JP6513541B2 - Measuring device and measuring system - Google Patents

Description

  The present invention relates to a measuring device and measuring system for measuring biological information.

  BACKGROUND Conventionally, a measuring device for measuring biological information from a test site such as the wrist of a subject is known. For example, in Patent Document 1, a pulse wave velocity (Pulse Wave Velocity (PWV)) is measured by attaching a pulse wave sensor to an upper arm and a knee of a subject and detecting each pulse wave. A wave propagation velocity measuring device is disclosed.

JP 2005-329122 A

  However, the measuring device as described in Patent Document 1 requires a relatively large configuration.

  An object of the present invention made in view of such a point of view is to provide a measuring device and a measuring system capable of measuring biological information with high accuracy with a small scale configuration.

In order to solve the above-mentioned subject, the measuring device concerning the present invention is:
An attachment unit attached to the subject;
And a first sensor unit supported by the mounting unit and having a light emitting unit and a light receiving unit, respectively.
When the first sensor unit and the second sensor unit acquire biological information of the subject, the first sensor unit and the second sensor unit are configured to receive the test subject while the mounting unit is attached to the subject. are arranged at intervals of less than 35mm along the blood vessel,
The distance between the light emitting unit in the first sensor unit and the light emitting unit in the second sensor unit is the distance between the light receiving unit in the first sensor unit and the light receiving unit in the second sensor unit. Less than.

  In addition, the light emitting element of the light emitting unit in the first sensor unit and the light emitting element of the light emitting unit in the second sensor unit are arranged at intervals of 35 mm or less along a predetermined blood vessel of the subject. May be

  The light emitting units may be disposed on both sides of the light receiving unit along a direction perpendicular to a predetermined blood vessel of the subject.

  The light receiving unit may include an opening having a predetermined diameter.

  The mounting unit may be a band mounted on the wrist of the subject.

  The biological information may be a pulse wave.

  Moreover, the control part which calculates a pulse wave propagation velocity based on the acquired pulse wave may be provided.

MEANS TO SOLVE THE PROBLEM In order to solve the said subject, the measurement system which concerns on this invention is
The measuring device described above,
And a display unit configured to display information based on the biological information acquired by the measurement device.

  According to the present invention, it is possible to provide a measuring device and a measuring system capable of measuring biological information with high accuracy in a small scale configuration.

It is a perspective view showing the appearance of the measuring device concerning one embodiment of the present invention. It is a schematic diagram which shows a part of measurement apparatus which concerns on one Embodiment of this invention, and its arrangement | positioning. It is the model which showed the time change of the output voltage output from two light receiving elements in an ideal state of an artery. It is a schematic diagram which shows the typical blood flow of wrist vicinity of a subject. It is the model which showed the time change of the output voltage output from two light receiving elements in a typical condition of an artery. It is the model which showed arrangement | positioning of the light emission part of the measuring apparatus which concerns on the 1st Embodiment of this invention. It is the model which showed arrangement | positioning of the light emission part of the measuring apparatus which concerns on the 2nd Embodiment of this invention. It is a schematic diagram which shows arrangement | positioning of the sensor part of the measuring apparatus which concerns on the 3rd and 1st embodiment of this invention. It is the schematic diagram which showed the package of the light receiving element of the measuring apparatus concerning the 4th Embodiment of this invention, and its arrangement | positioning. It is the model which showed the structure of the light emitting / receiving element of the measuring apparatus which concerns on the 5th Embodiment of this invention. It is the model which showed the mode of arrangement | positioning in the to-be-tested site | part of each light emitting / receiving element of the measuring apparatus concerning the 5th Embodiment of this invention. It is a schematic diagram which shows arrangement | positioning of the sensor part of the measuring apparatus which concerns on the 6th Embodiment of this invention. It is a schematic diagram which shows the measuring system containing the measuring device which concerns on embodiment of this invention.

  Hereinafter, an embodiment of the present invention will be described in detail with reference to the drawings.

  FIG. 1 is a schematic perspective view showing a schematic configuration of a measuring apparatus 100 according to an embodiment of the present invention. As shown in FIG. 1, the measuring apparatus 100 includes a mounting unit 110 and sensor units 120 a and 120 b. As shown in FIG. 1, the mounting portion 110 has a back surface 111 facing in the negative Z-axis direction and a surface 112 facing in the positive Z-axis direction shown in the figure. The measuring apparatus 100 is mounted and used in a state in which the back surface 111 side of the mounting unit 110 is directed to the test site of the living body of the subject. Therefore, in a state in which the subject wears the mounting unit 110 of the measurement apparatus 100, the subject can view the surface 112 of the mounting unit 110.

  The mounting unit 110 of the measuring apparatus 100 has openings 113a and 113b on the back surface 111 side. The measuring device 100 has a structure in which the sensor unit 120a protrudes from the opening 113a and the sensor unit 120b protrudes from the opening 113b.

  Since the mounting unit 110 is used in a state of being mounted on a subject, it is preferable that the mounting unit 110 have a member such as, for example, the band units 114 and 115. In FIG. 1, as an example, band portions 114 and 115 which are used by being wound around the arm of a subject are illustrated halfway through broken lines. The band portions 114 and 115 are not limited to the configuration as shown in FIG. 1 and may be any configuration that can be attached to the subject. In the present embodiment, the mounting portion 110 can be a band that is mounted on the wrist of the subject, including the band portions 114 and 115.

  The measuring device 100 measures biological information of the subject while the subject wears the measuring device 100. The biological information measured by the measuring device 100 can be any biological information that can be measured by the sensor units 120a and 120b. Hereinafter, as an example, measurement device 100 explains as what measures pulse wave of two places of a subject, and measures PWV.

  Further, in the present embodiment, the mounting portion 110 can be an elongated band including the band portions 114 and 115. The measurement of the biological information is performed, for example, in a state in which the subject wraps the mounting portion 110 of the measuring device 100 around the wrist. Specifically, the subject winds the mounting unit 110 around the wrist such that the sensor units 120a and 120b contact the test site, and measures biological information. The measuring apparatus 100 measures the PWV of the blood flowing in the ulnar artery or radial artery at the wrist of the subject.

