertures) of the aperture portions 80 and 82 may be similar to the translucent region of the translucent member 30 (substantially similar shape or pseudo-similar shape), or the light receiving portion 140 or the convex portion 40. The structure may be similar to the structure (substantially similar or pseudo-similar). Alternatively, it may be similar to the light receiving range of the light receiving unit 140 or the light emitting range of the light emitting unit 150 (substantially similar or pseudo-similar).

  According to the biological information detection apparatus of the present embodiment described above, the outgoing light passing through the region where the contact pressure between the pulse wave sensor and the skin is weak, or the region where the contact state between the pulse wave sensor and the skin is likely to change By blocking the diffused light from the skin, the noise component superimposed on the pulse wave detection signal can be reduced, and the signal quality can be improved.

3. In the present embodiment, the diaphragm portions 80 and 82 and the light shielding portion 100 may be integrally formed as the light shielding member 78. That is, the diaphragm portions 80 and 82 and the light shielding portion 100 (light shielding wall) are integrated. FIG. 13 is a perspective view showing a first example of the light shielding member 78 integrally formed as described above. FIGS. 14A and 14B are views showing a first example of the light shielding member 78, respectively. It is the upper side figure of an example, and sectional drawing.

  As shown in FIGS. 13 to 14B, the light blocking member 78 includes a diaphragm unit 80 (first diaphragm unit) provided on the light receiving unit side and a diaphragm unit 82 (on the light emitting unit side). A second diaphragm portion). A diaphragm opening 81 on the light receiving unit side is formed corresponding to the diaphragm unit 80 on the light receiving unit side, and a diaphragm opening 83 on the light emitting unit side is formed corresponding to the diaphragm unit 82 on the light emitting unit side. ing. Between the aperture portions 80 and 82, a light shielding portion 100 is formed integrally with the aperture portions 80 and 82. For example, the light shielding member 78 has a shape of a bottomed cylindrical portion having a bottom portion formed on one end side and opened on the other end side, and the bottom portions of the bottomed cylindrical portion are formed as throttle portions 80 and 82. Openings 81 and 83 that function as apertures are formed in the throttle portions 80 and 82 that are the bottom portions. Further, the light shielding portion 100 is formed so that the opening region on the other end side of the bottomed cylindrical portion is divided into two (divided).

  As shown in FIGS. 13 and 14A, the light shielding portion 100 has a small thickness at the central portion 102 thereof. By doing so, the distance between the light receiving unit 140 and the light emitting unit 150 can be made closer, and the optical efficiency and performance can be improved.

  Further, the height of the light shielding unit 100 in the direction DRH orthogonal to the housing surface 22 (see FIGS. 3 and 4) of the biological information detection device is H1, and the lower surface which is the surface on the detection unit 130 side of the diaphragms 80 and 82 Is assumed to be H2. These heights H1 and H2 are heights from a reference plane (for example, the substrate 160). In this case, the relationship of H1> H2 is established as shown in FIG. That is, the light shielding portion 100 is a light shielding wall that extends to a position higher than the lower surfaces of the aperture portions 80 and 82. By doing so, it is possible to suppress a situation in which light from the light emitting unit 150 is reflected by the diaphragm units 80 and 82 and is incident on the light receiving unit 140. That is, it becomes possible to remove the influence of the directly reflected light of the light emitting unit 150, and it is possible to suppress a decrease in reliability of measurement data.

  As shown in FIG. 14B, the light blocking member 78 is attached toward the substrate 160 from above (the direction DRH) of the substrate 160 on which the light receiving unit 140 and the light emitting unit 150 are mounted. That is, the light-shielding member 78 is attached so that the substrate 160 on which the light-receiving unit 140 and the light-emitting unit 150 are mounted is inserted into the opening region on the other end side of the bottomed cylindrical part shape of the light-shielding member 78. Projection portions 86 and 88 are formed on the light shielding member 78, and the projection portions 86 and 88 are fitted into holes formed in the substrate 160, so that the light shielding member 78 is attached to the substrate 160. It is fixed against. Thereby, for example, the diaphragm portions 80 and 82, the light shielding portion 100, the light receiving portion 140, and the light emitting portion 150 are arranged at positions corresponding to the concave portions 32 on the back side of the translucent member 30. In this case, the thickness of the translucent member 30 is thin at the concave portion 32. Therefore, the length of the optical path, which is the passing distance of the light incident on the light receiving unit 140 and the light emitted from the light emitting unit 150, through the translucent member 30 can be shortened. Therefore, attenuation of these lights in the translucent member 30 is reduced, and the amount of transmitted light can be improved.

