JP2013017612A - Probe for measuring living body - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a prove for measuring a living body capable of reducing the effect of disturbance while reducing the effect of optical mixing on measuring spectrums.SOLUTION: An irradiation fiber 35 and a light receiving fiber 34 are attached to a probe body 30 so as to form: vertical parts 35b and 34b arranged so that an irradiation surface 35a of the irradiation fiber 35 and a light receiving surface 34a of the light receiving fiber 34 abut on a skin surface 43a of the living body substantially in parallel; parallel parts 35c and 34c arranged so as to extend to the skin surface 43a of the living body substantially in parallel; and bent parts 35d and 34d continuously arranging the vertical parts 35b and 34b and the parallel parts 35c and 34c. The irradiation fiber 35 and the light receiving fiber 34 are optically isolated at least at the bent parts 35d and 34d.

Description

  The present invention irradiates a living skin tissue with near infrared light, receives diffuse reflection or transmitted light from the skin tissue, measures a signal from the obtained skin tissue, and determines biological components and properties. The present invention relates to biological component sensing technology that performs qualitative and quantitative analysis, and in particular, relates to a biometric probe that measures skin tissue spectrum in a blood glucose monitoring device that measures blood glucose level of a living body using a change in glucose concentration in skin tissue as a substitute characteristic. .

  Regarding blood glucose level monitoring or blood glucose level monitoring, there was a higher need for blood glucose level management in diabetics than before, but in recent years, the mortality rate has been reduced by managing blood glucose levels within an appropriate range in the intensive care unit (ICU). Medical effects such as a decrease in the incidence of complications have been medically verified, and their application fields are expanding.

  The blood glucose level is measured by using an invasive method (enzyme electrode method: GOD method, GDH method, enzyme colorimetric method: HX method, etc.) that uses the collected blood and quantifies it using an enzyme reaction such as glucose oxidase. The blood pressure level can be roughly classified into non-invasive techniques for estimating blood glucose levels based on some information obtained from a living body without performing an operation such as blood collection to damage the body.

  As measuring devices, not only large-scale devices for clinical tests but also portable blood glucose meters using invasive techniques are widely used for self-blood glucose measurement (SMBG) in diabetic patients. Puncture with a lancet and collect about 1 drop of blood to measure blood glucose level. The reliability of blood glucose measurement by such blood collection is high, and the measurement error is 15% or less in most models that are commercially available even for portable blood glucose meters used for self-blood glucose measurement.

  Various methods have been proposed for non-invasive estimation of blood glucose levels, but there are still problems with estimation accuracy and reliability. At this point, Japan's regulatory approval and US FDA approval There is no product obtained. Among the proposed methods, the method using near infrared light is the most known. The method of non-invasively measuring blood glucose levels with near-infrared light qualifies the living tissue from signals and spectra obtained by irradiating the living tissue with near-infrared light and measuring the light diffusely reflected inside the living tissue.・ Perform quantitative analysis.

  As an example, a technique for measuring a blood glucose level from a near-infrared spectrum obtained from a living tissue as disclosed in Patent Document 1 has been proposed. FIGS. 13A and 13B show a non-invasive optical blood glucose level measuring system disclosed in Patent Document 1, in which near-infrared light emitted from the halogen lamp 1 is a heat shielding plate 2. The light enters the living tissue 6 through the pinhole 3, the lens 4, and the optical fiber bundle 5.

  One end of the measurement optical fiber 7 and one end of the reference optical fiber 8 are connected to the optical fiber bundle 5. One end of the measurement optical fiber 7 is connected to the skin tissue measurement probe 9, and the other end of the reference optical fiber 8 is connected to the reference probe 10. Furthermore, the skin tissue measurement probe 9 and the reference probe 10 are connected to the measurement-side emitter 11 and the reference-side emitter 12 via the optical fiber 7, respectively.

  When near-infrared spectrum measurement is performed by bringing the tip of the skin tissue measurement probe 9 into contact with the surface of a living tissue 6 such as the forearm of a human body, near-infrared light incident on the optical fiber bundle 5 from the halogen lamp 1 is The light is transmitted through the optical fiber bundle 5 and irradiated from the tip of the skin tissue measurement probe 9 as shown in FIG. 13 (B) onto the surface of the living tissue 6 through twelve light emitting fibers 20 arranged concentrically. The

  The measurement light applied to the living tissue 6 is diffusely reflected in the living tissue 6, and then a part of the diffuse reflected light is received by the light receiving fiber 19 arranged at the center of the tip of the skin tissue measuring probe 9. The received light is emitted from the measurement-side emitting body 11 through the light receiving fiber 19. The light emitted from the measurement-side emitting body 11 enters the diffraction grating 14 through the lens 13, and after being split, is detected by the light receiving element 15.

  The optical signal detected by the light receiving element 15 is AD converted by the A / D converter 16 and then input to the arithmetic device 17 such as a personal computer. The blood glucose level is calculated by analyzing the spectrum data. In the reference measurement, light reflected from a reference plate 18 such as a ceramic plate is measured, and this is used as reference light. That is, near-infrared light incident on the optical fiber bundle 5 from the halogen lamp 1 is irradiated to the surface of the reference plate 18 from the tip of the reference probe 10 through the reference optical fiber 8.

  The reflected light of the light irradiated on the reference plate is emitted from the refanless emitter 12 through the light receiving fiber 19 disposed at the center of the tip of the reference probe 10. A shutter 22 is disposed between the measurement-side emitting body 11 and the lens 13 and between the refanless-side emitting body 12 and the lens 13. One of the lights from the side emitter 12 is selectively passed.

  The end surfaces of the skin tissue measurement probe 9 and the reference probe 10 are twelve light emitting fibers 20 arranged on a circle as shown in FIG. 13B and one light receiving fiber 19 arranged at the center thereof. It is configured. The center distance L between the light emitting fiber 20 and the light receiving fiber 19 is 0.65 mm. The end faces of the measurement-side emitter 11 and the reference-side emitter 12 are not shown, but the exit fiber is arranged at the center.