  FIG. 2A is a side view schematically showing a part of a measuring apparatus 100 according to an embodiment of the present invention. FIG. 2A shows the side surface of the measuring apparatus 100 when viewed from the positive direction of the X axis shown in FIG. FIG. 2B is a schematic view showing the arrangement of the sensor units 120a and 120b of the measuring apparatus 100 according to an embodiment of the present invention. FIG. 2B shows only the sensor units 120a and 120b of the measuring apparatus 100 when viewed in the negative direction of the Z axis shown in FIG. In addition, the XYZ coordinate system shown to FIG. 2 (A) and (B) is the same as FIG. 1, and suppose that it is the same also in subsequent figures.

  As shown in FIG. 2A, the sensor units 120 a and 120 b are supported by the mounting unit 110. The measuring apparatus 100 has a structure in which the sensor units 120a and 120b protrude from the back surface 111 side of the mounting unit 110 in the negative Z-axis direction.

  Sensor part 120a, 120b is provided with a living body sensor which acquires living body information on a subject. The sensor units 120a and 120b measure biological information of the subject while in contact with the test site of the subject.

As described later, when the sensor unit 120a and the sensor unit 120b acquire the biological information of the subject, the sensor unit 120a and the sensor unit 120b extend along a predetermined blood vessel of the subject when the mounting unit 110 is attached to the subject. Will be placed. At that time, an interval ΔD ₁ between the sensor unit 120 a and the sensor unit 120 b is arranged to be 35 mm or less. Further, as shown in FIG. 2 (B), each sensor unit is disposed vertically (in the X-axis direction) with respect to the artery through which the blood flows in the positive Y-axis direction. The sensor units 120a and 120b respectively acquire pulse waves at different test sites by an optical method. Here, the pulse wave refers to a change in blood vessel volume caused by blood inflow as a waveform from the body surface, and is a part of biological information. In one embodiment of the present invention, the sensor units 120a and 120b optically acquire pulse waves that are biological information. Further, based on the acquired pulse wave, the control unit of the measuring apparatus 100 calculates PWV. In FIG. 2B, the sensor unit 120a is disposed on the upstream side of the artery and the sensor unit 120b is disposed on the downstream side. However, the present invention is not limited to this. It may be

  As shown in FIG. 2B, the sensor unit 120a includes two light emitting units 121a and 122a and a light receiving unit 123a. Similarly, the sensor unit 120b includes two light emitting units 121b and 122b and a light receiving unit 123b. As shown in FIG. 2B, the sensor units 120a and 120b are disposed at predetermined intervals along the X axis. In the sensor unit 120a, each light emitting / receiving unit is disposed in the order of the light emitting unit 121a, the light receiving unit 123a, and the light emitting unit 122a so as to intersect the artery and move in the positive X-axis direction. Similarly, in the sensor unit 120b, each light emitting / receiving unit is disposed in the order of the light emitting unit 121b, the light receiving unit 123b, and the light emitting unit 122b so as to intersect the artery and move in the positive X-axis direction. That is, the light emitting units are arranged at predetermined intervals on both sides of the corresponding light receiving unit along a direction (X-axis direction) perpendicular to a predetermined blood vessel of the subject.

  Further, as shown in FIGS. 2A and 2B, the light emitting portions 121a, 122a and 121b, 122b include the light emitting elements 124a, 125a and 124b, 125b, respectively, and the light receiving portions 123a and 123b are light receiving elements 126a and 126b. Each contains The light emitted from each of the light emitting elements propagates to the outside of the light emitting unit, and passes from the test site to the inside of the living body. At that time, the light scattered inside the living body is detected by each light receiving element. The pulse wave is acquired according to the detected scattered light intensity. As a light emitting element, an element such as an LED (Light Emitting Diode: Light Emitting Diode), an LD (Laser Diode: Laser Diode), or an SLD (Super Luminescent Diode: Superluminescent Diode) can be applied. Further, as the light receiving element, an element such as PD (photodiode: Photodiode) or PT (phototransistor: Phototransistor) can be applied, for example. In FIG. 2B, one light emitting / receiving element is shown for each light emitting / receiving unit, but the present invention is not limited to this, and the number of light emitting / receiving elements included in each light emitting / receiving unit may be plural. Good.

  In the above configuration, the case where each sensor unit includes two light emitting units and one light receiving unit has been described, but in one embodiment of the present invention, one light emitting unit and two light emitting units are included in each sensor unit. The measurement can also be performed by the configuration having the light receiving unit. Moreover, in each sensor part, it can measure also by the structure which has a light emission part and a light reception part one each, respectively. Hereinafter, a configuration having two light emitting units and one light receiving unit will be described.

  The light emitting units 121a and 122a and 121b and 122b emit, for example, light of any one of green (wavelength: 500 to 550 nm), red (wavelength: 630 to 780 nm), and near infrared (wavelength: 800 to 1600 nm). As long-wavelength light does not attenuate to a deeper position in the body as compared with short-wavelength light, measurement accuracy improves when biological information is measured using a near-infrared light emitting element.

  The principle of measuring PWV between close distances on the wrist based on the two acquired pulse waves will be described with reference to FIGS. 3 (A) and 3 (B). FIG. 3A is a schematic diagram showing an ideal state in which an artery is in a straight line between the two sensor units 120a and 120b, and the distance from the skin A1 does not change in the living body A2. FIG. 3B is a schematic diagram showing the time change of the output voltage output from the light receiving elements 126a and 126b included in the light receiving units 123a and 123b in the sensor units 120a and 120b in the state as illustrated in FIG. 3A. FIG. In FIG. 3A, among the light emitting and receiving units in the sensor units 120a and 120b, in particular, only the light emitting unit 121a of the sensor unit 120a and the light emitting unit 121b of the sensor unit 120b are shown. The light emitting units 121a and 121b respectively include light emitting elements 124a and 124b therein. In the embodiment of the present invention, each light emitting element is an LED, and each light receiving element is a PD.

