WO2006082859A1 - 光学素子およびそれを用いた光学測定装置 - Google Patents
光学素子およびそれを用いた光学測定装置 Download PDFInfo
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- WO2006082859A1 WO2006082859A1 PCT/JP2006/301686 JP2006301686W WO2006082859A1 WO 2006082859 A1 WO2006082859 A1 WO 2006082859A1 JP 2006301686 W JP2006301686 W JP 2006301686W WO 2006082859 A1 WO2006082859 A1 WO 2006082859A1
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- light
- prism
- sample
- light receiving
- optical element
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Classifications
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- G—PHYSICS
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N21/3103—Atomic absorption analysis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
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- A—HUMAN NECESSITIES
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
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- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6813—Specially adapted to be attached to a specific body part
- A61B5/6825—Hand
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- A—HUMAN NECESSITIES
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- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
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- F02B—INTERNAL-COMBUSTION PISTON ENGINES; COMBUSTION ENGINES IN GENERAL
- F02B53/00—Internal-combustion aspects of rotary-piston or oscillating-piston engines
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- F02B53/08—Charging, e.g. by means of rotary-piston pump
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F02—COMBUSTION ENGINES; HOT-GAS OR COMBUSTION-PRODUCT ENGINE PLANTS
- F02B—INTERNAL-COMBUSTION PISTON ENGINES; COMBUSTION ENGINES IN GENERAL
- F02B55/00—Internal-combustion aspects of rotary pistons; Outer members for co-operation with rotary pistons
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- G—PHYSICS
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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- A—HUMAN NECESSITIES
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- A61B2562/14—Coupling media or elements to improve sensor contact with skin or tissue
- A61B2562/146—Coupling media or elements to improve sensor contact with skin or tissue for optical coupling
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F02—COMBUSTION ENGINES; HOT-GAS OR COMBUSTION-PRODUCT ENGINE PLANTS
- F02B—INTERNAL-COMBUSTION PISTON ENGINES; COMBUSTION ENGINES IN GENERAL
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- F02B2053/005—Wankel engines
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- G—PHYSICS
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- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N21/35—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light
- G01N21/359—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light using near infrared light
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02T—CLIMATE CHANGE MITIGATION TECHNOLOGIES RELATED TO TRANSPORTATION
- Y02T10/00—Road transport of goods or passengers
- Y02T10/10—Internal combustion engine [ICE] based vehicles
- Y02T10/12—Improving ICE efficiencies
Definitions
- the present invention relates to an optical element used to measure the concentration of glucose, cholesterol, urea or triglyceride in a sample by optically measuring a sample such as a living tissue or a solution, and an optical element using the same.
- the present invention relates to an optical measurement device.
- FIG. 8 is a configuration diagram of a conventional optical element having a groove portion proposed in WO 01/58355 A1. Arrows in FIG. 8 indicate the path of light emitted from the light source 44.
- the light (arrow X in FIG. 8) incident on the side surface 42a of the groove 42 in the optical element 41 passes through the living tissue 48 and then exits from the side surface 42b. Information on the living tissue can be obtained by detecting the emitted light with a detector or the like.
- the groove 42 of the conventional optical element as described above is formed directly on the plane of the optical element material mainly by machining such as surface grinding or ultrasonic processing or etching, etc. In this method, it is difficult to obtain a smooth machined surface in which the groove portion 42 obtained is easily scratched, and there is a problem that it is difficult to machine it into a predetermined shape.
- the groove 42 shown in FIG. 8 is processed into a V shape by rotating a grinding wheel whose processing surface is V-shaped and pressing it against the flat surface of the optical element material.
- the accuracy of the grinding wheel shape is directly reflected in the machining accuracy and surface roughness, or when the grinding wheel is worn out, the depth and shape of the groove 42 change, and the surface roughness increases. It is difficult to machine the groove 42 into a predetermined shape with high accuracy.
- the depth of the groove 32 When the size and shape change or the roughness of the processed surface increases, the actual light path may differ from the designed path, or light may be scattered on the surface of the groove 42, Measurement accuracy will be reduced.
- the light emitted from the light source 44 is generally a parallel light force S, not a perfect parallel light,. Therefore, the light reflected by the bottom 42c of the groove 42 (arrow Y in FIG. 8), the light reflected by the surface other than the groove 42 (arrow Z in FIG. 8), and the incident surface without being incident on the living tissue 48. Unwanted light such as light (not shown) reflected and emitted inside the optical element 42a is also detected along with the light X, and the measurement accuracy is lowered.