  In this apparatus, the spectrum of the dermis part of the skin tissue having a layered structure of epidermis, dermis, and subcutaneous tissue from the skin surface is selectively measured, so that the center distance L = 0 as shown in FIG. The light receiving fiber 19 is disposed at a distance of 65 mm, and the skin tissue measuring probe 9 is used as an incident point and a detection point. When the skin tissue measurement probe 9 is brought into contact with the skin surface and spectrum measurement is performed, the near-infrared light irradiated from the incident optical fiber is diffusely reflected in the skin tissue, and a part of the incident light is detected light. It reaches the fiber, and its light propagation path is called a banana shape and propagates around the dermis. Therefore, the SN ratio of the light absorption signal is improved, and the biological component concentration can be accurately measured.

  Moreover, as a conventional skin tissue measurement probe, there is a structure disclosed in Patent Document 2, for example. This probe for measuring skin tissue measures the optical signal of the skin tissue by fixing the probe which is the tip of the optical fiber bundle to the skin surface and irradiating the skin with near infrared light from the probe. is there. A support fixing means for supporting and fixing an arbitrary part of the optical fiber bundle is provided at a position within 10 cm from the probe, and the optical fiber bundle arranged between the probe and the support fixing means can be bent freely.

  Moreover, as a conventional skin tissue measurement probe, there is a structure disclosed in Patent Document 3, for example. The probe for skin tissue measurement includes a probe body having a skin contact surface that contacts the skin surface, and a light receiving / emitting section having a light emitting surface and a light receiving surface connected to a light emitting source and a light receiving processing section via a communication cable, respectively. And. The light emitting / receiving unit is integrally extended from one side surface of the probe main body, and the light emitting surface and the light receiving surface of the light receiving / emitting unit are parallel to the skin contact surface and deviated by 1 to 3 mm from the skin contact surface. It is a structure that has been placed.

JP 2006-087913 A JP 2011-064022 A JP 2003-079589 A

  Non-invasive and non-invasive methods for estimating blood glucose levels regardless of blood collection are highly needed because they can measure blood glucose levels without placing a burden on patients. Various measurement methods have been proposed. However, there are still problems in estimation accuracy and reliability, and at this point, there are no products that have obtained Japanese regulatory approval or US FDA approval.

  In addition, in non-invasive blood glucose level measurement using near-infrared light targeted by the present invention, there are still problems in estimation accuracy and reliability, but it is under measurement as one factor that reduces estimation accuracy and reliability. There is a change in the contact state between the skin tissue measurement probe 9 and the skin due to body movement. In order to reduce changes in the contact state between the skin tissue measurement probe 9 and the skin due to body movement, the skin tissue measurement probe 9 and the skin contact with each other even if the body is moved. It is necessary to take any one of the structures that do not easily change the state.

  However, the near-infrared wavelength optical fiber suitable for non-invasive blood glucose measurement as in Patent Document 1 needs to use a glass fiber having a diameter of about 200 μm, and therefore has a relatively high rigidity and is difficult to bend. Has characteristics. Therefore, in the vicinity of the skin tissue measurement probe 9, the optical fiber bundle 5 tends to be elongated in a direction perpendicular to the skin surface so that the optical fiber is not bent as much as possible. It is easy to be transmitted to the tip of the bundle 5 and easily affected.

  Therefore, in Patent Document 2, a support and fixing means for supporting and fixing an arbitrary portion of the optical fiber bundle is provided at a position within 10 cm from the probe, so that a force due to body movement or the like is not easily transmitted to the distal end portion of the optical fiber bundle 5. doing.

  However, in the structure of Patent Document 2, the optical fiber bundle is installed so as to protrude from the measurement probe in a direction perpendicular to the measurement skin, and the optical fiber bundle is bent in an inverted U shape. An arbitrary part of the bundle is supported by the support fixing means.

  For this reason, when an object or a person comes into contact with the inverted U-shaped portion of the optical fiber bundle, a disturbance occurs and the measurement conditions become unstable, which may affect the measurement spectrum.

  As a solution to this, a method has been proposed in which a fiber is bent in a measurement probe and the fiber is pulled out in a direction parallel to the measurement skin, as in Patent Document 3.

  By the way, in order not to be influenced by force due to body movement or the like, it is preferable that the distance between the measurement skin and the measurement skin of the fiber drawn in the parallel direction is small.

  However, as described above, a near-infrared wavelength optical fiber suitable for non-invasive blood glucose measurement has a relatively strong rigidity and is difficult to bend. Therefore, if the optical fiber is bent with a small radius of curvature of about several millimeters, the optical fiber may be broken.

  Furthermore, in the structure of Patent Document 3, the light emitting surface and the light receiving surface of the light receiving and emitting unit are deviated by 1 to 3 mm in parallel to the skin contact surface and in the direction away from the skin contact surface.

  As described above, the structure of Patent Document 3 has a problem that the distance between the fiber to be measured and the fiber to be measured in the direction parallel to the measurement skin cannot be reduced so much that it is difficult to reduce the influence of disturbance.

  Further, when the fiber is bent, the light leaked from the bent portion to the outside of the fiber enters the inside from the bent portion of the other fiber, and the light is mixed, which may affect the measurement spectrum.

  Therefore, an object of the present invention is to obtain a biometric probe that can further reduce the influence of disturbance while further reducing the influence of light mixing on the measurement spectrum.

  The present invention is a biometric probe having an irradiation fiber that irradiates skin tissue of a living body with near-infrared light, and a light-receiving fiber that receives diffuse reflection or transmitted light from the skin tissue. The light receiving fiber is arranged so that the irradiation surface of the irradiation fiber and the light receiving surface of the light receiving fiber are in contact with the skin surface of the living body substantially parallel to each other, and the light receiving fiber extends substantially parallel to the skin surface of the living body. Attached to the probe main body so that a parallel portion to be formed and a bent portion connecting the vertical portion and the parallel portion are formed, and the irradiation fiber and the light receiving fiber are optically at least in the bent portion. It is characterized by being isolated.