  As shown in FIG. 3A, the light emitting units 121a and 121b contact the skin A1 on the surface of the wrist represented by a solid line when measuring biological information. The light emitted from the light emitting elements 124 a and 124 b is isotropically spread widely and enters the inside of the living body A 2 from the skin A 1 and reaches an artery to be measured for a pulse wave. In the artery, blood flows from left to right (Y-axis positive direction), and thus the pulse wave propagates in the same direction. At this time, the emitted light from the light emitting elements 124a and 124b that has reached the artery is scattered, and the scattered light intensity changes according to the volume time change of the blood vessel. The light receiving elements 126a and 126b included in the light receiving sections 123a and 123b detect the scattered light and output a voltage, whereby a pulse wave is obtained. In FIG. 3A, the light receiving portions 123a and 123b have the same position in the Y and Z axis directions as the light emitting portions 121a and 121b, and only the position in the X axis direction differs.

  FIG. 3 (B) shows a pulse wave waveform obtained in an ideal state as shown in FIG. 3 (A). The pulse wave a indicates the time change of the voltage output from the light receiving element 126a on the side of the sensor unit 120a having the light emitting unit 121a. The pulse wave b indicates the time change of the voltage output from the light receiving element 126b on the side of the sensor unit 120b having the light emitting unit 121b. In FIG. 3 (B), the respective waveforms are arranged vertically and compared.

Since the sensor unit 120a is disposed on the upstream side of the artery and the sensor unit 120b is disposed on the downstream side of the artery, the rising of the peak of the pulse wave a is earlier by Δt ₁ compared to the rising of the peak of the pulse wave b. Become. The PWV (m / sec) is obtained by dividing the interval ΔD ₁ between the sensor unit 120 a and the sensor unit 120 b by Δt ₁ . Thus, assuming an ideal state in which the artery is straight, the pulse waves a and b have the same waveform, and the phase difference at any point is also constant.

  By the way, an actual blood vessel does not become an ideal state as shown in FIG. 3 (A). The following description is given on the assumption that biological information is measured from an actual blood vessel. First, an actual blood vessel will be described with reference to FIG. FIG. 4 is a view schematically showing a state in which representative bones and blood vessels in the vicinity of the right wrist of a general subject are seen through from above the palm. At the right wrist of a typical subject, there are two bones, an ulna and a rib. Furthermore, two arteries, the ulnar artery V1 and the radial artery V2, pass through the inside of the living body along the ulna and the calcaneus respectively. In each artery, blood flows in the direction of the arrow shown in FIG.

  Here, as shown in FIG. 4, in the region R1 where the terminal end of the ulna is present, the ulnar artery V1 is disposed along the terminal end of the ulna. In the region R2 where the ulnar artery V1 is not disposed on the ulna, the ulnar artery V1 enters the inside of the living body. For this reason, the ulnar artery V1 dives deeper into the living body from the skin surface near the wrist in the regions R1 and R2 shown in FIG. That is, on the downstream side of the ulnar artery V1 viewed from the region R1 and on the upstream side of the ulnar artery V1 viewed from the region R2, the distance from the skin to the ulnar artery V1 is longer. Conversely, in the region between the regions R1 and R2, the ulnar artery V1 is disposed on the ulna and the ulnar artery V1 passes between the ulna and the skin, so the depth of the ulnar artery V1 in the living body It gets shallow. In the region sandwiched by the regions R1 and R2, the distance from the skin to the ulnar artery V1 is shorter and is almost constant.

  Similarly, as shown in FIG. 4, in the region R3 where the end of the rib is present, the radial artery V2 is disposed along the end of the rib. In the region R4 where the radial artery V2 is not placed on the radial bone, the radial artery V2 enters the inside of the living body. Therefore, the radial artery V2 dives deeper from the skin surface to the inside of the living body in the vicinity of the wrist in the regions R3 and R4 shown in FIG. That is, on the downstream side of the radial artery V2 viewed from the region R3 and on the upstream side of the radial artery V2 viewed from the region R4, the distance from the skin to the radial artery V2 is longer. Conversely, in the region between the regions R3 and R4, the radial artery V2 is disposed on the radial bone, and the radial artery V2 passes between the radial bone and the skin, so the depth of the radial artery V2 in the living body is It gets shallow. In the region sandwiched by the regions R3 and R4, the distance from the skin to the radial artery V2 is shorter and is almost constant.

  When measuring biological information from a blood vessel, it is preferable to use a site where the distance from the skin to the blood vessel is short, that is, where the depth of the blood vessel from the skin surface to the inside of the living body is shallow is the test site. Further, as shown in FIG. 3A, a state in which the distance from the skin to the blood vessel does not change inside the living body is ideal. By satisfying such conditions, the pulse wave can be measured more accurately. Therefore, in the present embodiment, the test site is immediately above the radial artery V2 in the region between the ulnar artery V1 or the regions R3 and R4 in the region between the regions R1 and R2 shown in FIG. Make it

  As a result of observing the waveform of the pulse wave outputted while variously changing the test site of the wrist, the lengths L1 and L2 of the ulnar artery V1 and the radial artery V2 just under the above-mentioned optimum test site are respectively 35 mm. The As a result of observation, it was found that the lengths L1 and L2 were 35 mm on average, though there were individual differences in the arrangement of blood vessels. The region R1 in which the terminal end of the ulna is present can be confirmed from the outside as a protrusion (ulnar protrusion) of the wrist. The region R3 in which the end of the rib is present can be confirmed from the outside as a protrusion (radial protrusion) of the wrist. The optimum range for pulse wave measurement is a range of 35 mm from the ulnar process to the upstream side of the ulnar artery. The optimum range for pulse wave measurement is a range of 35 mm from the radial projection to the upstream of the radial artery. The optimum range for pulse wave measurement is a range in which a blood vessel is present on the skin side of the rib or on the skin side of the ulna, respectively.

