Biological component measuring apparatus

Abstract

A biological component measuring device (1) includes an optical medium (10), a high-thermal-conductivity film (30), an excitation light source (16), a probe light source (20), and a light position detector (25). The high-thermal-conductivity film (30) has a higher thermal conductivity than the optical medium (10) and is disposed on a sample placement surface (second surface (12)) of the optical medium (10). The high-thermal-conductivity film (30) diffuses heat generated from a sample (5) irradiated with excitation light (17) more in a first direction (x direction) than in a second direction (y direction). The first direction is a direction of travel of probe light (21) in a plan view of the sample placement surface. The second direction is a direction perpendicular to the first direction in the plan view of the sample placement surface.

Description

Technical Field

[0001] This disclosure relates to a device for measuring the composition of organisms. Background Technology

[0002] Japanese Patent Publication No. 2017-519214 (Patent Document 1) discloses a non-invasive analysis system comprising an optical medium, an infrared light source, a detection light source, and a photodiode. Specifically, a biological sample is placed on the surface of the optical medium. The infrared light source radiates infrared light. The infrared light passes through the optical medium and irradiates the biological sample. The infrared light is absorbed by the biological sample, causing the sample to heat up. The degree of heat absorption by the biological sample depends on the amount or concentration of biological components in or on the surface of the sample.

[0003] The probe light source radiates visible light towards the optical medium. At the interface between the optical medium and the biological sample, the probe light undergoes total internal reflection and exits from the optical medium. Heat absorption by the biological sample is transferred to the optical medium, causing a change in its refractive index. This change in the refractive index affects the total internal reflection of the probe light at the interface, altering the direction of travel of the probe light emitted from the optical medium. A photodiode detects this change in the direction of travel. Based on the change in the direction of travel of the probe light detected by the photodiode, the amount or concentration of the biological component is determined. For example, in the case of a patient's skin sample, the patient's blood glucose level is measured as a biological component.

[0004] Existing technical documents

[0005] Patent documents

[0006] Patent Document 1: Japanese Patent Publication No. 2017-519214 Summary of the Invention

[0007] However, in the non-invasive analysis system disclosed in Patent Document 1, the optical medium is formed of zinc sulfide (ZnS). Zinc sulfide (ZnS) has a high thermal conductivity of 27.2 W / (m·K). The heat absorbed by the biological sample is transferred to the optical medium and diffuses rapidly and isotropically within it. A large amount of heat diffuses into the region of the optical medium outside the optical path of the probe light. The temperature rise of the portion of the optical medium in the optical path of the probe light is reduced. The change in refractive index of the portion of the optical medium in the optical path of the probe light is smaller. Therefore, it is not possible to determine the biological components with high accuracy. This disclosure was made in view of the above-mentioned problems, and its object is to provide a biological component measuring device capable of measuring biological components with improved accuracy.

[0008] The biocomposition measuring device disclosed herein includes an optical medium, a high thermal conductivity film, an excitation light source, a detection light source, and a light position detector. The optical medium includes a sample mounting surface. The high thermal conductivity film has a higher thermal conductivity than the optical medium and is disposed on the sample mounting surface. The excitation light source radiates excitation light that travels through the optical medium onto the sample mounted on the high thermal conductivity film. The detection light source radiates detection light that travels through the optical medium. The light position detector detects the position of the detection light emitted from the optical medium. In a top view of the sample mounting surface, the optical path of the detection light in the optical medium overlaps with the irradiated portion of the excitation light in the sample mounting surface. The high thermal conductivity film causes heat generated from the sample irradiated by the excitation light to diffuse more in the first direction than in the second direction. The first direction is the direction of travel of the detection light in the top view of the sample mounting surface. The second direction is the direction perpendicular to the first direction in the top view of the sample mounting surface.

[0009] The high thermal conductivity film concentrates the temperature gradient region of the optical medium caused by heat generated from the sample irradiated with excitation light into the portion of the optical medium within the optical path of the probe light. The temperature change in the portion of the optical medium within the optical path of the probe light increases, and the length of the temperature gradient region of the optical medium through which the probe light propagates increases. The refractive index change in the portion of the optical medium within the optical path of the probe light also increases, and the length of the refractive index gradient region of the optical medium through which the probe light propagates increases. The displacement of the probe light detected by the optical position detector increases. The biological composition measuring device of this disclosure can measure biological composition with improved accuracy. Attached Figure Description

[0010] Figure 1 This is a schematic diagram of the biological composition measuring device according to Embodiment 1.

[0011] Figure 2 This is a partial enlarged top view of the biological composition measuring device of Embodiment 1.

[0012] Figure 3 This is a flowchart illustrating the biological composition determination method of Embodiment 1.

[0013] Figure 4 This is a diagram showing the simulation results of the temperature gradient region of the optical medium in the biological composition measuring device of Example 1 of Embodiment 1.

[0014] Figure 5 This is a graph showing the simulation results of the temperature distribution in the temperature gradient region of the optical medium in the biological composition measuring device of the comparative example.

[0015] Figure 6 This is a partial enlarged top view of the biological composition measuring device of a variation of Embodiment 1.

[0016] Figure 7 This is a partial enlarged top view of the biological composition measuring device of Embodiment 2.

[0017] Figure 8 This is a partial enlarged top view of the biological composition measuring device of Embodiment 3.

[0018] Figure 9 This is a schematic diagram of the biological composition measuring device according to Embodiment 4.

[0019] Figure 10 This is a partial enlarged top view of the biological composition measuring device of Embodiment 4.

[0020] Figure 11 This is a graph showing the simulation results of the temperature distribution in the temperature gradient region of the optical medium in the biological composition measuring device of Embodiment 4 of Embodiment 4.

[0021] Figure 12 This is a schematic diagram of the biological composition measuring device of Embodiment 5.

[0022] Figure 13 This is a partial enlarged top view of the biological composition measuring device of Embodiment 5.

[0023] Figure 14 This is a graph showing the simulation results of the temperature distribution in the temperature gradient region of the optical medium in the biological composition measuring device of Example 5 of Embodiment 5.

[0024] Figure 15 This is a partial enlarged top view of the biological composition measuring device of a modified embodiment 5.

[0025] Figure 16 This is a schematic diagram of the biological composition measuring device according to Embodiment 6.

[0026] Figure 17 This is a schematic diagram of the biological composition measuring device according to Embodiment 7.