  In addition, it is desirable that the diaphragm portions 80 and 82 and the light shielding portion 100 are subjected to processing for improving the optical efficiency and performance of the pulse wave sensor. For example, the processing of roughening the surfaces (wall surfaces) of the diaphragm portions 80 and 82 and the light shielding portion 100 is performed to suppress the light reflectance. Alternatively, the surfaces of the diaphragm portions 80 and 82 and the light shielding portion 100 have a moth-eye structure. For example, an uneven structure having a period of several tens to several hundreds of nanometers is formed on the surface to form an antireflection structure. Alternatively, the surface color of the apertures 80 and 82 and the light shielding unit 100 is set to a predetermined color such as black so as to prevent irregular reflection of light. In this way, it is possible to effectively suppress a situation in which the reflected light from the diaphragm portions 80 and 82 and the light shielding portion 100 becomes stray light and becomes a noise component of measurement data.

  As described above, in order to improve the optical efficiency and performance of the pulse wave sensor, it is desirable to minimize the distance between the light receiving unit 140 and the light emitting unit 150. For this reason, it is necessary to make the light-shielding part 100 as thin as possible. In particular, the wall thickness of the light shielding unit 100 is reduced in the central portion 102 of the light shielding unit 100 in FIGS. 13 and 14A (a region intersecting with a line connecting the center position of the light receiving unit 140 and the center position of the light emitting unit 150). .

  However, the strength of the single-piece structure of the light-shielding portion 100 having such a thin wall thickness is insufficient. For example, when traveling using a pulse meter or riding a bicycle, a strong impact (for example, about 10G) is applied to the device, and thus strength that can cope with the impact is required.

  Therefore, in the present embodiment, a technique is adopted in which the aperture portions 80 and 82 and the light shielding portion 100 are integrated. That is, each of the aperture portions 80 and 82 and the light shielding portion 100 is not realized by a single member, but a light shielding member 78 in which the aperture portions 80 and 82 and the light shielding portion 100 are integrally formed is used as shown in FIG. . With such a light shielding member 78 formed integrally, even if the wall thickness of the light shielding portion 100 is thin, it is possible to ensure the strength to withstand an impact.

  In addition, since the diaphragm portions 80 and 82 and the light shielding portion 100 all coincide with each other in terms of the purpose of optical stabilization, it is easy to share materials. For example, it becomes easy to set the colors of the surfaces of the diaphragm portions 80 and 82 and the light shielding portion 100 to black that does not cause irregular reflection.

  Further, by integrating the aperture portions 80 and 82 and the light shielding portion 100, the assemblability at the time of assembling the components is improved, which contributes to cost reduction. For example, in FIG. 14B, the light shielding member 78 is inserted into the concave portion 32 of the light transmitting member 30, and the projections 86 and 88 of the light shielding member 78 are attached to the substrate 160 on which the light receiving portion 140 and the light emitting portion 150 are mounted. The assembly of the pulse wave sensor can be completed simply by fitting and fixing.

  Further, considering the mass productivity of equipment, it is desirable to manufacture the light shielding member 78 by injection molding. However, if the wall thickness of the light shielding portion 100 is too thin, there is a possibility that the resin is not sufficiently filled in the portion of the light shielding portion 100 during injection molding.

  Therefore, in FIG. 14A, the area of the aperture 83 of the aperture 82 on the light emitting unit side is smaller than the area of the aperture 81 of the aperture 80 (first aperture) on the light receiving unit side. I have to.

  In FIG. 14A, the wall thickness of the light shielding unit 100 is minimized on a line LNRT connecting the center of the light receiving unit 140 and the center of the light emitting unit 150. For example, the wall thickness decreases as the distance from the central portion 102 approaches.