  FIG. 5A is a schematic view showing how the artery is curved near the two sensor portions 120a and 120b, and the distance from the skin A1 is long (deep in the living body A2). FIG. 5A shows a part of the inside of the living body along the Y-axis direction in FIG. 4 and a cross section of the two sensor units 120a and 120b. As described above, when the subject is a human, in many subjects, the ulnar artery or radial artery near the wrist is typically in a cross-sectional shape as shown in FIG. 5 (A). FIG. 5B is a schematic diagram showing the time change of the output voltage output from the light receiving elements 126a and 126b included in the two light receiving portions 123a and 123b in the state as shown in FIG. 5A. Similar to FIG. 3A, FIG. 5A particularly shows only the light emitting unit 121a of the sensor unit 120a and the light emitting unit 121b of the sensor unit 120b among the light emitting and receiving units. The light emitting unit 121a and the light emitting unit 121b respectively include the light emitting elements 124a and 124b therein.

  As in the case of FIG. 3A, in the artery, the blood flows in the positive Y-axis direction, and therefore the pulse wave also propagates in the same direction. At this time, the emitted light from the light emitting elements 124a and 124b that has reached the artery is scattered, and the scattered light intensity changes according to the volume time change of the blood vessel. The pulse waves are measured by detecting the scattered light by the light receiving elements 126a and 126b included in the light receiving sections 123a and 123b and outputting a voltage. In FIG. 5A, the light receiving portions 123a and 123b have the same position in the Y and Z axis directions as the light emitting portions 121a and 121b, and only the position in the X axis direction differs.

  FIG. 5 (B) shows the waveform of the pulse wave obtained in a typical state as shown in FIG. 5 (A) by a solid line. The pulse waves a and b show the waveform of the pulse wave obtained in the ideal state shown in FIG. 3B by a dotted line for comparison. The pulse wave a 'indicates the time change of the voltage output from the light receiving element 126a on the side of the sensor unit 120a having the light emitting unit 121a. The pulse wave b 'indicates the time change of the voltage output from the light receiving element 126b on the side of the sensor unit 120b having the light emitting unit 121b. In FIG. 5 (B), the respective waveforms are arranged vertically and compared.

  Since the light emitted from the light emitting elements 124a and 124b spreads isotropically and passes from the skin A1 through the inside of the living body A2, the waveform outputted from each light receiving element is directly below the test site where the sensor parts 120a and 120b are disposed. In addition to the blood vessel information of the above, blood vessel information of the upstream and downstream thereof is included. That is, in the situation as shown in FIG. 5A, the output voltage from each light receiving element is not only the information of the pulse wave obtained from the straight part of the artery, but the artery is curved upstream and downstream thereof It also includes pulse wave information obtained from the part.

  In such a situation, first, the pulse wave a 'and the pulse wave a are compared. Since the artery is curved on the upstream side as viewed from the light emitting element 124a and the distance from the skin A1 is long, the distance between the curved portion and the light receiving element 126a is also long. The longer the distance to the light receiving element 126a, the weaker the intensity of the scattered light to be detected. Therefore, the rising of the peak of the pulse wave a 'is delayed relative to the rising of the peak of the pulse wave a, as the intensity of the scattered light is weakened. On the other hand, since the downstream artery seen from the light emitting element 124a is linear as in the ideal state, the falling edge of the pulse wave a 'is the same as the falling edge of the pulse wave a. become. As described above, the phase of the pulse wave a 'is shifted in a direction delayed in time as compared to the phase of the pulse wave a by the delay of the rising of the peak.

  Subsequently, the pulse wave b and the pulse wave b 'are compared. Since the artery is curved downstream from the light emitting element 124b and the distance from the skin A1 is long, the distance between the curved portion and the light receiving element 126b is also long. The longer the distance to the light receiving element 126b, the weaker the intensity of the scattered light to be detected. Therefore, the fall of the peak of the pulse wave b 'is faster than the fall of the peak of the pulse wave b as the intensity of the scattered light becomes weaker. On the other hand, since the upstream artery seen from the light emitting element 124b is linear as in the ideal state, the rise of the peak of the pulse wave b 'is almost the same as the rise of the peak of the pulse wave b. Become. As described above, the phase of the pulse wave b 'is shifted in the temporally advancing direction as compared with the phase of the pulse wave b, as the fall of the peak becomes faster.

Here, the pulse wave a 'and the pulse wave b' are compared. The pulse wave a ′ and the pulse wave b ′ have phases shifted in opposite directions to each other as compared with the waveform (pulse wave a, pulse wave b) of each pulse wave obtained in an ideal state. The phase of the pulse wave a 'is shifted in the direction of delay in time, and the phase of the pulse wave b' is shifted in the direction of progress in time. In addition, the similarity of the waveforms of the two pulse waves a ′ and b ′ tends to be lost. Thus, in the ideal state, the rise of the peak of the pulse wave a on the upstream side is earlier by Δt ₁ than the rise of the peak of the pulse wave b on the downstream side. It is also assumed that the rise of the peak of the pulse wave a ′ is delayed by Δt ₂ compared to the rise of the peak of the pulse wave b ′ on the downstream side. Thus, in an actual measurement, if the interval ΔD ₁ between the two sensor parts is not optimally adjusted, the peak of the pulse wave b ′ is detected earlier in time depending on the measurement position of the pulse wave with respect to the artery. Ru. For this reason, apparently, a waveform is obtained as if the pulse wave is backflowing from the right to the left (in the negative Y-axis direction).

  Therefore, in the present invention, the reverse phenomenon of the phase difference between the sensor units 120a and 120b is eliminated. In the following, some solutions are described on the basis of some embodiments of the present invention. In each embodiment, a configuration different from the above-described configuration will be mainly described. Further, for convenience of explanation, the same reference numerals are appended to components having the same functions as the components described above, and the description thereof will be simplified or omitted as appropriate. When the present invention is carried out, only one of the following embodiments may be applied, or a plurality of different embodiments may be appropriately combined and applied.