[0027] (Explanation of reference numerals in the attached diagram)

[0028] 1, 1a, 1b, 1c, 1d, 1e, 1f, 1g, 1h: Biocomposition Measurement Device; 5: Sample; 6: Surface; 10: Optical Medium; 11: First Surface; 12: Second Surface; 13: Third Surface; 14: Fourth Surface; 16: Excitation Light Source; 17: Excitation Light; 17r: Irradiation Part; 18: Refractive Index Gradient Region; 19: Temperature Gradient Region; 20: Detection Light Source; 21: Detection Light; 21a: First Emitted Detection Light; 21b: Second Emitted Detection Light; 22a: First Position; 22b: Second Position; 25: Light Position Detector; 27: Displacement Calculation Unit; 28: Biocomposition Measurement Unit; 30: High Thermal Conductivity Film; 31, 32: High Thermal Conductivity Film Parts; 33: Opening; 35: Anti-Reflection Film. Detailed Implementation

[0029] The following describes the implementation method. Furthermore, the same reference numerals are used for the same structure, and their descriptions are not repeated.

[0030] Implementation method 1.

[0031] Reference Figure 1 as well as Figure 2 The following describes the biological composition measuring device 1 according to Embodiment 1. The biological composition measuring device 1 mainly includes an optical medium 10, a high thermal conductivity film 30, an excitation light source 16, a detection light source 20, a light position detector 25, a displacement calculation unit 27, and a biological composition measuring unit 28.

[0032] The optical medium 10 includes a first surface 11, a second surface 12 opposite to the first surface 11, a third surface 13 connecting the first surface 11 and the second surface 12, and a fourth surface 14 connecting the first surface 11 and the second surface 12 and opposite to the third surface 13. The first surface 11 of the optical medium 10 is the incident surface of the excitation light 17 radiated from the excitation light source 16. The second surface 12 is the sample placement surface. The sample 5 is placed on the second surface 12. The sample 5 is, for example, a patient's skin or bodily fluids. If the substance being measured is a liquid, the sample 5 is a liquid contained in a transparent sample holder (not shown). The third surface 13 is the incident surface of the detection light 21 radiated from the detection light source 20. The fourth surface 14 is the exit surface of the detection light 21.

[0033] The optical medium 10 is transparent to the excitation light 17. In this specification, "transparent to the excitation light 17" means that the optical medium 10 has a light transmittance of 25% or more to the excitation light 17. The light transmittance of the optical medium 10 to the excitation light 17 can be 50% or more, 75% or more, or 90% or more. The optical medium 10 is transparent to the probe light 21. In this specification, "transparent to the probe light 21" means that the optical medium 10 has a light transmittance of 25% or more to the probe light 21. The light transmittance of the optical medium 10 to the probe light 21 can be 50% or more, 75% or more, or 90% or more. The optical medium 10 is formed, for example, of zinc selenide (ZnSe, thermal conductivity 27 W / (m·K)) or zinc sulfide (ZnS, thermal conductivity 18 W / (m·K)). The optical medium 10 can also be formed from an infrared-transmitting material such as a chalcogenide glass.

[0034] An excitation light source 16 radiates excitation light 17, which travels through an optical medium 10, onto a sample 5 placed on a sample mounting surface (second surface 12) and a high thermal conductivity film 30. The excitation light 17 radiates from the excitation light source 16 and enters the optical medium 10 from the first surface 11. The excitation light 17 travels through the optical medium 10. The excitation light 17 enters the sample 5 from the second surface 12. The excitation light 17 is absorbed by biological components in the sample 5 or on the surface 6 of the sample 5. For example, in the case of obtaining a patient's blood glucose value using a biological component measuring device 1, the biological component is sugar present in the interstitial fluid of the epidermis. Absorption of the excitation light 17 by the biological components generates heat of absorption in the sample 5. The heat of absorption of the sample 5 is conducted through the optical medium 10. A temperature gradient region 19 and a refractive index gradient region 18 are generated within the optical medium 10.

[0035] The wavelength of the excitation light 17 is determined based on the absorption wavelength of the biological components in sample 5 or on surface 6 of sample 5. The wavelength of the excitation light 17 can also be longer than the wavelength of the probe light 21. The excitation light 17 is, for example, infrared light with a wavelength of 3 μm or more and 20 μm or less. The excitation light 17 can also be light with multiple wavelengths. For example, when measuring a patient's blood glucose level using the biological component analysis device 1, the wavelength range of the excitation light 17 is the wavelength range that includes the fingerprint spectrum of glucose (e.g., a wavelength range of 8.5 μm or more and 10 μm or less). The excitation light source 16 is, for example, a quantum cascade laser capable of emitting broadband infrared light. Reference light that is not absorbed by the biological components in sample 5 or on surface 6 of sample 5 can also be irradiated onto sample 5 together with the excitation light 17.

[0036] The probe light source 20 radiates probe light 21. Probe light 21 has a wavelength, for example, encompassing the wavelength region from the visible to the near-infrared. The probe light source 20 is, for example, a semiconductor laser. In a top view of the sample mounting surface (second surface 12), the probe light 21 propagates in the first direction (x-direction). In the top view of the sample mounting surface (second surface 12), the optical path of the probe light 21 in the optical medium 10 overlaps with the irradiated portion 17r of the excitation light 17 in the sample mounting surface (second surface 12).

[0037] Specifically, the probe light 21 is incident on the optical medium 10 from the third surface 13. The probe light 21 travels along the second surface 12 of the optical medium 10. During its travel within the optical medium 10, the probe light 21 travels through a refractive index gradient region 18 generated within the optical medium 10 due to the heat absorbed by the sample 5. The probe light 21 refracts in the refractive index gradient region 18, causing a change in its direction of travel. The probe light 21 (first emitted probe light 21a, second emitted probe light 21b) exits from the fourth surface 14 of the optical medium 10.

[0038] The optical position detector 25 detects the position of the probe light 21 (first emitted probe light 21a, second emitted probe light 21b) emitted from the optical medium 10. Specifically, the optical position detector 25 detects the first position 22a of the probe light 21 (first emitted probe light 21a) when the sample 5 is not illuminated by the excitation light 17. The optical position detector 25 detects the second position 22b of the probe light 21 (second emitted probe light 21b) when the sample 5 is illuminated by the excitation light 17. By illuminating the sample 5 with the excitation light 17, the position of the probe light 21 detected by the optical position detector 25 changes from the first position 22a to the second position 22b.