  According to the present invention, the irradiation fiber and the light receiving fiber are provided on a vertical portion arranged so that the irradiation surface of the irradiation fiber and the light receiving surface of the light receiving fiber are in contact with the skin surface of the living body, and the skin surface of the living body. It is attached to the probe main body so as to form a parallel part arranged so as to extend substantially in parallel and a bent part connecting the vertical part and the parallel part. That is, by bending the irradiation fiber and the light receiving fiber, the irradiation fiber and the light receiving fiber are drawn out in a direction substantially parallel to the measurement skin surface. Therefore, compared with the case where the irradiation fiber and the light receiving fiber protrude in the direction perpendicular to the measurement skin, it is possible to make the device less susceptible to the influence of contact with an object or a person.

  Furthermore, according to the present invention, at least the bent portions of the irradiation fiber and the light receiving fiber are optically isolated. Therefore, the influence on the measurement spectrum due to the mixing of the light of the irradiation fiber and the light receiving fiber can be further reduced.

FIG. 1 is a diagram schematically showing a skin tissue measured with a probe for skin tissue measurement. FIG. 2 is a view showing a living body part to which the probe for skin tissue measurement of the first embodiment is attached. 3A and 3B are diagrams illustrating the skin tissue measurement probe according to the first embodiment, in which FIG. 3A is a cross-sectional view, and FIG. 3B is an enlarged view of a portion A in FIG. FIG. 4 is a cross-sectional view showing a modification of the optical fiber of the first embodiment. FIG. 5 is a diagram for explaining the stress generation state of the skin tissue measurement probe of the first embodiment and the conventional skin tissue measurement probe. FIG. 5 (A) shows the stress generation state of the conventional skin tissue measurement probe. The figure shown, (B) is a figure which shows the stress generation state of the probe for skin tissue measurement of 1st Embodiment. 6A and 6B are diagrams schematically showing the optical fiber of the first embodiment and an optical fiber of a modification thereof, wherein FIG. 6A is a diagram showing the optical fiber of the first embodiment, and FIG. It is a figure which shows an optical fiber. 7A and 7B are diagrams showing a skin tissue measurement probe according to the second embodiment, in which FIG. 7A is a sectional view and FIG. 7B is a perspective view. FIG. 8 is a cross-sectional view showing the skin tissue measurement probe of the third embodiment. FIG. 9 is a perspective view showing the skin tissue measurement probe of the fourth embodiment. FIG. 10 is a perspective view showing a skin tissue measurement probe of a first modification of the fourth embodiment. 11A and 11B are diagrams showing a skin tissue measurement probe according to a second modification of the fourth embodiment, in which FIG. 11A is a perspective view showing a state in which the tip of the optical fiber is detached, and FIG. It is a perspective view which shows the state which is going to fix the detached optical fiber to a probe main body. FIG. 12 is a perspective view showing a skin tissue measurement probe of a third modification of the fourth embodiment. FIGS. 13A and 13B are diagrams showing a conventional skin tissue measuring apparatus, in which FIG. 13A is an overall configuration diagram, and FIG. 13B is an enlarged view of a tip portion of an optical fiber bundle.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. Note that similar components are included in the following embodiments. Therefore, in the following, common reference numerals are given to those similar components, and redundant description is omitted.

(First embodiment)
In order to non-invasively estimate the blood sugar level, it can be estimated by measuring the optical signal (diffuse reflection spectrum) of the skin tissue by irradiating the skin with near infrared light having a wavelength of 1300 nm to 2500 nm. As shown in FIG. 1, the living skin tissue is roughly composed of three layers of an epidermal tissue S1, a dermal tissue S2, and a subcutaneous tissue S3.

  The epidermal tissue S1 is a tissue including the stratum corneum, and the capillaries are not so developed in the tissue. The subcutaneous tissue S3 is mainly composed of adipose tissue. Therefore, it is considered that the correlation between the concentration of water-soluble biological components contained in the two tissues, in particular, the glucose concentration and the blood glucose concentration (blood glucose level) is low.

  On the other hand, for the dermal tissue S2, the concentration of biological components in the tissue, particularly interstitial fluid (especially interstitial fluid ( It is considered that the glucose concentration in ISF (Interstitial Fluid) changes following the blood glucose level. Therefore, if spectrum measurement targeting the dermis tissue S2 is performed, it is possible to measure a spectrum signal that correlates with biological component concentrations, particularly blood glucose level fluctuations.

  When using near-infrared light having a wavelength of 1300 nm to 2500 nm, a near-infrared spectrum skin tissue measurement probe having a light-emitting part 100 and a light-receiving part 101 separated from each other with a center-to-center distance L = 0.65 mm is applied to the skin. When the near-infrared spectrum is measured by contact, the near-infrared light Hv irradiated from the light emitting unit 100 is irradiated onto the skin tissue from the irradiation surface, diffusely reflected in the skin tissue, and a part thereof is reflected on the light receiving unit 101. To reach. In this case, the light propagation path propagates in the skin tissue with the dermis tissue S2 as the center, and takes a shape called a banana shape. This enables selective measurement in the depth direction of the skin tissue, and accurate measurement is possible. it can.

  Next, the skin tissue measurement probe (biological measurement probe) according to this embodiment will be described.

  A skin tissue measurement probe (biological measurement probe) 30A according to this embodiment shown in FIG. 3 irradiates near-infrared light Hv to the skin tissue of the living body, and diffuse reflection or transmitted light from the skin tissue. An optical fiber 33 having a light receiving fiber 34 for receiving light is provided.

  As the light receiving fiber 34 and the irradiation fiber 35, those having a diameter of 50 μm or more and less than 300 μm are preferably used. In the present embodiment, a light receiving fiber 34 and an irradiation fiber 35 having a diameter of 200 μm are used. Thus, by using the light receiving fiber 34 and the irradiation fiber 35 having a diameter of 200 μm, the fiber can be bent easily while minimizing optical loss during measurement.

  In this embodiment, the optical fiber 33 is formed by arranging a plurality of irradiation fibers 35 or light receiving fibers 34 on concentric circles of the light receiving fibers 34 or irradiation fibers 35.

  Specifically, as in FIG. 13B, the optical fiber 33 is composed of twelve irradiation fibers 35 arranged concentrically and one light receiving fiber 34 arranged in the center thereof. Yes. Note that the center-to-center distance L between the irradiation fiber 35 and the light receiving fiber 34 is 0.65 mm, as in FIG.