First Embodiment
FIG. 6 is a schematic view showing the arrangement of the sensor units 120a and 120b of the measuring apparatus 100 according to the first embodiment of the present invention. FIG. 6 representatively shows only the light emitting units 121a and 121b and the light emitting elements 124a and 124b among the components of the sensor units 120a and 120b.

In order to eliminate the reverse phenomenon of the phase difference between the sensor units 120a and 120b, in the measuring apparatus 100 according to the first embodiment of the present invention, as shown in FIG. 6, the distance between the sensor unit 120a and the sensor unit 120b. Is adjusted optimally. That is, the interval between the sensor unit 120a and the sensor unit 120b is newly defined as ΔD _{2 and} is smaller than the interval ΔD ₁ shown in FIG. 5A (ΔD ₂ <ΔD ₁ ). The sensor units 120a and 120b are disposed at positions where light emitted from the light emitting elements 124a and 124b does not easily reach the curved portion of the artery. Thereby, the phase shift of pulse wave a 'and pulse wave b' as described in FIG. 5B does not occur, and acquisition of the ideal pulse wave described in FIG. 3B becomes possible. . When the interval ΔD ₂ between the sensor unit 120 a and the sensor unit 120 b is increased, the phase difference between the pulse wave a ′ and the pulse wave b ′ becomes sufficiently large, and the measuring apparatus 100 can measure the pulse wave more accurately. it can. However, if ΔD ₂ is too large, the sensor unit 120a and the sensor unit 120b are disposed immediately above the region where the artery is curved and the distance from the skin A1 is longer (regions B1 and B2 shown in FIG. 5A). It will be As a result, the intensity of the scattered light detected by the light receiving elements 126a and 126b becomes weak, and it becomes difficult to output the pulse wave waveform.

Under conditions that can detect the waveform of the pulse wave, the interval [Delta] D ₂ between the sensor portion 120a and the sensor section 120b has an upper limit. As a result of observing the waveform of the pulse wave outputted while variously changing the test site of the wrist, the upper limit value of the distance between the sensor units 120a and 120b was found to be 35 mm. This value can be considered to be equal to the lengths L1 and L2 of the ulnar artery V1 and the radial artery V2 immediately below the optimum test site in FIG. Therefore, preferably, when the sensor unit 120a and the sensor unit 120b acquire the biological information of the subject, the predetermined blood vessels of the subject (the mounting part 110 is attached to the subject) For example, they are arranged at intervals of 35 mm or less along the ulnar artery or radial artery near the subject's wrist. More specifically, the light emitting element 124a of the light emitting unit 121a in the sensor unit 120a and the light emitting element 124b of the light emitting unit 121b in the sensor unit 120b are arranged at an interval of 35 mm or less along a predetermined blood vessel of the subject Configure as.

On the other hand, since the size of each sensor unit 120a, 120b can be about 5 mm in width, in the present embodiment, the lower limit value of ΔD ₂ is about 5 mm (the distance between the light emitting elements of light emitting units 121a, 121 _b ) It can also be done. However, if ΔD ₂ is 5 mm, the phase difference between the output waveforms becomes small, and the output waveforms overlap. Therefore, under the condition that PWV can be measured appropriately, 10 to 15 mm is appropriate as the lower limit value of ΔD ₂ .

Thus, the above-mentioned reversal phenomenon of the phase difference is eliminated by adjusting ΔD ₂ more optimally between the above lower limit value and the upper limit value. As a result, the measuring apparatus 100 can accurately measure the biological information including the PWV while reducing the size of the configuration.

Second Embodiment
In the second embodiment of the present invention, as shown in FIG. 7, a lens unit is provided in the light emitting element of the light emitting unit, and the spread of light emitted from each light emitting element is suppressed. FIG. 7 representatively shows only one light emitting unit 121a of the sensor unit 120a and one light emitting unit 121b of the sensor unit 120b, and the light emitting elements 124a and 124b are respectively included therein. In the present embodiment, the lens portion 134a is provided to suppress the spread of the light emitted from the light emitting element 124a, and the lens portion 134b is provided to suppress the spread of the light emitted from the light emitting element 124b. In addition, it is preferable to provide a lens part similarly about each light emitting element contained inside the other light emission part 122a of the sensor part 120a, and the other light emission part 122b of the sensor part 120b.

As shown in FIG. 7, in this embodiment, it defines the distance [Delta] D ₃ between the sensor portion 120a and the sensor section 120b. As in the first embodiment of the present invention, ΔD ₃ is set to 35 mm or less. That is, the two sensor units 120a and 120b are disposed directly above the straight portion of the artery. In the artery, blood flows in the positive Y-axis direction shown in the figure, and thus the pulse wave also propagates in the same direction.

  At this time, the light emitted from the light emitting elements 124a and 124b is condensed by the lens portions 134a and 134b, so that the spread of the emitted light in the living body A2 is suppressed. The area where the light incident on the inside of the living body A2 is scattered is narrower than in the case where the light is emitted widely without providing the lens portions 134a and 134b. In other words, light incident on the inside of the living body A2 only reaches the straight part of the artery and is scattered only by the straight part. That is, in the present embodiment, the output voltage from each light receiving element includes only pulse wave information obtained from the straight portion of the artery, and includes pulse wave information obtained from the curved portions located upstream and downstream thereof. Absent.

  Thus, in the second embodiment of the present invention, the pulse wave information from the curved portion of the artery, which causes the phase inversion phenomenon as described above, is not included. For this reason, in the present embodiment, the measuring device 100 can improve the measurement accuracy of the pulse wave. Further, in the present embodiment, by providing the lens portions 134a and 134b on the light emitting elements 124a and 124b, the light emitted from the light emitting elements 124a and 124b is effectively used. That is, in the present embodiment, the measuring apparatus 100 can prevent light from entering in a direction not related to the arterial direction, and can perform measurement efficiently.