[0039] The optical position detector 25 outputs the first position 22a of the probe light 21 (first emitted probe light 21a) and the second position 22b of the probe light 21 (second emitted probe light 21b) to the displacement calculation unit 27. The optical position detector 25 is, for example, a photodiode or a semiconductor position detection element.

[0040] The displacement calculation unit 27 is connected to the light position detector 25. The displacement calculation unit 27 calculates the displacement δ of the probe light 21 corresponding to the distance between the first position 22a and the second position 22b. The biological composition measurement unit 28 measures the biological composition in the sample 5 or on the surface 6 of the sample 5 based on the displacement δ of the probe light 21. The displacement calculation unit 27 and the biological composition measurement unit 28 can be implemented, for example, using a computational processing device.

[0041] A high thermal conductivity film 30 is disposed on the sample mounting surface (second surface 12). The sample 5 is placed on the high thermal conductivity film 30. The high thermal conductivity film 30 has a higher thermal conductivity than the optical medium 10. For example, the thermal conductivity of the high thermal conductivity film 30 may be more than 1.5 times that of the optical medium 10. For example, the thermal conductivity of the high thermal conductivity film 30 may be more than 2.0 times that of the optical medium 10. The high thermal conductivity film 30 is formed, for example, from silicon (Si, thermal conductivity 160 W / (m·K)) or germanium (Ge, thermal conductivity 59 W / (m·K)).

[0042] In the top view of the sample mounting surface (second surface 12), the high thermal conductivity film 30 overlaps with the irradiated portion 17r of the excitation light 17 in the sample mounting surface (second surface 12). The high thermal conductivity film 30 is transparent to the excitation light 17. In this specification, the transparency of the high thermal conductivity film 30 to the excitation light 17 means that the light transmittance of the high thermal conductivity film 30 to the excitation light 17 is 25% or more. The light transmittance of the high thermal conductivity film 30 to the excitation light 17 can be 50% or more, 75% or more, or 90% or more.

[0043] The high thermal conductivity film 30 can also be transparent to the probe light 21. In this specification, the transparency of the high thermal conductivity film 30 to the probe light 21 means that the light transmittance of the high thermal conductivity film 30 to the probe light 21 is 25% or more. The light transmittance of the high thermal conductivity film 30 to the probe light 21 can be 50% or more, 75% or more, or 90% or more.

[0044] The high thermal conductivity film 30 causes the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). The second direction (y direction) is perpendicular to the first direction (x direction) in a top view of the sample mounting surface (second surface 12). In the top view of the sample mounting surface (second surface 12), the high thermal conductivity film 30 overlaps with the probe light 21 in the first direction (x direction).

[0045] In the top view of the sample mounting surface (second surface 12), the high thermal conductivity film 30 has an elongated shape with its length in the first direction (x-direction) and its width in the second direction (y-direction). The first length L1 of the high thermal conductivity film 30 in the first direction (x-direction) is greater than the second length L2 of the high thermal conductivity film 30 in the second direction (y-direction). The first length L1 is, for example, more than twice the second length L2. The first length L1 can also be more than three times the second length L2, more than four times the second length L2, more than five times the second length L2, more than six times the second length L2, more than eight times the second length L2, or more than ten times the second length L2. The thickness of the high thermal conductivity film 30 can be more than 1 μm or more.

[0046] In the top view of the sample mounting surface (second surface 12), the high thermal conductivity film 30 traverses the irradiation portion 17r in the first direction (x direction). The first length L1 of the high thermal conductivity film 30 in the first direction (x direction) is greater than the diameter D of the irradiation portion 17r. The second length L2 of the high thermal conductivity film 30 in the second direction (y direction) may also be less than the diameter D of the irradiation portion 17r. The second length L2 of the high thermal conductivity film 30 in the second direction (y direction) may also be greater than the width of the probe light 21, which is the length of the probe light 21 in the second direction (y direction). In the top view of the sample mounting surface (second surface 12), the high thermal conductivity film 30 may also be formed symmetrically with respect to the optical axis of the irradiation portion 17r or the excitation light 17 in both the first direction (x direction) and the second direction (y direction).

[0047] Reference Figure 3 This describes the biological composition determination method of this embodiment using the biological composition determination device 1.

[0048] The biological composition determination method of this embodiment includes: detecting the first position 22a of the probe light 21 (first emitted probe light 21a) using a light position detector 25 without irradiating the sample 5 with the excitation light 17 (S1). Since the sample 5 is not irradiated with the excitation light 17, no heat absorption occurs in the sample 5. No temperature gradient region 19 or refractive index gradient region 18 is generated inside the optical medium 10. When the sample 5 is not irradiated with the excitation light 17, the probe light 21 (first emitted probe light 21a) is emitted from the optical medium 10. The first position 22a of the probe light 21 (first emitted probe light 21a) is the position of the probe light 21 (first emitted probe light 21a) detected by the light position detector 25 when the sample 5 is not irradiated with the excitation light 17.

[0049] The biological component determination method of this embodiment includes: irradiating a sample 5 with excitation light 17 while using a photoposition detector 25 to detect the second position 22b of a probe light 21 (second emitted probe light 21b) (S2). Since the sample 5 is irradiated with excitation light 17, the excitation light 17 is absorbed by biological components in the sample 5 or on the surface 6 of the sample 5. Absorption of excitation light 17 by biological components generates heat of absorption in the sample 5. The high thermal conductivity film 30 causes the heat of absorption of the sample 5 to diffuse more in the first direction (x direction) than in the second direction (y direction). The heat of absorption of the sample 5 is conducted through the high thermal conductivity film 30 in the optical medium 10. A temperature gradient region 19 and a refractive index gradient region 18 are generated inside the optical medium 10.

[0050] The probe light 21 is refracted in the refractive index gradient region 18, causing a change in its direction of travel. When the sample 5 is illuminated by the excitation light 17, the probe light 21 (the second emitted probe light 21b) is emitted from the optical medium 10. The second position 22b of the probe light 21 (the second emitted probe light 21b) is the position of the probe light 21 (the second emitted probe light 21b) detected by the light position detector 25 when the sample 5 is illuminated by the excitation light 17. By illuminating the sample 5 with the excitation light 17, the position of the probe light 21 detected by the light position detector 25 changes from the first position 22a to the second position 22b.