  The skin tissue measurement probe 30 </ b> A includes a probe body 30 that fixes and supports the irradiation fiber 35 and the light receiving fiber 34.

  In the present embodiment, the probe main body 30 includes a bottomed cylindrical housing 31 in which a space 31 a is formed, and a lid portion 32 that is attached so as to close the space 31 a of the housing 31.

  The housing 31 includes a substantially cylindrical side wall portion 31b, a substantially disc-shaped bottom wall portion 31c, and a flange portion 31d that extends substantially in parallel from the upper portion of the side wall portion 31b and to which the lid portion 32 is attached. ing.

  At the substantially central portion of the bottom wall portion 31c, the tips of the irradiation fiber 35 and the light receiving fiber 34 (tip portions where the irradiation surface 35a and the light receiving surface 34a are formed: vertical portions 34b and 35b described later) are directed from the inside to the outside. An insertion hole 31e that is fixed in the inserted state is formed.

  In this embodiment, the tip side of the vertical portions 34b and 35b (in the vicinity of the irradiation surface 35a of the irradiation fiber 35 and the light reception surface 34a of the light receiving fiber 34) is fixed to the housing 31 (probe body 30) using the adhesive 50. Yes.

  At this time, the distal ends of the vertical portions 34b and 35b are fixed to the housing 31 (probe body 30) with the irradiation surface 35a and the light receiving surface 34a slightly protruding from the bottom wall portion 31c.

  Further, a notch 31f is formed on the outer peripheral portion of the bottom wall portion 31c, and the fitting protrusion 30a of the probe main body 30 is formed by forming the notch 31f. Thus, by forming the fitting convex part 30a of the probe main body 30, the fitting convex part 30a is inserted into the fitting hole 36a of the mounting auxiliary member 36 described later, and the probe main body 30 is attached to the mounting auxiliary member 36. I can do it.

  Further, the flange portion 31d is formed with a groove portion 31g that opens to the inside and the outside, and the optical fiber 33 (the irradiation fiber 35 and the light receiving fiber 34) can be accommodated in the groove portion 31g.

  In the present embodiment, as shown in FIG. 3A, the housing 31 and the lid portion 32 in a state where the optical fiber 33 (the irradiation fiber 35 and the light receiving fiber 34) is accommodated in the groove portion 31g by the adhesive 50. It is fixed to the (probe body 30).

  The groove portion may be provided in the lid portion 32, or may be provided in both the flange portion 31d and the lid portion 32.

  In this way, by fixing the optical fiber 33 (the irradiation fiber 35 and the light receiving fiber 34) in a state of being accommodated in the groove 31f, the optical fiber 33 and the light receiving fiber 34 extend substantially parallel to the skin surface 43a of the living body. Parallel portions 35c and 34c arranged so as to exist are formed.

  The distal ends (vertical portions 35b, 34b) of the irradiation fiber 35 and the light receiving fiber 34 are fixed to the probe body 30 so as to be substantially perpendicular to the skin surface 43a, and the distal ends of the irradiation fiber 35 and the light receiving fiber 34 are fixed. Bending portions 35d and 34d connecting the vertical portions 35b and 34b and the parallel portions 35c and 34c by bending the opposite side to the probe main body 30 so that the parallel portions 35c and 34c are formed. Is to be formed.

  That is, by bending the irradiation fiber 35 and the light receiving fiber 34, the irradiation fiber 35 and the light receiving fiber 34 are pulled out in a direction substantially parallel to the measurement skin surface 43a.

  In the present embodiment, the height H of the probe main body 30 is about 8 mm, and the curvature radius of the bent portion is about 4 mm to 6 mm. The radius of curvature is preferably set to be as small as possible within a range where the irradiation fiber 35 and the light receiving fiber 34 are not damaged.

  And in this embodiment, as above-mentioned, the irradiation fiber 35 and the light reception fiber 34 are the vicinity of the irradiation surface 35a of the said irradiation fiber 35, the light reception surface 34a of the light reception fiber 34, and the bending part 35b of the parallel parts 35c and 34c, The probe body 30 is fixed at only two points in the vicinity of 34b.

  Further, the bent portions 35 d and 34 d of the irradiation fiber 35 and the light receiving fiber 34 are in a free state with respect to the probe main body 30.

  That is, in this embodiment, the space 31a in which the bent portions 35d and 34d are formed is not filled with resin or the like.

  In FIG. 3, for the sake of convenience, the irradiation fiber 35 and the light receiving fiber 34 are illustrated as being scattered on the tip side, but the tip side of the irradiation fiber 35 and the light receiving fiber 34 is also shown in FIG. Alternatively, it may be bundled. In this manner, if the distal ends of the irradiation fiber 35 and the light receiving fiber 34 are also bundled, it is easy to fix the housing 31 (the probe body 30), and the irradiation fiber 35 and the light receiving fiber 34 are relatively displaced. Can be suppressed.

  Furthermore, as described above, in this embodiment, the probe 30A for skin tissue measurement has the probe main body 30 fixedly supported by the irradiation fiber 35 and the light receiving fiber 34, thereby attaching the irradiation surface 35a of the irradiation fiber 35 and the light receiving fiber 34. Is provided with an attachment assisting member 36 for attaching and holding the light receiving surface 34a to the skin measurement site.

  The attachment auxiliary member 36 is configured to attach and hold the irradiation surface 35a of the irradiation fiber 35 and the light receiving surface 34a of the light receiving fiber 34 on the skin measurement site, and has a donut shape. The attachment assisting member 36 is formed of a flexible member that is in close contact with the skin around the measurement site and keeps the light receiving surface 34a and the irradiation surface 35a in contact with the skin surface 43a substantially in parallel. For example, it is made of a material such as polyurethane or silicon rubber which is rich in flexibility.

  In this way, by using the mounting assisting member 36 as a flexible mounting member, even when a living body part that is a soft tissue having a curved surface is measured, the mounting assisting member is in close contact with the curved surface due to its flexible material characteristics. 36 can be pasted. As a result, the contact state of the light receiving surface 34a and the irradiation surface 35a with the skin surface 43a can be stabilized.