Third Embodiment
FIG. 8A is a schematic view showing the arrangement of the sensor units 120a and 120b of the measuring apparatus 100 according to the third embodiment of the present invention. FIG. 8B is a diagram schematically showing again the arrangement of the sensor units 120a and 120b of the measuring apparatus 100 according to the first embodiment of the present invention for comparison with FIG. 8A. is there. In FIGS. 8 (A) and 8 (B), defining a distance [Delta] D ₄ of the sensor unit 120a and the sensor section 120b. As described above, ΔD ₄ is set to 35 mm or less. That is, the two sensor units 120a and 120b are disposed directly above the straight portion of the artery. As shown in FIGS. 8A and 8B, in the artery, blood flows in the positive Y-axis direction, and hence the pulse wave also propagates in the same direction.

  In the third embodiment of the present invention, as shown in FIG. 8A, the distance between the light emitting units 121a and 122a in the sensor unit 120a and the light emitting units 121b and 122b in the sensor unit 120b is the light receiving unit in the sensor unit 120a. It is shorter than the distance between 123 a and the light receiving unit 123 b in the sensor unit 120 b. Further, as in the second embodiment, each light emitting element is provided with a lens portion so as to suppress the spread of light emitted from each light emitting element. In FIG. 8A, illustration of the light emitting / receiving element in each light emitting / receiving unit is omitted. In the first embodiment described above, as shown in FIG. 8B, the light emitted from each light emitting element spreads isotropically. On the other hand, in the third embodiment, as shown in FIG. 8A, directivity is given to light emitted from each light emitting element. In order to realize this directivity, in the third embodiment, the optical axis of the light emitted from each of the light emitting elements of the light emitting units 121a and 122a in the sensor unit 120a is inclined toward the light receiving unit 123a via the lens unit. There is. Similarly, the optical axes of light emitted from the light emitting elements of the light emitting units 121b and 122b in the sensor unit 120b are inclined toward the light receiving unit 123b via the lens unit. That is, in the third embodiment, the direction of light emitted from each light emitting element changes before and after passing through the lens unit. Similarly, each light receiving element may be provided with a lens portion. In this case, the direction of light incident on each light receiving element changes before and after passing through the lens unit.

  In the third embodiment, the upstream blood vessel information viewed from the sensor unit 120a and the downstream blood vessel information viewed from the sensor unit 120b are included in the scattered light detected by the light receiving elements of the light receiving units 123a and 123b. Absent. That is, in the third embodiment, since the pulse wave information obtained from the curved portion of the artery is not included in the measurement result, the similarity of the pulse wave waveforms output from the light receiving elements of the sensor units 120a and 120b is It is improved and reversal of the phase difference is avoided. In the third embodiment, the optical axis of the light emitted from each light emitting unit is inclined toward the corresponding light receiving unit 123a or 123b through the lens unit, and the light output received by each light receiving element is increased. . Furthermore, in the third embodiment, the optical axis of the light emitted from each light emitting element is inclined to the light receiving element side in the same sensor unit, so the light emitted from the light emitting element in one sensor unit is in the other sensor unit Prevent incident light to the light receiving element. Thus, the measuring apparatus 100 can measure the pulse wave with high accuracy.

Fourth Embodiment
FIG. 9A is a schematic view showing a package of the light receiving element 126 a of the measuring apparatus 100 according to the fourth embodiment of the present invention. FIG. 9B is a schematic view showing the light receiving units 123a and 123b of the measurement apparatus 100 according to the present embodiment when arranged along an artery. In FIG. 9B, the two light emitting units of each sensor unit are not shown.

  As shown in FIG. 9A, the light receiving unit 123a includes a light receiving element 126a. In the present embodiment, as shown in FIG. 9A, the light receiving element 126a is surrounded by a light shielding plate 150a having an opening 140a having a predetermined diameter. The opening 140a is provided immediately above the light receiving element 126a so that the light receiving element 126a can detect part of the light scattered by the artery. The same configuration as that described above can be applied to the light receiving unit 123b.

  As shown in FIG. 9 (B), in the artery, blood flows in the positive Y-axis direction, and therefore, the pulse wave also propagates in the same direction. In the present embodiment, light shielding plates 150a and 150b are provided to exclude scattered light including information on unwanted pulse waves. That is, the light scattered by the curved portion of the artery on the upstream side viewed from the light receiving unit 123a and the downstream artery viewed from the light receiving unit 123b is blocked by the light blocking plates 150a and 150b so as not to be incident on the light receiving elements 126a and 126b. Therefore, the light incident from the openings 140a and 140b and detected by the light receiving elements 126a and 126b is limited to the light scattered by the straight part of the artery.

  As described above, in the fourth embodiment, the pulse wave information obtained from the curved portion of the artery is excluded by the light shielding plates 150a and 150b, so the pulse waves output from the light receiving elements 126a and 126b of the sensor units 120a and 120b. The resemblance of the waveforms of D.I. is improved, and inversion of the phase difference is avoided. In addition, the light receiving unit area is enlarged by arranging the light receiving units 123a and 123b in a direction perpendicular to the artery (in the X-axis direction). Thus, not only the output voltage output from the light receiving elements 126a and 126b is improved, but also the tolerance of the installation position with respect to the test site is improved.

Fifth Embodiment
FIG. 10A is a schematic view showing a light emitting element 124 a of the measuring apparatus 100 according to the fifth embodiment of the present invention. FIG. 10B is a schematic view showing a light receiving element 126a of the measuring apparatus 100 according to the fifth embodiment of the present invention.

  In the fifth embodiment of the present invention, each light emitting element of the sensor units 120a and 120b and at least one element of each light receiving element are inclined toward the other sensor unit. Preferably three patterns are conceivable. That is, in the first pattern, in the measuring apparatus 100, all of the two light emitting elements of the sensor unit 120a, one light receiving element, and the two light emitting elements of the sensor unit 120b and one light receiving element are on the other sensor unit side. It is configured to tilt. In the second pattern, the measuring apparatus 100 is configured such that only the two light emitting elements of the sensor unit 120a and the two light emitting elements of the sensor unit 120b are inclined toward the other sensor unit. In the third pattern, the measuring apparatus 100 is configured such that only one light receiving element of the sensor unit 120a and one light receiving element of the sensor unit 120b are inclined toward the other sensor unit.