- the present invention provides an optical element that can be easily formed and has excellent measurement accuracy, and highly reliable optical using the optical element.
- An object of the present invention is to provide a measuring apparatus by an easy and simple method.
- optical element of the present invention is a lens
- a light receiving prism having a light receiving surface on which light returned from the sample is received, and a light reduction portion provided between the light emitting prism and the light receiving prism, the light emitting prism and the light receiving prism And a recess in contact with the sample is formed, and light emitted from the light emitting surface travels straight through the sample in contact with the recess and is incident on the light receiving surface. It is characterized by
- the “light reduction part” in the present invention refers to a member or part having a function of reducing the amount of light passing therethrough.
- “light reduction” means reducing the amount of light emitted with respect to the amount of light incident when light moves between two or more media, that is, the amount of light passing through. (I) reduce the amount of light passing by changing the refractive index (reflectance) between the media, as well as ( ⁇ ) blocking the amount of light passing through (eg Reducing by reflection, absorption, etc.).
- a light source for emitting light to the light irradiation prism in order to irradiate the light from the light irradiation prism to the sample; And a photodetector for detecting light returned from the sample to the light receiving prism.
- the present invention it is possible to easily form an optical element having a recess, and to obtain an optical element in which a decrease in measurement accuracy caused by unnecessary light such as reflected light inside the optical element is suppressed. Can. Further, by using the optical element of the present invention, a highly reliable optical measuring device can be easily and simply realized.
- FIG. 1 is a view showing a configuration of an optical measurement device in a first embodiment of the present invention.
- FIG. 2 is a characteristic diagram showing wavelength characteristics of the transmission detection light amount when the transmission detection light amount of the finger is measured using the optical measurement device of FIG.
- FIG. 3 is a view showing a configuration of a modification of the optical measurement device in the first embodiment of the present invention.
- FIG. 4 is a view showing a configuration of an optical measurement device in Embodiment 2 of the present invention.
- FIG. 5 is a view showing the configuration of an optical measurement device in a third embodiment of the present invention.
- FIG. 6 is a view showing the configuration of an optical measurement device in a fourth embodiment of the present invention.
- FIG. 7 is a view showing the configuration of an optical measurement device in a fifth embodiment of the present invention.
- FIG. 8 is a configuration diagram of an optical element having a groove in contact with a conventional sample.
- the optical element of the present invention comprises a light irradiation prism having a light emission surface from which light irradiated to a sample is emitted, a light receiving prism having a light reception surface on which light returned from the sample is received, and A light reduction portion provided between a light irradiation prism and the light receiving prism is provided, and the light irradiation prism and the light receiving prism are combined to form a recess in contact with the sample.
- the light emitted from the light emitting surface travels straight through the sample in contact with the recess and is incident on the light receiving surface.
- the concave portions are formed by combining the light irradiation element and the light receiving prism, so that the concave portions are formed after the concave portions are formed. There is no need to smooth the surface. Therefore, it is possible to easily form a recess having a smooth surface, and it is possible to obtain an optical element which does not reduce the optical measurement accuracy by light scattering in the recess.
- the above-mentioned concave portion can be easily configured by combining, for example, a processing surface having a planar shape.
- the recess may be formed by a compound plane composed of a plurality of planes such as a step shape by using a known technique. It is also positive to combine the curved surfaces to form the recess.
- the recess is formed by processing the light irradiation prism and the light receiving prism into a predetermined shape and then combining them, it is easy to process the bottom of the recess with high accuracy.
- the light reducing portion may be a gap provided between the light emitting prism and the light receiving prism.
- reflected light is generated at each interface due to the difference between the refractive index of the light emitting prism and the light receiving prism, and the refractive index of the gap portion.
- the amount of light incident on the light receiving prism without passing through the sample can be reduced. Then, unnecessary light can be prevented from reaching the photodetector described later, and a decrease in measurement accuracy can be reliably suppressed.
- the light reduction part may be a light shielding part provided between the light irradiation prism and the light receiving prism.
- the light shielding portion provided between the light emitting prism and the light receiving prism blocks the light that has passed through the light emitting prism but does not pass through the sample but is incident on the light receiving prism. be able to. Then, unnecessary light can be prevented from reaching the photodetector described later, and a decrease in measurement accuracy can be reliably suppressed.