[0051] The biological composition measurement method of this embodiment includes: calculating the displacement amount δ of the probe light 21 (S3). Specifically, the displacement amount calculation unit 27 calculates the displacement amount δ of the probe light 21 corresponding to the distance between the first position 22a and the second position 22b.

[0052] The biological component determination method of this embodiment includes: determining biological components in sample 5 or on surface 6 of sample 5 based on the displacement δ of probe light 21 (S4). For example, biological component determination unit 28 is connected to a memory (not shown). The memory stores a data table that corresponds the type of biological component, the displacement δ of probe light 21, and the amount or concentration of biological component. The biological component determination unit 28 refers to the data table and, for example, obtains the amount or concentration of biological components in sample 5 or on surface 6 of sample 5 based on the type of biological component and the displacement δ of probe light 21.

[0053] Referring to the biological composition measuring apparatus 1 of Examples 1 to 3 of this embodiment and the biological composition measuring apparatus of the comparative example, the operation of the biological composition measuring apparatus 1 of this embodiment will be explained. As shown in Table 1, Examples 1 to 3 differ from each other in the shape (first length L1) of the high thermal conductivity film 30. In Examples 1 to 3, the thickness of the high thermal conductivity film 30 is 10 μm. As shown in Table 1, the comparative example differs from this embodiment in that the high thermal conductivity film 30 is not provided on the sample placement surface (second surface 12) of the optical medium 10.

[0054] [Table 1]

[0055]

[0056] Table 1 lists the displacement δ of the probe light 21 in Examples 1 to 3 and the comparative example, with values ​​normalized to the displacement δ of the probe light 21 in the comparative example. In Examples 1 to 3 and the comparative example, the diameter D of the excitation light 17 is 40 μm, and the width of the probe light 21 is 20 μm.

[0057] In the comparative example, a high thermal conductivity film 30 was not provided on the sample mounting surface (second surface 12) of the optical medium 10. Therefore, in the top view of the sample mounting surface (second surface 12), the absorbed heat of sample 5 diffuses isotropically. Figure 5 As shown, in the comparative example, the temperature gradient region 19 diffuses isotropically in the top view of the sample mounting surface (second surface 12).

[0058] In contrast, in Examples 1 to 3, the high thermal conductivity film 30 causes the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). The heat generated from the sample 5 is transferred in the optical medium 10 along the shape of the high thermal conductivity film 30. The high thermal conductivity film 30 concentrates the temperature gradient region 19 of the optical medium 10 caused by the heat generated from the sample 5 irradiated by the excitation light 17 into a portion of the optical medium 10 located in the optical path of the probe light 21. In Examples 1 to 3, compared to the comparative example, the temperature change of the portion of the optical medium 10 located in the optical path of the probe light 21 (temperature gradient region 19) is greater, and the length of the temperature gradient region 19 of the optical medium 10 through which the probe light 21 propagates is longer (see, for example, reference...). Figure 4 The temperature gradient region 19 in Example 1 is shown. In Examples 1 to 3, compared to the comparative example, the refractive index change is greater in the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18), and the length of the refractive index gradient region 18 of the optical medium 10 through which the probe light 21 propagates is longer. Therefore, Examples 1 to 3, compared to the comparative example, can determine the composition of biological organisms with improved accuracy.

[0059] Reference Figure 6 This describes a modified example of the biological composition measuring apparatus 1a according to Embodiment 1. In the biological composition measuring apparatus 1a, regarding the high thermal conductivity film 30, as it approaches the irradiation portion 17r, the second length L2 of the high thermal conductivity film 30 in the second direction (y direction) decreases. Therefore, when more excitation light 17 is irradiated onto the sample 5, the absorbed heat of the sample 5 increases. In addition, the high thermal conductivity film 30 reduces the diffusion of heat generated from the sample 5 irradiated by the excitation light 17 in the second direction (y direction). The high thermal conductivity film 30 causes the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse further in the first direction (x direction) compared to the second direction (y direction). The temperature change in the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) further increases. The refractive index change in the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) further increases. Therefore, biological composition can be measured with improved accuracy.

[0060] The effects of the biological composition measuring devices 1 and 1a of this embodiment are explained.

[0061] The biological composition measuring apparatus 1, 1a of this embodiment includes an optical medium 10, a high thermal conductivity film 30, an excitation light source 16, a detection light source 20, and a light position detector 25. The optical medium 10 includes a sample mounting surface (second surface 12). The high thermal conductivity film 30 has a higher thermal conductivity than the optical medium 10 and is disposed on the sample mounting surface (second surface 12). The excitation light source 16 radiates excitation light 17 that travels through the optical medium 10 to a sample 5 placed on the sample mounting surface (second surface 12) and the high thermal conductivity film 30. The detection light source 20 radiates detection light 21 that travels through the optical medium 10. The light position detector 25 detects the position of the detection light 21 emitted from the optical medium 10. In a top view of the sample mounting surface (second surface 12), the optical path of the detection light 21 in the optical medium 10 overlaps with the irradiated portion 17r of the excitation light 17 in the sample mounting surface (second surface 12). The high thermal conductivity film 30 causes the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). The first direction (x direction) is the direction of travel of the probe light 21 in a top view of the sample mounting surface (second surface 12). The second direction (y direction) is the direction perpendicular to the first direction (x direction) in a top view of the sample mounting surface (second surface 12).

[0062] In the biological composition measuring devices 1 and 1a, the high thermal conductivity film 30 concentrates the temperature gradient region 19 of the optical medium 10 caused by the heat generated from the sample 5 irradiated by the excitation light 17 onto a portion of the optical medium 10 in the optical path of the probe light 21. The temperature change of the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) increases, and the length of the temperature gradient region 19 of the optical medium 10 through which the probe light 21 propagates increases. The refractive index change of the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) increases, and the length of the refractive index gradient region 18 of the optical medium 10 through which the probe light 21 propagates increases. The displacement δ of the probe light 21 detected by the photoposition detector 25 increases. The biological composition measuring devices 1 and 1a are able to measure biological composition with improved accuracy.