  For example, if the area of the opening 83 on the light emitting part side is reduced, the paths DP1 and DP2 in FIG. 14A can be set as the resin pouring path in the injection molding. Then, by pouring the resin through the path from DP1 to DP3 and the path from DP2 to DP4, the resin can be sufficiently filled, and the light shielding part 100 can be formed from the resin even in the central portion 102 where the wall thickness is thin. . For example, the size of the light emitting unit 150 realized by an LED or the like is generally smaller than the size of the light receiving unit 140 realized by a semiconductor IC of a photodiode or the like. Therefore, even if the area of the opening 83 on the light emitting unit side is reduced, there is not much problem. And by increasing the area of the opening part 81 on the light receiving part side, the light receiving efficiency can be increased, and the performance and the like of the biological information detecting apparatus can be improved.

  If the area of the opening 83 on the light emitting part side is reduced in this way to facilitate the pouring of the resin and the wall thickness at the central part 102 of the light shielding part 100 is reduced, the light receiving part 140 and the light emitting part 150 are obtained. The distance between can be reduced. Thereby, optical efficiency and performance can be improved. That is, it is possible to prevent the resin from being insufficiently filled at the time of injection molding and improve the yield and the like while achieving both the strength of the light shielding unit 100 and the optical efficiency and performance.

  15, 16 (A), and 16 (B), a perspective view, a top view, and a cross-section of a second example of the light shielding member 78 in which the aperture portions 80 and 82 and the light shielding portion 100 are integrally formed. The figure is shown. In the light shielding member 78 of the second example, as shown in FIG. 16A, the area of the opening 81 on the light receiving part side and the area of the opening 83 on the light emitting part side are equal. As shown in FIG. 16B, the translucent member 30 does not have a curved convex portion. As described above, various modifications can be made to the structure and shape of the light shielding member 78.

4). As shown in FIG. 17A, in this embodiment, the translucent member 30 has a convex portion 40 that comes into contact with and applies pressure to the subject when measuring biological information of the subject. Yes.

  The diaphragm portions 80 and 82 block light passing through the peripheral region of the convex portion 40 as indicated by C1 and C2. By doing so, it is possible to suppress a decrease in reliability of measurement data caused by stray light in a place where the contact state is unstable such as C1 and C2.

  Moreover, in FIG. 17 (A), the press suppression part 60 is provided. The pressing suppression unit 60 is provided so as to surround the convex portion 40 on the body surface (surface on the subject side) of the biological information detecting device, and suppresses the pressure that the convex portion 40 applies to the subject. In FIG. 3 and FIG. 4, the pressing suppression portion 60 has a pressing suppression surface that extends from the position of the convex portion 40 to the second direction DR2 side (the direction side from the hand toward the lower arm). Specifically, the pressing suppression unit 60 is realized by a bank-shaped portion formed on the cover member 20.

  In this case, for example, the height of the convex portion 40 in the direction DRH orthogonal to the housing surface of the biological information detecting device is HA (for example, the height of the apex of the curved surface shape of the convex portion 40), and the height of the pressing suppression unit 60 is high. When the height is HB (for example, the height at the highest place) and the value obtained by subtracting the height HB from the height HA (the difference between the heights HA and HB) is Δh, Δh = HA−HB> 0 A relationship is established. For example, the convex portion 40 protrudes from the pressure suppression surface of the pressure suppression unit 60 toward the subject so that Δh> 0. That is, the convex portion 40 protrudes toward the subject side by Δh from the pressure suppression surface of the pressure suppression portion 60.

  As described above, by providing the convex portion 40 that satisfies Δh> 0, for example, it is possible to apply an initial pressure to the subject to exceed the vein vanishing point. In addition, by providing the pressure suppressing unit 60 for suppressing the pressure applied to the subject by the convex portion 40, it is possible to minimize the pressure fluctuation in the usage range in which the biological information is measured by the biological information detecting device. Therefore, noise components and the like can be reduced. Here, the vein vanishing point is reduced to such an extent that the signal caused by the vein superimposed on the pulse wave signal disappears or does not affect the pulse wave measurement when the convex portion 40 is brought into contact with the subject and the pressure is gradually increased. It is a point.