  The skin tissue measurement probe 30A is attached and fixed to the skin surface 43a of the arm 43 with, for example, a double-sided tape (not shown) (see FIG. 2).

  Here, in this embodiment, the irradiation fiber 35 and the light receiving fiber 34 are optically isolated at least at the bent portions 35d and 34d.

  Specifically, the light receiving fiber 34 that is at least one of the irradiation fiber 35 and the light receiving fiber 34 is covered with a light shielding tube 37 so as to be optically isolated. It is also possible to optically isolate the fiber surface by coating or the like. Moreover, as shown in FIG. 4, it is also possible to optically isolate by filling the absorber 37a between fibers. In FIG. 4, with one light receiving fiber 34 disposed at the center and twelve irradiation fibers 35 disposed concentrically, the space 31a is filled with a light absorber 37a, thereby absorbing light between the respective fibers. The one filled with the body 37a is shown.

  As described above, in the present embodiment, the irradiation fiber 35 and the light receiving fiber 35 are arranged so that the irradiation surface 35a of the irradiation fiber 35 and the light receiving surface 34a of the light receiving fiber 34 are in contact with the skin surface 43a of the living body substantially in parallel. The arranged vertical parts 35b and 34b, the parallel parts 35c and 34c arranged so as to extend substantially parallel to the skin surface 43a of the living body, and the vertical parts 35b and 34b and the parallel parts 35c and 34c are connected in series. The bent portions 35d and 34d are attached to the probe main body 30 so as to be formed. That is, by bending the irradiation fiber 35 and the light receiving fiber 34, the irradiation fiber 35 and the light receiving fiber 34 are pulled out in a direction substantially parallel to the measurement skin surface 43a. Therefore, compared with the case where the irradiation fiber 35 and the light receiving fiber 34 protrude in the direction perpendicular to the skin for measurement, it is possible to make it less likely to be affected by contact with an object or a person.

  That is, it is possible to further reduce the influence of disturbances such as contact and body movement of an object or a person.

  Further, according to the present embodiment, at least the bent portions 35d and 34d of the irradiation fiber 35 and the light receiving fiber 34 are optically isolated. Therefore, the influence on the measurement spectrum due to the mixing of the light of the irradiation fiber 35 and the light receiving fiber 34 can be further reduced.

  Further, according to the present embodiment, the vicinity of the skin contact portion (near the irradiation surface 35a of the irradiation fiber 35 and the light reception surface 34a of the light receiving fiber 34) and the vicinity of the lead portion from the probe body 30 (the bent portions of the parallel portions 35c and 34c). The irradiation fiber 35 and the light receiving fiber 34 are fixed to the probe main body 30 at only two points (near 35b and 34b). As a result, the number of places where the irradiation fiber 35 and the light receiving fiber 34 are fixed to the probe main body 30 is reduced, so that the processing is facilitated and the manufacturing can be simplified.

  Further, according to the present embodiment, the bent portions 35 d and 34 d of the irradiation fiber 35 and the light receiving fiber 34 are in a free state with respect to the probe main body 30.

  That is, in this embodiment, the space 31a in which the bent portions 35d and 34d are formed is not filled with resin or the like.

  By the way, when forming the bent portions 35d and 34d, it is desirable to reduce the internal force of the optical fiber as much as possible and to make the generated maximum principal stress and the like sufficiently smaller than the breaking threshold of the optical fiber. In particular, it is required to design the internal force such as residual stress to be small.

  For example, when the periphery of the optical fiber is completely fixed with resin 200 or the like as in the prior art, as shown in FIG. 5 (A), the internal stress F generated when the bent portions 35d and 34d return to the original straight state. , M, and P, residual stresses t and w due to the resin 200 are generated.

  However, in this embodiment, since the bent portions 35d and 34d of the irradiation fiber 35 and the light receiving fiber 34 are in a free state with respect to the probe main body 30, as shown in FIG. Residual stresses t and w are not generated. As a result, compared to the conventional case where the periphery of the optical fiber is completely fixed with resin or the like, the internal force generated in each part of the optical fiber, such as residual stress during manufacturing, can be reduced, and the curvature of the bent portions 35d and 34d can be reduced. The radius can be made smaller.

  Further, since the internal force generated in each part of the optical fiber is reduced, the manufacture of the fiber bending portion is simplified, and the internal force generated in the optical fiber 33 can be further reduced when the same radius of curvature is used. Therefore, the possibility of deterioration (breakage etc.) of the optical fiber 33 can be further reduced.

  Further, according to the present embodiment, since the optical fiber 33 is formed by arranging a plurality of the irradiation fibers 35 or the light receiving fibers 34 on the concentric circles of the light receiving fibers 34 or the irradiation fibers 35, the probe for skin tissue measurement The skin characteristics with which 30A is brought into contact can be averaged, and baseline fluctuations and spectral shape changes can be reduced.

  Next, a modification of this embodiment will be described.

  In this modification, as shown in FIG. 6 (B), a plurality of fibers (irradiation fibers 35) arranged concentrically among the light receiving fiber 34 and the irradiation fiber 35 have a bent portion 35d spirally twisted. Yes.

  Specifically, the irradiation fiber 35 is twisted by 180 degrees (one round) or more in a spiral manner at the bent portion 35d. The twist angle of the irradiation fiber 35 is preferably set to be 180 × n degrees (n = 1, 2, 3...).

  Also according to the above modification, the same operations and effects as those of the first embodiment can be obtained.

  Moreover, according to this modification, the bending part 35d of the irradiation fiber 35 is twisted helically.

  By the way, in the said 1st Embodiment, as shown to FIG. 6 (A), the bending part 35d of the irradiation fiber 35 is not twisted. In this way, if the irradiation fiber 35 is bent without being twisted, the curvature radius of the bent portion 35d differs between the inner irradiation fiber 35 and the outer irradiation fiber 35. Therefore, the optical characteristics vary between the inner side and the outer side of the optical fiber 33. Specifically, the outer irradiation fiber 35 has a large radius of curvature, and light attenuation is reduced. In the inner irradiation fiber 35, the radius of curvature is small, and the attenuation of light is increased.