[0063] In the biological composition measuring apparatus 1 and 1a of this embodiment, in the top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 overlaps with the probe light 21 in the first direction (x direction). Therefore, the temperature change of the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 increases, and the length of the temperature gradient region 19 of the optical medium 10 through which the probe light 21 propagates increases. The refractive index change of the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 increases, and the length of the refractive index gradient region 18 of the optical medium 10 through which the probe light 21 propagates increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring apparatus 1 and 1a can measure biological composition with improved accuracy.

[0064] In the biological composition measuring apparatus 1 and 1a of this embodiment, the second length L2 of the high thermal conductivity film 30 in the second direction (y direction) is greater than the width of the probe light 21, which is the length of the probe light 21 in the second direction (y direction). Therefore, the temperature distribution of the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 becomes more uniform over the width range of the probe light 21. The refractive index distribution of the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 becomes more uniform over the width range of the probe light 21. The propagation disorder of the probe light 21 in the optical medium 10 is reduced. The biological composition measuring apparatus 1 and 1a can measure biological composition with improved accuracy.

[0065] In the biological composition measuring apparatus 1 and 1a of this embodiment, in a top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 has an elongated shape with the first direction (x direction) as the length direction and the second direction (y direction) as the width direction. Therefore, the high thermal conductivity film 30 causes the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). The temperature change of the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 increases, and the length of the temperature gradient region 19 of the optical medium 10 through which the probe light 21 propagates increases. The refractive index change of the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 increases, and the length of the refractive index gradient region 18 of the optical medium 10 through which the probe light 21 propagates increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring devices 1 and 1a are capable of measuring biological composition with improved accuracy.

[0066] In the biological composition measuring apparatus 1 and 1a of this embodiment, in a top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 traverses the irradiation portion 17r in the first direction (x direction). Therefore, the high thermal conductivity film 30 can be positioned near the sample 5, which serves as a heat source. The temperature change of the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 increases, and the length of the temperature gradient region 19 of the optical medium 10 through which the probe light 21 propagates increases. The refractive index change of the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 increases, and the length of the refractive index gradient region 18 of the optical medium 10 through which the probe light 21 propagates increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring apparatus 1 and 1a can measure biological composition with improved accuracy.

[0067] In the biological composition measuring apparatus 1a of this embodiment, regarding the high thermal conductivity film 30, as the irradiation portion 17r approaches, the second length L2 of the high thermal conductivity film 30 in the second direction (y direction) decreases. Therefore, when more excitation light 17 is irradiated onto the sample 5, the absorbed heat of the sample 5 increases. The temperature change of the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) further increases. The refractive index change of the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) further increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring apparatus 1a is able to measure biological composition with improved accuracy.

[0068] In the biological composition measuring apparatus 1 and 1a of this embodiment, the high thermal conductivity film 30 is formed of silicon or germanium. Therefore, the high thermal conductivity film 30 is transparent to the excitation light 17. When more excitation light 17 is irradiated onto the sample 5, the absorbed heat of the sample 5 increases. The temperature change of the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) further increases. The refractive index change of the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) further increases. The displacement δ of the probe light 21 detected by the photoposition detector 25 increases. The biological composition measuring apparatus 1 and 1a can measure biological composition with improved accuracy.

[0069] Implementation method 2.

[0070] Reference Figure 7 This section describes the biological composition measuring device 1b according to Embodiment 2. The biological composition measuring device 1b of this embodiment has the same structure as the biological composition measuring device 1 of Embodiment 1, but differs mainly in the following aspects.

[0071] In the biological composition measuring device 1b, at least one opening 33 is provided in the portion of the high thermal conductivity film 30 that overlaps with the irradiation portion 17r. Multiple openings 33 may also be provided in the portion of the high thermal conductivity film 30 that overlaps with the irradiation portion 17r. The diameter of the opening 33 (or each opening of the multiple openings 33) is smaller than the diameter of the excitation light 17 and smaller than the diameter D of the irradiation portion 17r. In a top view of the sample mounting surface (second surface 12), the total area of ​​the openings 33 can be either 50% or more of the area of ​​the portion of the high thermal conductivity film 30 that overlaps with the irradiation portion 17r, or 80% or more of the area of ​​the portion of the high thermal conductivity film 30 that overlaps with the irradiation portion 17r.

[0072] Since the high thermal conductivity film 30 is absent in a portion of the irradiation section 17r, more excitation light 17 can be irradiated onto the sample 5. Therefore, as the material for the high thermal conductivity film 30 in this embodiment, a material with lower transmittance to the excitation light 17 but higher thermal conductivity can be used compared to the material of the high thermal conductivity film 30 in Embodiment 1. The material for the high thermal conductivity film 30 in this embodiment is, for example, a metal such as gold (Au, thermal conductivity 295 W / (m·K)) or copper (Cu, thermal conductivity 386 W / (m·K)).

[0073] In addition to the effects of the biological composition measuring device 1 of Embodiment 1, the biological composition measuring device 1b of this embodiment also has the following effects.

[0074] In the biological composition measuring device 1b of this embodiment, at least one opening 33 is provided in the portion of the high thermal conductivity film 30 that overlaps with the irradiation portion 17r.

[0075] Therefore, when sample 5 is irradiated with more excitation light 17, the absorbed heat of sample 5 increases. Consequently, as the material for the high thermal conductivity film 30, a material with lower transmittance but higher thermal conductivity for the excitation light 17 can be used. The temperature change in the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) further increases. The refractive index change in the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) further increases. The displacement δ of the probe light 21 detected by the photoposition detector 25 increases. The biological composition measuring device 1b is able to measure biological composition with improved accuracy.

[0076] Implementation method 3.

[0077] Reference Figure 8 This describes the biological composition measuring device 1c according to Embodiment 3. The biological composition measuring device 1c of this embodiment has the same structure as the biological composition measuring device 1 of Embodiment 1, but differs mainly in the following aspects.

[0078] In the biological composition measuring device 1c, the high thermal conductivity film 30 includes a plurality of high thermal conductivity film portions 31. The plurality of high thermal conductivity film portions 31 are spaced apart from each other and arranged in the second direction (y direction). In a top view of the sample mounting surface (second surface 12), the plurality of high thermal conductivity film portions 31 may also be formed symmetrically with respect to the optical axis of the irradiation portion 17r or the excitation light 17 in both the first direction (x direction) and the second direction (y direction).