  For example, in FIG. 17B, the horizontal axis is generated by the load mechanism described in FIGS. 1B to 2C (a mechanism constituted by an elastic member such as a spring or a stretchable part, a band, or the like). The load represents the load, and the vertical axis represents the pressure (pressure applied to the blood vessel) that the convex portion 40 applies to the subject. Then, it is assumed that the amount of change in the pressing of the convex portion 40 with respect to the load by the load mechanism that generates the pressing of the convex portion 40 is a pressing change amount. This amount of change in pressure corresponds to the inclination of the change characteristic of pressure against the load.

  In this case, the pressure suppression unit 60 has a second load range in which the load of the load mechanism is larger than FL1 with respect to the pressure change amount VF1 in the first load range RF1 in which the load of the load mechanism is 0 to FL1. The pressure applied to the subject by the convex portion 40 is suppressed so that the pressure change amount VF2 at RF2 is reduced. That is, in the first load range RF1 that is the initial pressing range, the pressing change amount VF1 is increased, while in the second load range RF2 that is the usage range of the biological information detecting device, the pressing change amount VF2 is decreased.

  That is, in the first load range RF1, the pressure change amount VF1 is increased to increase the inclination of the pressure change characteristic with respect to the load. Such a pressing with a large gradient of the change characteristic is realized by Δh corresponding to the protrusion amount of the convex portion 40. That is, by providing the convex portion 40 where Δh> 0, even when the load by the load mechanism is small, it is possible to give the subject an initial pressure necessary and sufficient to exceed the venous vanishing point. become.

  On the other hand, in the second load range RF2, the pressure change amount VF2 is reduced to reduce the inclination of the pressure change characteristic with respect to the load. Such a pressing with a small inclination of the change characteristic is realized by pressing suppression by the pressing suppressing unit 60. In other words, the pressure suppression unit 60 suppresses the pressure applied to the subject by the convex portion 40, thereby minimizing the pressure variation even when there is a load variation or the like in the usage range of the biological information detection device. It becomes possible to suppress. As a result, noise components can be reduced.

  As described above, by applying an optimized pressure (for example, about 16 kPa) to the subject, the signal component (M) of the pulse wave sensor can be increased and the noise component (N) can be reduced. In addition, by setting the pressure range used for pulse wave measurement to a range corresponding to the second load range RF2, it is possible to suppress a minimum pressure fluctuation (for example, about ± 4 kPa), and a noise component Can be reduced. In addition, by reducing the optical noise using the diaphragms 80 and 82 and the light shielding unit 100, it is possible to further reduce the noise component on the pulse wave detection signal.

  Now, Δh representing the protruding amount of the convex portion 40 is an important parameter for defining the optimum pressing. That is, in order to always give a pressure for exceeding the venous vanishing point, a certain amount of pop-out amount is necessary, and Δh needs to be a large value. However, if Δh becomes an excessive value, it may cause a reduction in the signal component of the pulse wave sensor and an increase in pressure fluctuation.

  Therefore, the minimum Δh is selected within a range where a signal component of the pulse wave sensor can be sufficiently secured, that is, within a range where the optimum pressure can be applied. That is, as long as Δh is smaller, the noise component can be kept lower as long as the optimum pressure can be applied.

  For example, FIG. 18A is an example of a measured value representing the relationship between Δh and the MN ratio (SN ratio) when the user performs a grouper action (GP). FIG. 18B is an example of a measurement value representing the relationship between Δh and the MN ratio when the user performs a running operation (RUN). Here, the MN ratio corresponds to the ratio of the signal component (M) and the noise component (N) of the pulse wave sensor.

  18A and 18B, the range of Δh is desirably 0.01 mm ≦ Δh ≦ 0.5 mm, and more preferably 0.05 mm ≦ Δh ≦ 0.35 mm. It is understood that it is desirable. For example, by making Δh = about 0.25 mm, the MN ratio can be maximized. That is, by setting Δh to a small value in this way, an increase in noise components caused by pressure fluctuations or the like is suppressed while giving the subject a minimum pressure to exceed the venous vanishing point, and the signal It becomes possible to increase the MN ratio representing the quality.

5. Overall Configuration of Biological Information Detection Device FIG. 19 is a functional block diagram illustrating an example of the overall configuration of the biological information detection device. 19 includes a detection unit 130, a body movement detection unit 190, a processing unit 200, a storage unit 240, and a display unit 310. Note that the biological information detection apparatus of the present embodiment is not limited to the configuration shown in FIG. 19, and various modifications such as omitting some of the components or adding other components are possible.