  FIG. 10A shows, as an example, that the light emitting element 124a included in the light emitting unit 121a of the sensor unit 120a is inclined toward the sensor unit 120b. In FIG. 10A, it is assumed that the other sensor unit 120b is disposed to the right of the light emitting unit 121a. By inclining the light emitting element 124a, the optical axis of the light emitted from the light emitting element 124a is inclined toward the sensor unit 120b. Here, the optical axis is perpendicular to the emission surface of the light emitting element 124a. Similarly, FIG. 10B shows, as an example, that the light receiving element 126a included in the light receiving unit 123a of the sensor unit 120a is inclined toward the sensor unit 120b. Also in FIG. 10 (B), it demonstrates as that by which the other sensor part 120b is arrange | positioned on the right of the light-receiving part 123a. By inclining the light receiving element 126a, the optical axis of light incident on the light receiving element 126a is inclined toward the sensor unit 120b. Here, the optical axis is perpendicular to the incident surface of the light receiving element 126a. As in the fourth embodiment, also in the present embodiment, it is preferable that the light receiving element 126a be surrounded by a light shielding plate 150a having an opening 140a having a predetermined diameter. However, in the present embodiment, unlike the fourth embodiment, the light receiving element 126a is not disposed immediately below the opening 140a, and is disposed so as to be slightly closer to the light shielding plate 150a.

  As described above, it is preferable that the inclined portions be the respective light emitting / receiving elements included in the respective light emitting / receiving units, and it is preferable that the light emitting / receiving portions not be inclined. The respective light emitting and receiving units are disposed at predetermined intervals along a predetermined blood vessel of the subject in a state where the mounting unit 110 is mounted on the subject when acquiring the biological information of the subject. At this time, it is necessary that the emission surface from which the light of each light emitting portion is emitted and the entire incident surface where the light of each light receiving portion is incident are sufficiently in contact with the skin of the wrist surface which is the test site of the subject. There is. Therefore, it is preferable that each light emitting and receiving unit itself is not inclined to the other sensor unit side, but only each light emitting and receiving element included in the inside is inclined to the other sensor unit side.

  11A and 11B show the arrangement of the light emitting and receiving elements at the test site so that the arrangement of the light emitting and receiving elements with respect to the artery of the measurement apparatus 100 according to the present embodiment can be more easily understood. It is shown schematically. In both arteries, blood flows in the positive direction of the Y-axis, and thus the pulse wave also propagates in the same direction. In FIG. 11A, of the two light emitting units of each sensor unit, only the light emitting unit 121a and the light emitting unit 121b are shown as an example. Further, in FIG. 11B, only the light receiving units 123a and 123b of each sensor unit are shown, and illustration of two light emitting units of each sensor unit is omitted.

  Referring to FIG. 11A, the light emitting elements 124a and 124b included in the light emitting units 121a and 121b are inclined toward the other sensor units 120b and 120a, and the optical axes of the light emitting elements 124a and 124b are also closer to the other sensor units 120b and 120a Incline. By arranging in this way, the light emitted from the light emitting element 124a is unlikely to reach the curved portion of the upstream artery seen from the sensor unit 120a because the optical axis is inclined toward the sensor unit 120b. Similarly, the light emitted from the light emitting element 124b hardly reaches the curved portion of the downstream artery seen from the sensor unit 120b because the light axis is inclined toward the sensor unit 120a. That is, the region where light incident on the living body A2 is scattered can be limited to a certain extent to the straight part of the artery, and the pulse wave information from the curved part of the artery causing the reversal of the phase difference is included. It becomes difficult. Thus, the measuring apparatus 100 can measure the pulse wave with high accuracy.

  Referring to FIG. 11B, the light receiving elements 126a and 126b included in the light receiving units 123a and 123b are inclined toward the other sensor units 120b and 120a, respectively, and the optical axes of light incident thereon are also the other sensor unit 120b. , Incline to the side of 120a. With this arrangement, light scattered by the curved portion of the upstream artery seen from the sensor unit 120a is substantially eliminated, and the other scattered light enters the light receiving element 126a. Similarly, the light scattered by the curved portion of the downstream artery viewed from the sensor unit 120b is substantially eliminated, and the other scattered light enters the light receiving element 126b. That is, the scattered light detected by the light receiving elements 126a and 126b can be limited to a certain extent to the light scattered by the straight portion of the artery, and pulse waves from the curved portion of the artery cause the reversal of the phase difference. Information is almost eliminated. Thus, the measuring apparatus 100 can measure the pulse wave with high accuracy. Further, by shifting the arrangement of the light receiving elements 126a and 126b toward the light shielding plates 150a and 150b, light scattered from the curved portions of the arteries upstream and downstream of the sensor portions 120a and 120b is more reliably excluded, and the light shielding effect Improve further.

Sixth Embodiment
FIG. 12A is a schematic view showing the arrangement of the sensor unit 120a of the measuring apparatus 100 according to the sixth embodiment of the present invention. FIG. 12B schematically shows how the light emitting elements 124a and 125a and the light receiving element 126a of the measuring apparatus 100 according to the sixth embodiment of the present invention are disposed on the skin A1 on the wrist surface of the subject 12A is a cross-sectional view taken along the line A-A of FIG. In FIG. 12A, only the sensor unit 120a is shown, and the sensor unit 120b is not shown. The blood in the artery flows from the bottom to the top (the Y-axis positive direction), so the pulse wave also propagates in the same direction. With the sensor unit 120a disposed vertically (in the X-axis direction) along the artery, each light-emitting / receiving unit emits the light-emitting unit 121a, the light-receiving unit 123a, and the light-emitting unit so as to intersect the artery in the positive X-axis direction. It is arranged in order of 122a. In FIG. 12B, which is a cross-sectional view of FIG. 12A, the blood in the artery flows from the front to the back of the paper (in the positive Y-axis direction), and therefore the pulse wave also propagates in the same direction. .