[0079] Each of the plurality of high thermal conductivity film portions 31 has an elongated shape with its length in a first direction (x-direction) and its width in a second direction (y-direction). The third length L3 (the first length L1 of the high thermal conductivity film 30) of each of the plurality of high thermal conductivity film portions 31 in the first direction (x-direction) is greater than the fourth length L4 of each of the plurality of high thermal conductivity film portions 31 in the second direction (y-direction). The third length L3 is, for example, more than twice the fourth length L4. The third length L3 may also be more than three times the fourth length L4, more than four times the fourth length L4, more than five times the fourth length L4, more than six times the fourth length L4, more than eight times the fourth length L4, or more than ten times the fourth length L4.

[0080] In the top view of the sample mounting surface (second surface 12), multiple high thermal conductivity film portions 31 are respectively superimposed on the irradiation portion 17r of the excitation light 17 in the sample mounting surface (second surface 12). The multiple high thermal conductivity film portions 31 cause the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). In the top view of the sample mounting surface (second surface 12), the multiple high thermal conductivity film portions 31 can be either superimposed on the probe light 21 or separated from the probe light 21.

[0081] In the top view of the sample mounting surface (second surface 12), multiple high thermal conductivity film portions 31 traverse the irradiation portion 17r in the first direction (x direction). The third length L3 of each of the multiple high thermal conductivity film portions 31 in the first direction (x direction) is greater than the diameter D of the irradiation portion 17r. The fourth length L4 of each of the multiple high thermal conductivity film portions 31 in the second direction (y direction) is less than the diameter D of the irradiation portion 17r. The spacing between a pair of adjacent high thermal conductivity film portions 31 is less than the diameter D of the irradiation portion 17r.

[0082] In addition to the effects of the biological composition measuring device 1 of Embodiment 1, the biological composition measuring device 1c of this embodiment also has the following effects.

[0083] In the biological composition measuring device 1c of this embodiment, the high thermal conductivity film 30 includes a plurality of high thermal conductivity film portions 31. Each of the plurality of high thermal conductivity film portions 31 has an elongated shape with a first direction (x direction) as its length direction and a second direction (y direction) as its width direction. The plurality of high thermal conductivity film portions 31 are spaced apart from each other and arranged in the second direction (y direction).

[0084] Therefore, when sample 5 is irradiated with more excitation light 17, the absorbed heat of sample 5 increases. Consequently, as the high thermal conductivity film 30, a material with higher thermal conductivity but lower transmittance to the excitation light 17 can be used. The temperature change in the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) further increases. The refractive index change in the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) further increases. The displacement δ of the probe light 21 detected by the photoposition detector 25 increases. The biological composition measuring device 1c is able to measure biological composition with improved accuracy.

[0085] Implementation method 4.

[0086] Reference Figure 9 as well as Figure 10 This section describes the biological composition measuring device 1d according to Embodiment 4. The biological composition measuring device 1d of this embodiment has the same structure as the biological composition measuring device 1c of Embodiment 3, but differs mainly in the following aspects.

[0087] In the biological composition measuring apparatus 1d, in a top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 is completely separated from the irradiation portion 17r in the first direction (x direction). Specifically, the high thermal conductivity film 30 includes a plurality of high thermal conductivity film portions 32. The plurality of high thermal conductivity film portions 32 are arranged in the first direction (x direction) with a spacer G between them. In the top view of the sample placement surface (second surface 12), the irradiation portion 17r is located between a pair of adjacent high thermal conductivity film portions 32. The pair of adjacent high thermal conductivity film portions 32 are positioned on opposite sides of the irradiation portion 17r in the first direction (x direction) (specifically, the positive first direction (+x direction) side and the negative first direction (-x direction) side). The spacer G between the pair of adjacent high thermal conductivity film portions 32 is greater than or equal to the diameter D of the irradiation portion 17r. Specifically, the spacer G is greater than the diameter D of the irradiation portion 17r. Multiple high thermal conductivity film portions 32 are separated from the irradiated portion 17r in the first direction (±x direction). The interval G can be less than 2.0 times or less than 1.5 times the diameter D of the irradiated portion 17r.

[0088] The third length L3 of each of the plurality of high thermal conductivity film portions 32 in the first direction (x direction) is greater than the fourth length L4 of each of the plurality of high thermal conductivity film portions 32 in the second direction (y direction) (the second length L2 of the high thermal conductivity film 30). The plurality of high thermal conductivity film portions 32 cause the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). The third length L3 of each of the plurality of high thermal conductivity film portions 32 in the first direction (x direction) may also be greater than the diameter D of the irradiated portion 17r. The fourth length L4 of each of the plurality of high thermal conductivity film portions 32 in the second direction (y direction) may also be less than the diameter D of the irradiated portion 17r.

[0089] In the top view of the sample mounting surface (second side 12), the entire irradiation portion 17r is separated from the high thermal conductivity film 30, so the high thermal conductivity film 30 can be formed of a material having a higher thermal conductivity than the material forming the high thermal conductivity film 30 of Embodiment 1, but a lower transmittance for the excitation light 17. The high thermal conductivity film 30 is formed, for example, of a metal such as gold or copper.

[0090] like Figure 11 As shown, the high thermal conductivity film 30 causes the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). Therefore, the temperature change in the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 increases. The refractive index change in the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 increases. The displacement δ of the probe light 21 detected by the photoposition detector 25 increases. Therefore, the biological composition measuring device 1d can measure biological composition with improved accuracy. Furthermore, in Figure 11 In Embodiment 4 of this implementation, the third length L3 of each of the plurality of high thermal conductivity film portions 32 is 80 μm, the fourth length L4 of each of the plurality of high thermal conductivity film portions 32 in the second direction (y direction) is 20 μm, the thickness of each of the plurality of high thermal conductivity film portions 32 is 10 μm, and the spacing G is 40 μm. In Embodiment 4, the diameter D of the excitation light 17 is 40 μm, and the width of the probe light 21 is 20 μm.

[0091] In addition to the effects of the biological composition measuring device 1c in Embodiment 3, the biological composition measuring device 1d of this embodiment also has the following effects.

[0092] In the biological composition measuring device 1d of this embodiment, the high thermal conductivity film 30 includes a plurality of high thermal conductivity film portions 32. The plurality of high thermal conductivity film portions 32 are separated from the irradiation portion 17r in the first direction (±x direction).