  The detection unit 130 detects biological information such as a pulse wave, and includes a light receiving unit 140 and a light emitting unit 150. A pulse wave sensor (photoelectric sensor) is realized by the light receiving unit 140, the light emitting unit 150, and the like. The detection unit 130 outputs a signal detected by the pulse wave sensor as a pulse wave detection signal.

  The body motion detection unit 190 outputs a body motion detection signal that is a signal that changes according to body motion, based on sensor information of various sensors. The body motion detection unit 190 includes, for example, an acceleration sensor 192 as a body motion sensor. The body motion detection unit 190 may include a pressure sensor, a gyro sensor, or the like as a body motion sensor.

  The processing unit 200 performs various signal processing and control processing using the storage unit 240 as a work area, for example, and can be realized by a processor such as a CPU or a logic circuit such as an ASIC. The processing unit 200 includes a signal processing unit 210, a pulsation information calculation unit 220, and a display control unit 230.

  The signal processing unit 210 performs various types of signal processing (filter processing and the like). For example, the signal processing unit 210 performs signal processing on a pulse wave detection signal from the detection unit 130, a body movement detection signal from the body movement detection unit 190, and the like. Do. For example, the signal processing unit 210 includes a body movement noise reduction unit 212. Based on the body motion detection signal from the body motion detection unit 190, the body motion noise reduction unit 212 performs a process of reducing (removing) body motion noise that is noise caused by body motion from the pulse wave detection signal. Specifically, for example, noise reduction processing using an adaptive filter or the like is performed.

  The pulsation information calculation unit 220 performs pulsation information calculation processing based on the signal from the signal processing unit 210 and the like. The pulsation information is information such as the pulse rate. Specifically, the pulsation information calculation unit 220 obtains a spectrum by performing frequency analysis processing such as FFT on the pulse wave detection signal after the noise reduction processing in the body motion noise reduction unit 212, and obtains the spectrum. In FIG. 5, processing is performed in which a representative frequency is a heartbeat frequency. A value obtained by multiplying the obtained frequency by 60 is a commonly used pulse rate (heart rate). Note that the pulsation information is not limited to the pulse rate itself, and may be other various information (for example, the frequency or cycle of the heartbeat) representing the pulse rate, for example. Moreover, the information which represents the state of pulsation may be sufficient, for example, it is good also considering the value showing the blood volume itself as pulsation information.

  The display control unit 230 performs display control for displaying various information and images on the display unit 310. For example, as shown in FIG. 1A, control is performed to display various information such as pulse information such as a pulse rate and time information on the display unit 310. Moreover, you may provide the alerting | reporting device which performs the output which stimulates perception of users, such as light, a sound, or a vibration, instead of the display part 310. FIG. As such a notification device, for example, an LED, a buzzer, or a vibrator can be assumed.

  Although the present embodiment has been described in detail as described above, it will be easily understood by those skilled in the art that many modifications can be made without departing from the novel matters and effects of the present invention. Accordingly, all such modifications are intended to be included in the scope of the present invention. For example, a term described at least once together with a different term having a broader meaning or the same meaning in the specification or the drawings can be replaced with the different term in any part of the specification or the drawings. Further, the configuration and operation of the biological information detection apparatus are not limited to those described in the present embodiment, and various modifications can be made.

2 skin, 10 back cover, 20 cover member, 22 housing surface, 24 screw hole,
26 terminal hole part, 30 translucent member, 32 concave part, 40 convex part, 42 groove part,
60 pressure suppression part, 78 light shielding member, 80, 82 aperture part, 81, 83 opening part,
86, 88 Projection part, 100 Light shielding part, 102 Center part,
130 detector, 140 light receiver, 150 light emitter, 152 reflector,
160 substrate, 190 body motion detector, 192 acceleration sensor,
200 processing unit, 210 signal processing unit, 212 body movement noise reduction unit,
220 beat information calculation unit, 230 display control unit, 240 storage unit,
300 body, 310 display, 320, 322 bands,
330, 332 telescopic part, 340 connecting part, 342 fixing member, 343 indicator,
344 Slide member, 350, 352 Spring,
400 wrists, 410 hands, 420 lower arms

Claims (15)