  However, in this modification, the bent portion 35d of the irradiation fiber 35 is twisted in a spiral shape. Therefore, the radius of curvature difference between the irradiation fibers 35 arranged inside and outside before twisting can be made as small as possible. In particular, if the torsion angle is set to 180 degrees (one round) or more, more preferably 180 × n degrees (n = 1, 2, 3,...), The bending portion 35d of the irradiation fiber 35 is bent. The average curvature radius can be made substantially the same, and the light attenuation can be made almost the same.

  As described above, according to the present invention, variation in the radius of curvature of the bent portion 35d of the irradiation fiber 35 can be reduced, and variations in optical characteristics between the irradiation fibers 35 can be reduced.

(Second Embodiment)
The skin tissue measurement probe (biological measurement probe) 30A according to the present embodiment has basically the same configuration as that of the first embodiment. That is, the skin tissue measurement probe (biological measurement probe) 30A includes an irradiation fiber 35 that irradiates the skin tissue of the living body with near-infrared light Hv, and a light receiving fiber 34 that receives diffuse reflection or transmitted light from the skin tissue. Are provided.

  In this embodiment, the optical fiber 33 is formed by arranging a plurality of irradiation fibers 35 or light receiving fibers 34 on concentric circles of the light receiving fibers 34 or irradiation fibers 35.

  The skin tissue measurement probe 30 </ b> A includes a probe body 30 that fixes and supports the irradiation fiber 35 and the light receiving fiber 34.

  The probe body 30 includes a bottomed cylindrical housing 31 in which a space 31 a is formed, and a lid portion 32 that is attached so as to close the space 31 a of the housing 31.

  The housing 31 includes a substantially cylindrical side wall portion 31b, a substantially disc-shaped bottom wall portion 31c, and a flange portion 31d that extends substantially in parallel from the upper portion of the side wall portion 31b and to which the lid portion 32 is attached. ing.

  Then, at the substantially central portion of the bottom wall portion 31c, the tips of the irradiation fiber 35 and the light receiving fiber 34 (tip portions where the irradiation surface 35a and the light receiving surface 34a are formed: vertical portions 34b and 35b) are inserted from the inside to the outside. An insertion hole 31e is formed to be fixed in the state.

  Also in this embodiment, the tip side of the vertical portions 34b and 35b (in the vicinity of the irradiation surface 35a of the irradiation fiber 35 and the light reception surface 34a of the light receiving fiber 34) is fixed to the housing 31 (probe body 30) using the adhesive 50. ing.

  Further, the flange portion 31d is formed with a groove portion 31g that opens to the inside and the outside, and the optical fiber 33 (the irradiation fiber 35 and the light receiving fiber 34) can be accommodated in the groove portion 31g.

  Here, the skin tissue measurement probe 30A according to the present embodiment is mainly different from the first embodiment in that the irradiation fiber 35 and the light receiving fiber 34 are irradiated with the irradiation fiber 35 as shown in FIG. The probe is fixed to the probe body 30 at only one point in the vicinity of the surface 35a and the light receiving surface 34a of the light receiving fiber 34. 7A illustrates a case where the light receiving fiber 34 is covered with a light shielding tube 37, and FIG. 7B illustrates a case where a light absorber is filled between the fibers.

  Specifically, a guide wall portion 32 a having a shape corresponding to the outside of the bent portions 35 d and 34 d of the irradiation fiber 35 and the light receiving fiber 34 is formed on the lid portion 32. Then, while guiding the irradiation fiber 35 and the light receiving fiber 34 with the distal ends of the vertical portions 34b and 35b fixed by the guide wall portion 32a, the lid portion 32 is accommodated in the groove portion 31g of the flange portion 31d. By bending the lid, the bent portions 35d and 34d are formed. At this time, the vicinity of the bent portions 35b and 34b of the parallel portions 35c and 34c is accommodated in the groove portion 31g, so that the movement is restricted, but as in the first embodiment, the probe It is not fixed to the main body 30.

  As described above, in this embodiment, the irradiation fiber 35 and the light receiving fiber 34 fix the vicinity of the skin contact portion to the probe main body 30, and the internal structure (the lid 32, the guide wall portion 32a, and the space 31a) of the upper portion of the probe main body 30. The bent portions 35d and 34d are formed by using them.

  In addition, the shape of the guide wall portion may be a cylindrical shape, or the guide wall portion may be provided on the bottom wall 31c.

  Also according to this embodiment described above, the same operations and effects as those of the first embodiment can be achieved.

  Also. According to this embodiment, the irradiation fiber 35 and the light receiving fiber 34 are fixed to the probe main body 30 at only one point in the vicinity of the irradiation surface 35 a of the irradiation fiber 35 and the light receiving surface 34 a of the light receiving fiber 34. Thus, by reducing the number of fixing positions of the irradiation fiber 35 and the light receiving fiber 34, the manufacture of the skin tissue measurement probe 30A becomes simple. Further, by forming the bent portions 35d and 34d using the internal structure (the lid 32, the guide wall portion 32a, and the space 31a) on the probe main body 30, the internal space of the probe main body 30 can be effectively used. Therefore, a large curvature radius can be given to the bent portions 35d and 34d under the condition of the determined height H.

  The configuration of the present embodiment can be applied to a modification of the first embodiment.

(Third embodiment)
The skin tissue measurement probe (biological measurement probe) 30A according to the present embodiment has basically the same configuration as that of the first embodiment. That is, the skin tissue measurement probe (biological measurement probe) 30A includes an irradiation fiber 35 that irradiates the skin tissue of the living body with near-infrared light Hv, and a light receiving fiber 34 that receives diffuse reflection or transmitted light from the skin tissue. Are provided.

  In this embodiment, the optical fiber 33 is formed by arranging a plurality of irradiation fibers 35 or light receiving fibers 34 on concentric circles of the light receiving fibers 34 or irradiation fibers 35.

  The skin tissue measurement probe 30 </ b> A includes a probe body 30 that fixes and supports the irradiation fiber 35 and the light receiving fiber 34.

  The probe body 30 includes a bottomed cylindrical housing 31 in which a space 31 a is formed, and a lid portion 32 that is attached so as to close the space 31 a of the housing 31.