[0093] In the biological composition measuring apparatus 1d of this embodiment, in the top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 is completely separated from the irradiation portion 17r in the first direction (x direction).

[0094] Therefore, when sample 5 is irradiated with all the excitation light 17 incident on the irradiation portion 17r, the absorbed heat of sample 5 increases. Furthermore, as a high thermal conductivity film 30, a material with higher thermal conductivity but lower transmittance to the excitation light 17 can be used. The temperature change in the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) further increases. The refractive index change in the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) further increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring device 1d is able to measure biological composition with improved accuracy.

[0095] In the biological composition measuring apparatus 1d of this embodiment, the high thermal conductivity film 30 is formed of metal. Therefore, the thermal conductivity of the high thermal conductivity film 30 can be further improved. The temperature change of the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) is further increased. The refractive index change of the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) is further increased. The displacement δ of the probe light 21 detected by the light position detector 25 is increased. The biological composition measuring apparatus 1d can measure biological composition with improved accuracy.

[0096] Implementation method 5.

[0097] Reference Figure 12 as well as Figure 13 This section describes the biological composition measuring device 1e according to Embodiment 5. The biological composition measuring device 1e of this embodiment has the same structure as the biological composition measuring device 1 of Embodiment 1, but differs mainly in the following aspects.

[0098] In the biological composition measuring apparatus 1e, in a top view of the sample mounting surface (second surface 12), the high thermal conductivity film 30 is asymmetrically arranged relative to the irradiation portion 17r in the first direction (x direction). In the top view of the sample mounting surface (second surface 12), the high thermal conductivity film 30 is completely separated from the irradiation portion 17r in the first direction (x direction). The high thermal conductivity film 30 is only disposed on one side of the irradiation portion 17r in the first direction (x direction) (e.g., the negative first direction (-x direction) side).

[0099] The first length L1 of the high thermal conductivity film 30 in the first direction (x direction) can be greater than or equal to the second length L2 of the high thermal conductivity film 30 in the second direction (y direction). Specifically, the first length L1 can also be greater than the second length L2. The first length L1 can be less than or equal to the diameter D of the irradiated portion 17r. The first length L1 can also be greater than the diameter D of the irradiated portion 17r. The high thermal conductivity film 30 is formed of a metal such as gold or copper, similar to that in Embodiment 4.

[0100] like Figure 14 As shown, the high thermal conductivity film 30 causes the heat generated from the sample 5 irradiated by the excitation light 17 to diffuse more in the first direction (x direction) than in the second direction (y direction). Therefore, the temperature change in the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 increases. The refractive index change in the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 increases. The displacement δ of the probe light 21 detected by the photoposition detector 25 increases. Therefore, the biological composition measuring device 1e can measure biological composition with improved accuracy. Furthermore, in Figure 14 In Example 5 of this embodiment, the first length L1 of the high thermal conductivity film 30 is 20 μm, the second length L2 of the high thermal conductivity film 30 is 20 μm, the thickness of the high thermal conductivity film 30 is 10 μm, and the interval between the high thermal conductivity film 30 and the irradiation portion 17r is 10 μm. In Example 5, the diameter D of the excitation light 17 is 40 μm, and the width of the probe light 21 is 20 μm.

[0101] Reference Figure 15 The following describes a modified example of the biological composition measuring apparatus 1f of this embodiment. In the biological composition measuring apparatus 1f, in the top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 overlaps a portion of the irradiation portion 17r.

[0102] The biological composition measuring devices 1e and 1f of this embodiment have the same effects as the biological composition measuring device 1 of Embodiment 1.

[0103] In the biological composition measuring apparatus 1e and 1f of this embodiment, in the top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 is asymmetrically arranged relative to the irradiation portion 17r in the first direction. Therefore, the temperature change in the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 increases. The refractive index change in the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring apparatus 1e and 1f can measure biological composition with improved accuracy.

[0104] In the biological composition measuring apparatus 1e of this embodiment, in a top view of the sample placement surface (second surface 12), the high thermal conductivity film 30 is completely separated from the irradiation portion 17r in the first direction (x direction). Therefore, when all the excitation light 17 incident on the irradiation portion 17r is irradiated onto the sample 5, the absorbed heat of the sample 5 increases. Furthermore, as the high thermal conductivity film 30, a material with higher thermal conductivity but lower transmittance to the excitation light 17 can be used. The temperature change of the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) further increases. The refractive index change of the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) further increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring apparatus 1e is able to measure biological composition with improved accuracy.

[0105] In the biological composition measuring devices 1e and 1f of this embodiment, the high thermal conductivity film 30 is formed of metal. Therefore, the thermal conductivity of the high thermal conductivity film 30 can be further improved. The temperature change of the portion of the optical medium 10 in the optical path of the probe light 21 (temperature gradient region 19) is further increased. The refractive index change of the portion of the optical medium 10 in the optical path of the probe light 21 (refractive index gradient region 18) is further increased. The displacement δ of the probe light 21 detected by the photoposition detector 25 is increased. The biological composition measuring devices 1e and 1f can measure biological composition with improved accuracy.

[0106] Implementation method 6.

[0107] Reference Figure 16 This describes the biological composition measuring device 1g according to Embodiment 6. The biological composition measuring device 1g of this embodiment has the same structure as the biological composition measuring device 1 of Embodiment 1, but differs mainly in the following aspects.

[0108] The biological composition measuring device 1g also includes a reflection-preventing film 35 disposed on the surface of a high thermal conductivity film 30 away from the optical medium 10. The reflection-preventing film 35 reduces the reflection of excitation light 17 occurring at the interface between the sample 5 and the high thermal conductivity film 30. The reflection-preventing film 35 is formed of zinc selenide (ZnSe), zinc sulfide (ZnS), calcium fluoride (CaF2), magnesium fluoride (MgF2), potassium bromide (KBr), or sodium chloride (NaCl), or a combination thereof.

[0109] In addition to the effects of the biological composition measuring device 1 of Embodiment 1, the biological composition measuring device 1g of this embodiment also has the following effects.