  In the sixth embodiment of the present invention, in addition to the inclination to the other sensor unit side of each light emitting / receiving element described in the fifth embodiment, each light emitting element is also inclined in the artery direction. Also in the sixth embodiment, as in the other embodiments, the other sensor unit 120b is disposed at a predetermined interval in the positive Y-axis direction as viewed from the sensor unit 120a shown in FIG. Ru. Therefore, the inclination direction to the other sensor part of each light emitting / receiving element is the Y-axis direction of FIG. 12 (B). On the other hand, the inclination direction to the artery of each light emitting element is the X axis direction of FIG. 12 (B). That is, the optical axis of the light incident on the light receiving element 126a is inclined only in the positive direction of the Y axis, and the optical axis of the light emitted from the light emitting elements 124a and 125a is in the positive direction of the Y axis. As shown in), it also tilts in the X-axis direction. Since the light emitting units 121a and 122a are arranged symmetrically in the X axis direction with respect to the artery, the tilt directions of the optical axes of the light emitted from the light emitting elements 124a and 125a are directly opposite along the X axis. . That is, as an example in FIG. 12B, the optical axis of the light emitted from the light emitting element 124a is inclined in the positive direction of the X axis, while the optical axis of the light emitted from the light emitting element 125a is in the negative direction of the X axis Lean to

  With this configuration, in the present embodiment, the peak of the spatial intensity distribution of the light emitted from the light emitting elements 124a and 125a propagating through the inside of the living body A2 inclines in the direction of the artery. That is, most of the light emitted from the light emitting elements 124a and 125a reaches the artery, and the scattered light intensity of the light scattered by the artery increases. As a result, the intensity of the scattered light incident on the light receiving element 126a also increases, and the SN ratio of the signal output from the light receiving element 126a is improved. In other words, in the present embodiment, the measurement apparatus 100 can acquire a pulse wave waveform with relatively less noise compared to the signal intensity, as compared to the case where the optical axis of each light emitting element is not inclined in the arterial direction. .

  FIG. 13 shows a schematic view of a measurement system 1 including a measurement apparatus 100 embodying at least one of the first to sixth embodiments described above. Measurement system 1 includes server 200 and display unit 300 in addition to measurement apparatus 100. The server 200 aggregates the biological information acquired by the measuring device 100 and performs various information processing. The collection of biological information is performed by the measurement device 100 of each subject transmitting data to the server 200 via a wired or wireless communication network. The display unit 300 displays the result of the information processing performed by the server 200 based on the biological information acquired by the measuring device 100. That is, the display unit 300 displays information based on the biological information acquired by the measuring device 100.

  More specifically, the biological information acquired by the measuring device 100 is transmitted to the server 200 by the communication unit of the measuring device 100. When the server 200 receives the biological information transmitted from the measuring device 100, the control unit of the server 200 performs various information processing based on the received biological information of the subject. For example, the server 200 can store the biological information acquired by the measurement device 100 in the storage unit of the server 200 as time series data together with the acquisition time of the biological information. The control unit of the server 200 compares, for example, these stored data with the past data of the same subject already stored in the storage unit of the server 200 or the data of other subjects. Based on the results, the system generates advice that is optimal for the subject. The communication unit of the server 200 transmits the acquired time-series data of the subject and the generated advice to the display unit 300. The display unit 300 displays the received data and advice on the screen. In addition, a functional unit having the same function as the storage unit and the control unit of the server 200 may be included in the measuring apparatus 100 or the display unit 300, and in that case, the measuring system 1 may not necessarily include the server 200.

  It will be apparent to those skilled in the art that the present invention can be realized in other predetermined forms other than the above-described embodiment without departing from the spirit or essential characteristics thereof. Thus, the foregoing description is illustrative and not restrictive. The scope of the invention is defined by the appended claims rather than by the foregoing description. Some of the changes that come within the scope of the equivalents are intended to be embraced therein.

100 measuring device 110 mounting portion 111 back surface 112 front surface 113a, 113b, 140a, 140b opening portion 114, 115 band portion 120a, 120b sensor portion 121a, 121b, 122a, 122b light emitting portion 123a, 123b light receiving portion 124a, 124b, 125a, 125b Light emitting element 126a, 126b Light receiving element 134a, 134b Lens part 150a, 150b Light shielding plate 200 Server 300 Display part 1 Measurement system A1 Skin A2 Internal body R1, R2, R3, R4, R1, B1, B2 Area V1 ulnar artery V2 radial artery L1, L2 length

Claims (8)

An attachment unit attached to the subject;
And a first sensor unit supported by the mounting unit and having a light emitting unit and a light receiving unit, respectively.
When the first sensor unit and the second sensor unit acquire biological information of the subject, the first sensor unit and the second sensor unit are configured to receive the test subject while the mounting unit is attached to the subject. are arranged at intervals of less than 35mm along the blood vessel,
The distance between the light emitting unit in the first sensor unit and the light emitting unit in the second sensor unit is the distance between the light receiving unit in the first sensor unit and the light receiving unit in the second sensor unit. Shorter than
measuring device. The light emitting element of the light emitting unit in the first sensor unit and the light emitting element of the light emitting unit in the second sensor unit are disposed at an interval of 35 mm or less along a predetermined blood vessel of the subject.
The measuring device according to claim 1. The light emitting units are disposed on both sides of the light receiving unit along a direction perpendicular to a predetermined blood vessel of the subject.
The measuring device according to claim 1 or 2 . The light receiving unit includes an opening having a predetermined diameter,
The measuring device according to any one of claims 1 to 3 . The attachment unit is a band attached to a wrist of the subject.
The measuring device according to any one of claims 1 to 4 . The biological information is a pulse wave,
The measuring device according to any one of claims 1 to 5 . A controller configured to calculate a pulse wave velocity based on the acquired pulse wave;
The measuring device according to claim 6 . A measuring device according to any one of claims 1 to 7 ;
A display unit configured to display information based on biological information acquired by the measurement device;
Measurement system.

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