- the optical element of the present invention is provided between the light irradiation prism and the light receiving prism. It is preferable to have an equipped spacer.
- the measurement position in the depth direction on the sample by changing the thickness of the spacer and changing the distance between the light irradiation prism and the light reception prism. If the distance between the light emitting element and the light receiving element is increased, the sample can be deeply penetrated by the concave portion in contact, and as a result, the deep part of the sample can be measured. Conversely, when the distance between the light irradiation prism and the light receiving prism is narrowed, the sample is less likely to enter the recess, and as a result, the surface layer of the sample can be measured.
- the spacer may be made of the same material as the light reducing portion.
- the spacer when the spacer is formed of a material having a lower refractive index than the light emitting prism and the light receiving prism, the spacer can have the same role as the light reducing portion.
- the light emitting surface of the light emitting prism is a flat first inclined portion in contact with the sample, and the light receiving surface of the light receiving prism is a flat second in contact with the sample.
- the first inclined portion and the second inclined portion face each other to form the concave portion, and the first inclined portion and the second inclined portion of the concave portion are formed.
- the first inclined portion and the second inclined portion are respectively optically polished, the first inclined portion and the second inclined portion are made to face each other, and the sample comes in contact with the V-shape. Because of the formation of the concave portion, it is possible to obtain a concave portion with high optical accuracy which has a smooth flat surface easily. Also, in the case of the shape of the concave portion, it is possible to stabilize the optical path length at which the sample is easily fixed.
- the optical element of the present invention preferably includes a cover that covers a part of the recess and is combined with the light emitting prism and the light receiving prism to form a sample holder.
- a cover comprises, for example, a side surface of the light emitting prism, a first cover and a second cover disposed to cover the side surface of the light emitting prism and to open the upper surface of the recess. be able to.
- the optical element of the present invention comprises adjusting means for adjusting the distance between the light irradiation prism and the light receiving prism.
- the distance between the light emitting prism and the light receiving prism can be changed more easily and easily, and the measuring position in the depth direction on the sample can be adjusted more easily and easily. . If the distance between the light emitting prism and the light receiving prism is increased, the light can enter deeper into the recess in contact with the sample, and as a result, the deep part of the sample can be measured. Conversely, when the distance between the light emitting prism and the light receiving prism is narrowed, the sample is less likely to enter the recess, and as a result, the surface layer of the sample can be measured.
- An optical measuring device comprises: the above-described optical element according to the present invention; a light source for emitting light to the light irradiation prism for irradiating the light from the light irradiation prism to the sample; Force A light detector that detects light returned to the light receiving prism.
- the optical measurement device of the present invention preferably includes a dispersive element disposed between the light receiving prism and the light detector.
- FIG. 1 is a view showing the configuration of an optical measuring apparatus (component concentration measuring apparatus) according to Embodiment 1 of the present invention using the optical element (measuring element) of the present invention, and the arrows in the figure indicate optical paths. .
- the optical element will be described below.
- the optical element 12 comprises a light emitting prism 13 for emitting light to a sample, and a sample A light receiving prism 14 for receiving the returned light is combined and integrated, and a recess 15 for contacting the sample is formed between the light emitting prism 13 and the light receiving prism 14. Further, in the present embodiment, a light blocking portion for blocking light is formed between the light emitting prism 13 and the light receiving prism 14 as the light reducing portion 19.
- the surface is smoothed.
- the light emitting prism 13 and the light receiving prism 14 are joined in a V-shape so that the first inclined portion 13a and the second inclined portion 14a face each other.
- the first inclined portion 13a and the second inclined portion are used to optically polish the planar first inclined portion 13a and the second inclined portion 14a, respectively.
- 14a can be easily smoothed.
- optical element 12 of the present embodiment can be disassembled into the light emitting prism 13 and the light receiving prism 14, it is easier to clean the recess as compared with the conventional optical element (see FIG. 8) which can not be disassembled.
- silicon, germanium, SiC, diamond, ZnSe, ZnS, KrS or the like can be used.
- the transmittance is high at an infrared wavelength of about 9 to 10 microns. From the viewpoint of high processability and mechanical strength, it is preferable to use silicon or germanium.
- fused silica single crystal silicon, optical glass, transparent resin, or the like can be used.
- Light reduction part 19 in the present embodiment is, for example, a film-like, sheet-like, plate-like or rod-like light shield part, and light which does not reach the concave part of the light passing through the light irradiation prism, It has a function to prevent light which does not pass through the material from entering the light receiving prism.