  The housing 31 includes a substantially cylindrical side wall portion 31b, a substantially disc-shaped bottom wall portion 31c, and a flange portion 31d that extends substantially in parallel from the upper portion of the side wall portion 31b and to which the lid portion 32 is attached. ing.

  Then, at the substantially central portion of the bottom wall portion 31c, the tips of the irradiation fiber 35 and the light receiving fiber 34 (tip portions where the irradiation surface 35a and the light receiving surface 34a are formed: vertical portions 34b and 35b) are inserted from the inside to the outside. An insertion hole 31e is formed to be fixed in the state.

  Also in this embodiment, the tip side of the vertical portions 34b and 35b (in the vicinity of the irradiation surface 35a of the irradiation fiber 35 and the light reception surface 34a of the light receiving fiber 34) is fixed to the housing 31 (probe body 30) using the adhesive 50. ing.

  Further, the flange portion 31d is formed with a groove portion 31g that opens to the inside and the outside, and the optical fiber 33 (the irradiation fiber 35 and the light receiving fiber 34) can be accommodated in the groove portion 31g.

  Here, the skin tissue measurement probe (biological measurement probe) 30A according to the present embodiment is mainly different from the first embodiment in that the probe body 30 is measured by the measuring means 39 as shown in FIG. It has a temperature control means for controlling the heating means 38 based on the temperature of the living body.

  In addition, the irradiation fiber 35 and the light receiving fiber 34 are fixed to the probe main body 30 at only one point in the vicinity of the irradiation surface 35a of the irradiation fiber 35 and the light receiving surface 34a of the light receiving fiber 34, as in the first embodiment. Is different.

  In this embodiment, the skin tissue measurement probe 30 </ b> A includes a measurement unit 39 that measures the temperature of the skin (measurement unit) of a living body and a heating unit 38 that heats the probe body 30.

  In this embodiment, the temperature of the probe body 30 is kept constant by the temperature control means based on the measurement result (biological skin temperature: living body temperature) by the measuring means 39.

  Specifically, the temperature measured by the measuring means 39 is output to a calculation unit (temperature control means) (not shown), and the amount of heat of the heating means 38 is controlled based on the output.

  The measuring means 39 measures, for example, the skin surface temperature of the living body.

  Moreover, the temperature kept constant by the temperature control means can be set to a temperature that is substantially the same as the deep body temperature or a temperature that is always higher than the body temperature.

  A heater can be used as the heating means 38 for heating the probe main body 30.

  Note that the temperature control means may control the amount of heat of the heating means 38 so as to keep giving a constant amount of heat to the measurement unit.

  Also according to this embodiment described above, the same operations and effects as those of the first embodiment can be achieved.

  Further, according to the present embodiment, the skin tissue measurement probe (biological measurement probe) 30 </ b> A has the heating means 38 based on the temperature of the biological skin measured by the measurement means 39 by the probe body 30 (biological temperature). It has temperature control means to control.

  By the way, the temperature of the measured skin fluctuates due to the influence of thermal metabolism that changes according to the surrounding environment and physiological state. The measurement spectrum is influenced by the temperature of the measurement skin. Therefore, if the temperature control means is not provided as in the first embodiment and the second embodiment, the measurement spectrum is affected by the temperature of the measured skin.

  However, in this embodiment, since the skin tissue measurement probe (biological measurement probe) 30A has the temperature control means, the biological measurement can be performed without being affected by the temperature of the measured skin. . As described above, according to this embodiment, it is possible to perform biometric measurement in which the temperature change of the measurement skin is ignored or taken into consideration.

  The configuration of the present embodiment can be applied to the modification of the first embodiment and the second embodiment.

(Fourth embodiment)
The 30A according to the present embodiment has basically the same configuration as that of the second embodiment. That is, the skin tissue measurement probe (biological measurement probe) 30A includes an irradiation fiber 35 that irradiates the skin tissue of the living body with near-infrared light Hv, and a light receiving fiber 34 that receives diffuse reflection or transmitted light from the skin tissue. Are provided.

  In this embodiment, the optical fiber 33 is formed by arranging a plurality of irradiation fibers 35 or light receiving fibers 34 on concentric circles of the light receiving fibers 34 or irradiation fibers 35.

  The skin tissue measurement probe 30 </ b> A includes a probe body 30 that fixes and supports the irradiation fiber 35 and the light receiving fiber 34.

  The probe body 30 includes a bottomed cylindrical housing 31 in which a space 31 a is formed, and a lid portion 32 that is attached so as to close the space 31 a of the housing 31.

  The housing 31 includes a substantially cylindrical side wall portion 31b, a substantially disc-shaped bottom wall portion 31c, and a flange portion 31d that extends substantially in parallel from the upper portion of the side wall portion 31b and to which the lid portion 32 is attached. ing.

  Then, at the substantially central portion of the bottom wall portion 31c, the tips of the irradiation fiber 35 and the light receiving fiber 34 (tip portions where the irradiation surface 35a and the light receiving surface 34a are formed: vertical portions 34b and 35b) are inserted from the inside to the outside. An insertion hole 31e is formed to be fixed in the state.

  Also in this embodiment, the tip side of the vertical portions 34b and 35b (in the vicinity of the irradiation surface 35a of the irradiation fiber 35 and the light reception surface 34a of the light receiving fiber 34) is fixed to the housing 31 (probe body 30) using the adhesive 50. ing.

  Further, the flange portion 31d is formed with a groove portion 31g that opens to the inside and the outside, and the optical fiber 33 (the irradiation fiber 35 and the light receiving fiber 34) can be accommodated in the groove portion 31g.

  Further, a guide wall portion 32 a having a shape corresponding to the outside of the bent portions 35 d and 34 d of the irradiation fiber 35 and the light receiving fiber 34 is formed on the lid portion 32.

  Further, the irradiation fiber 35 and the light receiving fiber 34 are fixed to the probe main body 30 at only one point in the vicinity of the irradiation surface 35 a of the irradiation fiber 35 and the light receiving surface 34 a of the light receiving fiber 34.