[0110] The biological composition measuring device 1g of this embodiment also includes a reflection-preventing film 35 disposed on the surface of the high thermal conductivity film 30 away from the optical medium 10. Therefore, when more excitation light 17 is irradiated onto the sample 5, the absorbed heat of the sample 5 increases. The temperature change in the portion of the optical medium 10 (temperature gradient region 19) in the optical path of the probe light 21 further increases. The refractive index change in the portion of the optical medium 10 (refractive index gradient region 18) in the optical path of the probe light 21 further increases. The displacement δ of the probe light 21 detected by the light position detector 25 increases. The biological composition measuring device 1g is able to measure biological composition with improved accuracy.

[0111] Implementation method 7.

[0112] Reference Figure 17 This describes the biological composition measuring device 1h according to Embodiment 7. The biological composition measuring device 1h of this embodiment has the same structure as the biological composition measuring device 1 of Embodiment 1 and achieves the same effect, but differs mainly in the following aspects.

[0113] In the biological composition measuring device 1h, the third surface 13 is tilted relative to the incident direction of the probe light 21. The fourth surface 14 is tilted relative to the emission direction of the probe light 21. The emission direction of the probe light 21 to the optical medium 10 can also be parallel to the incident direction of the probe light 21 to the optical medium 10. The optical medium 10 is, for example, an internal total internal reflection prism (TIR prism).

[0114] The probe light 21 is incident on the optical medium 10 from the third surface 13. The probe light 21 is refracted at the third surface 13 and propagates towards the interface between the optical medium 10 (second surface 12) and the sample 5 within the optical medium 10. In a top view of the sample mounting surface (second surface 12), the optical path of the probe light 21 in the optical medium 10 overlaps with the portion of the sample mounting surface (second surface 12) illuminated by the excitation light 17. The probe light 21 undergoes total internal reflection at the interface between the optical medium 10 (second surface 12) and the high thermal conductivity film 30. During its propagation within the optical medium 10, the probe light 21 travels through a refractive index gradient region 18 generated within the optical medium 10 due to the heat absorbed by the sample 5. The probe light 21 is refracted within the refractive index gradient region 18, causing a change in its direction of travel. The probe light 21 (first emitted probe light 21a, second emitted probe light 21b) is emitted from the fourth surface 14 of the optical medium 10.

[0115] The embodiments 1-7 and their variations disclosed herein should be considered illustrative in all respects and not restrictive. At least two of the embodiments 1-7 and their variations may be combined, provided there is no contradiction. The scope of this disclosure is defined not by the foregoing description but by the claims, and is intended to include all modifications within the meaning and scope equivalent to the claims.

Claims

1. A biological component measuring apparatus comprising: an optical medium including a sample placement surface; a high thermal conductive film having a higher thermal conductivity than the optical medium, the high thermal conductive film being disposed on the sample placement surface; an excitation light source radiating excitation light advancing in the optical medium toward a sample placed on the sample placement surface and the high thermal conductive film; a probe light source radiating probe light advancing in the optical medium; and a light position detector detecting a position of the probe light emitted from the optical medium, wherein in a plan view of the sample placement surface, an optical path of the probe light in the optical medium overlaps with an irradiation portion of the excitation light in the sample placement surface, the high thermal conductive film diffuses heat generated from the sample irradiated with the excitation light more in a first direction than in a second direction, the first direction is a direction of advancement of the probe light in the plan view of the sample placement surface, the second direction is a direction perpendicular to the first direction in the plan view of the sample placement surface, and a first length of the high thermal conductive film in the first direction is greater than a second length of the high thermal conductive film in the second direction.

2. The biological component measuring apparatus according to claim 1, wherein in the plan view of the sample placement surface, the high thermal conductive film overlaps with the probe light in the first direction.

3. The biological component measuring apparatus according to claim 1 or 2, wherein a length of the high thermal conductive film in the second direction is greater than a width of the probe light.

4. The biological component measuring apparatus according to claim 1 or 2, wherein in the plan view of the sample placement surface, the high thermal conductive film has an elongated shape with the first direction being a length direction and the second direction being a width direction.

5. The biological component measuring apparatus according to claim 4, wherein in the plan view of the sample placement surface, the high thermal conductive film crosses the irradiation portion in the first direction.

6. The biological component measuring apparatus according to claim 5, wherein a length of the high thermal conductive film in the second direction decreases as approaching the irradiation portion.

7. The biological component measuring apparatus according to claim 5 or 6, wherein at least one opening portion is provided in a portion of the high thermal conductive film overlapping with the irradiation portion.

8. The biological component measuring apparatus according to claim 1 or 2, wherein the high thermal conductive film includes a plurality of high thermal conductive film portions, and the plurality of high thermal conductive film portions are separated from the irradiation portion in the first direction.

9. The biological component measuring apparatus according to claim 1 or 2, wherein in the plan view of the sample placement surface, the high thermal conductive film is asymmetrically disposed with respect to the irradiation portion in the first direction.

10. The biological component measuring apparatus according to claim 8, wherein in the plan view of the sample placement surface, the high thermal conductive film is separated from an entirety of the irradiation portion in the first direction. ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ 11. The biological component measuring apparatus according to any one of claims 1 to 2, 5 to 6, and 10, wherein a reflection preventing film is provided on a surface of the high thermal conductive film away from the optical medium.

12. The biological component measuring apparatus according to claim 11, wherein the reflection preventing film is formed of zinc selenide, zinc sulfide, calcium fluoride, magnesium fluoride, potassium bromide, or sodium chloride.

13. The biological component measuring apparatus according to any one of claims 1 to 2, 5 to 6, 10, and 12, wherein the high thermal conductive film is formed of silicon or germanium.

14. The biological component measuring apparatus according to any one of claims 1 to 2, 5 to 6, 10, and 12, wherein the high thermal conductive film is formed of a metal.

15. The biological component measuring apparatus according to any one of claims 1 to 2, 5 to 6, 10, and 12, wherein a displacement amount calculating section is further provided, the optical position detector outputs a first position of the probe light when the excitation light is not irradiated to the sample and a second position of the probe light when the excitation light is irradiated to the sample to the displacement amount calculating section, the displacement amount calculating section calculates a displacement amount of the probe light corresponding to a distance between the first position and the second position.

16. The biological component measuring apparatus according to claim 15, wherein a biological component measuring section is further provided, which measures a biological component in the sample or on a surface of the sample based on the displacement amount.

17. The biological component measuring apparatus according to any one of claims 1 to 2, 5 to 6, 10, 12, and 16, wherein the excitation light is infrared light having a wavelength of 3 μm or more and 20 μm or less.

Images