- a reflection film of a metal such as Al, Cu or Ag, a absorption film such as Cr or black, or a dielectric multilayer film for the light shielding portion is preferable to use.
- a multilayer film formed of a metal layer and a dielectric layer may be used.
- a known method such as vacuum evaporation, sputtering method or CVD method may be used.
- the films may be formed directly on the surface of the light irradiation prism 13 or the light receiving prism 14, or after the films are formed on both of the prisms, the films may be bonded to each other.
- the light shielding portion in addition to the sheet made of the material of the film, for example, an aluminum foil or a metal sheet of Cu can be used.
- a metal sheet may be directly attached to the light irradiation prism 13 or the light receiving prism 14, and then the metal sheet may be attached to both prisms, and then the two may be attached to each other.
- the light shielding portion a plate made of the material of the film or the sheet is used.
- the optical measurement device of the present embodiment can be obtained by using the optical element 12 of the present embodiment having the configuration as described above.
- the optical measurement apparatus according to the present embodiment detects the light passing through the optical element 12, the light source 11 for emitting light, the light separating element 16 for separating light returned from the sample via the light receiving prism 14, and the light separating element 16.
- a light detector 17 is provided.
- the light reducing portion 19 prevents the light not transmitted through the sample from entering the light receiving prism as described above. Don't let unnecessary light from the light source reach you. This improves the SZN ratio of the optical measurement device.
- the light source 11 can be used without particular limitation as long as it contains light of the absorption wavelength of the measurement component to be measured.
- a globe light source obtained by sintering SiC in a rod shape a C 2 O laser, a tungsten lamp, an infrared pulse light source, or a QCL light source.
- Can For example, when measuring a substance that has a strong absorption peak in the mid-infrared region, such as gonoreose, a globe light source, an infrared pulse light source, or a QCL light source is preferable.
- a substance that has a strong absorption peak in the mid-infrared region such as gonoreose, a globe light source, an infrared pulse light source, or a QCL light source is preferable.
- a substance having an absorption peak in the near infrared region for example, a halogen light source, a semiconductor laser or an LED can be used. It is known that glucose has an absorption peak in the near infrared region which is not only in the mid infrared region, and it is preferable to use, for example, a DFB laser or a DBR laser for LED light communication.
- a grating element or an optical filter element can be used as the spectral element 16 so that the force S can be obtained.
- FT-IR or laser spectroscopy may be used.
- the position of the spectral element is not particularly limited.
- the light detector 17 those known in the art can be used.
- pyroelectric sensors, thermopiles, thermistors, and MCT detectors HgCdTe detectors, which are a type of quantum detectors
- MCT detectors HgCdTe detectors, which are a type of quantum detectors
- an InGaAs detector, a photodiode, a PbS detector, an InSb detector, an InAs detector, or an array sensor of these detectors is used.
- the finger 18 is pressed against the recess 15 of the optical element 12 to abut. At this time, as shown in FIG. 1, the finger 18 slips into the recess 15 by light pressure.
- the light emitted from the light source 11 reaches the light irradiation prism 13 of the optical element 12 and the light reaching the light irradiation prism 13 is transmitted to the optical element 12. It reaches the recessed part 15 or the light shielding part 19 provided.
- the light reaching the light reducing portion 19 is absorbed or reflected so as not to be incident on the light receiving prism 14.
- the light that has reached the recess 15 is refracted due to the difference in refractive index between the light irradiation prism 13 and the finger 18 when exiting from the recess 15 and is transmitted through the finger 18.
- the light transmitted through the finger 18 is incident on the light receiving prism 14. Since the light travels along the path as described above, the light receiving prism 14 can easily receive much light traveling straight in the finger 18, and the light passing through the light receiving prism 14 is transmitted through the light separating element 16.
- the detector 17 is reached. For example, based on the light detected by the light detector 17, a living body tissue such as a glucose concentration Parameters can be calculated.
- the distance through which light passes in the finger 18 is not particularly limited, but may be set to, for example, about 1 to 2 mm. Further, the angle formed by the first inclined portion and the second inclined portion in the recess 15 is not particularly limited, and may be set to, for example, 90 degrees.
- the incident angle of light on the finger 18 which is a sample is determined by the shape of the recess 15 and the refractive index of the light irradiation prism 13 and the light receiving prism 14.