A detection unit having a light receiving unit for receiving light from the subject;
A translucent member that is provided on a body surface side that comes into contact with the subject of the biological information detection device, transmits light from the subject, and contacts the subject when measuring biological information of the subject;
Light from the subject provided in an optical path between the light transmitting member and the detection unit, between the light transmitting member and the subject, or in the light transmitting member, and between the subject and the detection unit. An aperture part for narrowing down,
A biological information detection device comprising: In claim 1,
The detector is
Including a light emitting unit that emits light to the subject;
The translucent member transmits light from the light emitting unit,
The throttle part is
The biological information detection apparatus characterized by narrowing the light from the light emitting part in the optical path between the subject and the detection part. In claim 2,
The living body information detection apparatus having a first diaphragm provided on the light receiving unit side and a second diaphragm provided on the light emitting unit side as the diaphragm unit. In claim 3,
The area of the opening of the second diaphragm provided on the light emitting part is smaller than the area of the opening of the first diaphragm provided on the light receiving part. Biological information detection device. In any one of Claims 1 thru | or 4,
A first end of the translucent region of the translucent member and a second end that is an end of the translucent region farther from the first end of the two ends of the light receiving unit; A line connecting the second end portion of the light receiving portion and the end portion on the opening side of the aperture portion, where θr is an angle formed between the line connecting the light receiving portion and the optical axis of the light receiving portion, and the optical axis A biological information detection apparatus, wherein θa <θr, where θa is an angle formed by. In any one of Claims 1 thru | or 4,
A first end portion which is an end portion of the light transmitting region closer to the first end portion of the light transmitting portion and a first end portion of the light transmitting region of the light transmitting member; A second end of the translucent region of the translucent member and an end portion of the two ends of the light receiving unit that are close to the second end of the translucent region. The biological information detecting apparatus, wherein the diaphragm portion is arranged and set so that the diaphragm portion is positioned on a line connecting the two end portions. In any of claims 2 to 4,
A first end that is a second end of the translucent region of the translucent member and an end far from the second end of the translucent region of the two ends of the light emitting unit; A line connecting the first end portion of the light emitting portion and the end portion on the opening side of the aperture portion, where θt is an angle between the line connecting the light emitting portion and the optical axis of the light emitting portion, and the optical axis A biological information detection apparatus, wherein θb <θt, where θb is an angle formed by. In any of claims 2 to 4,
A first end portion which is a first end portion of the translucent region of the translucent member and an end portion of the two end portions of the light emitting portion which are closer to the first end portion of the translucent region; A second end portion of the translucent region of the translucent member and an end portion on the side close to the second end portion of the translucent region among the two end portions of the light emitting unit. The biological information detecting apparatus, wherein the diaphragm portion is arranged and set so that the diaphragm portion is positioned on a line connecting the two end portions. In any one of Claims 1 thru | or 8.
The living body information detecting apparatus according to claim 1, wherein an area of the aperture region of the aperture portion is smaller than an area of the light transmitting region of the light transmitting member. In any one of Claims 1 thru | or 9,
The throttle part is
A biological information detection apparatus that blocks light passing through a peripheral region of the translucent member. In any one of Claims 1 thru | or 10.
The translucent member is
A convex portion that contacts and presses the subject when measuring the biological information of the subject;
The throttle part is
A biological information detection apparatus that blocks light passing through a peripheral area of the convex portion. In claim 11,
A biological information detection apparatus, comprising: a pressure suppression unit that is provided so as to surround the convex part, and that suppresses the pressure applied to the subject by the convex part. In claim 12,
When the amount of change in pressing of the convex portion relative to the load by the load mechanism that generates pressing of the convex portion is set as the amount of change in pressing,
The pressing suppression part is
The pressure change amount in the second load range in which the load of the load mechanism is larger than FL1 is smaller than the pressure change amount in the first load range in which the load of the load mechanism is 0 to FL1. As described above, the biological information detection apparatus is characterized by suppressing the pressure applied to the subject by the convex portion. In any one of Claims 1 thru | or 13.
The biological information detection apparatus according to claim 1, wherein the shape of the aperture region of the aperture portion is similar to the shape of the light transmitting region of the light transmitting member. In any one of Claims 1 thru | or 14.
A biological information detecting apparatus for detecting a pulse wave as the biological information.

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