  Here, the skin tissue measurement probe (biological measurement probe) 30A according to the present embodiment is mainly different from the second embodiment in that, as shown in FIG. It is in the point formed so that at least one part of the site | part which contact | abuts on the skin surface 43a can be made to detach | leave.

  In the present embodiment, the optical fiber 33 is provided with connectors 50 and 51 that can be fitted and optically connected to each other, and by removing the connectors 50 and 51, the entire skin tissue measurement probe 30A can be exchanged. It has become.

  Also according to this embodiment described above, the same operations and effects as those of the second embodiment can be achieved.

  Further, according to the present embodiment, since the entire skin tissue measurement probe 30A can be exchanged, each part on the measurement probe contact side that directly contacts the measurement skin can be more easily maintained hygienically. . In addition, it becomes possible to replace the member periodically, and if the member is replaced periodically, the influence of the strength reduction of the bent portion of the optical fiber can be eliminated by long-term use.

  Next, a modification of this embodiment will be described.

(First modification)
Even in this modification, the biometric probe 30A is formed so that at least a part of the part that contacts the skin surface 43a of the living body can be detached.

  In this modification, the mounting assisting member 36 can be replaced.

  Also according to the above modification, the same operations and effects as those of the fourth embodiment can be obtained.

(Second modification)
Even in this modification, the biometric probe 30A is formed so that at least a part of the part that contacts the skin surface 43a of the living body can be detached.

  In this modification, the tip of the optical fiber can be detached.

  Specifically, as shown in FIG. 11 (A), the optical fiber 33 is configured to be cut a plurality of times, and after use, the tip portion of the optical fiber 33 is cut off, and then, as shown in FIG. 11 (B). By fitting (fixing) the tip of the remaining part to the housing 31 of the probe body 30, the new irradiation surface 35a and the light receiving surface 34a can be brought into contact with the skin surface 43a.

  The fixing to the housing 31 may be performed by the adhesive 50 as in the fourth embodiment.

  Also according to the above modification, the same operations and effects as those of the fourth embodiment can be obtained.

(Third Modification)
Even in this modification, the biometric probe 30A is formed so that at least a part of the part that contacts the skin surface 43a of the living body can be detached.

  In this modification, the entire surface of the living body measurement probe 30A that contacts the skin surface 43a is sequentially cut off. This cutting may be performed by laminating portions to be cut off and sequentially cutting them off, or by scraping the entire surface in contact with the skin surface 43a after use.

  Also according to the above modification, the same operations and effects as those of the fourth embodiment can be obtained.

  Note that the configuration of the present embodiment or a modification thereof can be applied to the first embodiment and the modification thereof and the third embodiment.

  The preferred embodiments of the present invention have been described above. However, the present invention is not limited to the above embodiments, and various modifications can be made.

  For example, in each of the embodiments described above, the example in which the light receiving fiber is disposed at the center is illustrated, but the irradiation fiber may be disposed at the center.

  In each of the above embodiments, the light receiving fiber is covered with a light shielding tube. However, the irradiation fiber may be covered with a light shielding tube, or both the light receiving fiber and the irradiation fiber may be covered with a light shielding tube. Good.

  In the third embodiment, the temperature of the probe main body (measurement unit) is controlled by the measurement unit, the heating unit, and the temperature control unit. However, based on the measured temperature using the measurement unit. Alternatively, the measured blood sugar level may be corrected. Moreover, it is also possible to have only the heating means among the measuring means and the heating means.

  Moreover, in the said 3rd Embodiment, although the measurement means illustrated what measures the temperature of the skin of the biological body as a temperature of a biological body, you may make it a measurement means measure the body deep part temperature as a temperature of a biological body. .

  Further, the specifications (shape, size, layout, etc.) of the housing, the lid, and other details can be changed as appropriate.

30A Probe for skin tissue measurement (probe for biological measurement)
30 Probe body 34 Light receiving fiber 34a Light receiving surface 34b Vertical portion 34c Parallel portion 34d Bending portion 35 Irradiation fiber 35a Irradiation surface 35b Vertical portion 35c Parallel portion 35d Bending portion 37 Shading tube 38 Heating means 39 Measuring means

Claims (9)

A biological measurement probe having an irradiation fiber for irradiating a skin tissue of a living body with near infrared light, and a light receiving fiber for receiving diffuse reflection or transmitted light from the skin tissue,
The irradiation fiber and the light receiving fiber extend substantially parallel to the living body skin surface, and a vertical portion disposed so that the irradiation surface of the irradiation fiber and the light receiving surface of the light receiving fiber are in contact with the skin surface of the living body. A parallel part arranged so as to be attached to the probe main body so as to form a bent part connecting the vertical part and the parallel part,
The biological measurement probe, wherein the irradiation fiber and the light receiving fiber are optically isolated at least at the bent portion.   The irradiation fiber and the light receiving fiber are fixed to the probe main body only at two points near the irradiation surface of the irradiation fiber and the light receiving surface of the light receiving fiber and near the bent portion of the parallel portion. Item 2. The biological measurement probe according to Item 1.   2. The biometric probe according to claim 1, wherein the irradiation fiber and the light receiving fiber are fixed to the probe main body at only one point in the vicinity of the irradiation surface of the irradiation fiber and the light receiving surface of the light receiving fiber. .   The biological measurement probe according to claim 2, wherein the bent portions of the irradiation fiber and the light receiving fiber are in a free state.   5. The biometric probe according to claim 1, wherein a plurality of the irradiation fibers or light receiving fibers are arranged on a concentric circle of the light receiving fiber or irradiation fiber. 6.   The biometric probe according to claim 5, wherein a plurality of fibers arranged concentrically among the light receiving fiber and the irradiation fiber have a bent portion spirally twisted.   The said biometric probe has at least any one of the measurement means which measures the temperature of a biological body, and the heating means which heats the said probe main body, The any one of Claims 1-6 characterized by the above-mentioned. Probe for biometric measurement.   The biometric probe includes the measurement unit, the heating unit, and a temperature control unit that controls the heating unit based on the temperature of the living body measured by the probe body with the measurement unit. The biometric probe according to claim 7.   The said biometric probe is formed so that at least one part of the site | part which contact | abuts the skin surface of a biological body can be made to detach | leave. Biometric probe.

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