- the refractive index of the light emitting prism 13 and the light receiving prism 14 is preferably larger than the refractive index of the sample.
- the shape of the recess 15 or the finger 18 is determined according to the refractive index of the sample which is only determined by the refractive index of the optical element 12. It is preferable to set the incident angle of light to.
- the light separating element 16 can force S to transmit only light necessary to detect the concentration of the component.
- the component concentration is calculated based on the light detected by the light detector 17. That is, light of a specific wavelength is absorbed and reduced according to the component, and the reduced light amount depends on the component concentration, so the component concentration is calculated from the reduced light amount.
- FIG. 1 An example of the result of measuring the living tissue of the finger 18 using the above-described optical measurement device of the present invention is shown in FIG.
- the horizontal axis shows the wavelength
- the vertical axis shows the arbitrary value of the detected light quantity.
- A indicates the measurement result before pressing the finger 18 into the recess
- B indicates the measurement result when pressing the finger 18 into the recess.
- the spectrum change is largely changed when the finger 18 is pressed against the spectrum before the finger 18 is pressed. This is because the light from the light source 11 is largely absorbed by the blood components of the finger 18, such as water, talc, neutral fat and cholesterol, and various components that make up the finger 18, and the light is reduced. is there.
- 1. 1. 4 microns a greatly diminishing force, which corresponds to the absorption spectrum of water, indicates the presence of water in the living body.
- FIG. 3 is a diagram showing the configuration of a modification of the optical measurement device of the present embodiment.
- This modified embodiment is for measuring the component concentration of a sample liquid such as a solution or liquid, and similar to FIG. 1, the light source 11, the optical element 12, the light irradiation prism 13, the light receiving prism 14, the recess 15,
- the optical element 12 further comprises a first measuring force It has a bar 20a and a second measurement cover 20b.
- the first measurement cover 20 a and the second measurement cover 20 b cover the side surfaces of the light emitting prism 13 and the light receiving prism 14 while opening the upper portion of the recess 15.
- the sample for holding the sample solution 21 is surrounded by the concave portion 15 by the first inclined portion 13a, the second inclined portion 14a, the first measurement cover 20a and the second measurement cover 20b. It functions as a holding unit. For this reason, the sample liquid 21 is held in the recess 15 without spilling. With such a configuration, in this variation, the components of the sample solution can be easily measured simply by adding the measurement cover to the configuration of FIG. 1 in this manner.
- FIG. 4 is a view showing a configuration of an optical measuring apparatus (component concentration measuring apparatus) according to a second embodiment of the present invention using the optical element (measuring element) of the present invention, and the arrow in the figure indicates an optical path. .
- the optical element will be described below.
- the optical element 12 is configured by combining and integrating a light emitting prism 13 for emitting light to the sample and a light receiving prism 14 for receiving the light returned from the sample.
- a substantially V-shaped concave portion 15 in contact with the sample is formed between the and the light receiving prism 14.
- the distance between the light irradiation prism 13 and the light reception prism 14 is defined between the light irradiation prism 13 and the light reception prism 14, and the light passes through the light irradiation prism 13 to pass through the sample.
- a light reduction unit 19 is provided to reduce the amount of light that is incident on the light receiving prism 14 among the light that is not received.
- the light reducing portion 19 is made of, for example, a material (for example, glass or plastic) having a refractive index smaller than the refractive index of the light emitting prism 13 and the light receiving prism 14 and has a refractive index (ie, reflectance).
- a material for example, glass or plastic
- refractive index ie, reflectance
- the thickness (width) of the light reduction part 19, that is, the distance between the light irradiation prism 13 and the light reception prism 14 is not particularly limited.
- water absorption may occur if the optical path length is too long. Because it becomes too big, it is preferable that it is 3 mm or less.
- light reducing portion 19 has a rectangular parallelepiped shape, and concave portion 15 is formed in a substantially V shape by a combination of light irradiation prism 13, light receiving prism 14 and light reducing portion 19. Being done Ru.
- the planar first inclined portion 13a in contact with the sample in the light irradiation prism 13 and the planar second inclined portion 14a in contact with the sample in the light receiving prism 14 are disposed to face each other, and are respectively recessed
- the upper surface of the light reducing portion 19 is located between the lower end of the first inclined portion 13a and the lower end of the second inclined portion 14a, and forms the bottom surface portion of the recess 15.
- the light path of the light passing through the recess 15 can be easily changed. That is, if the light reduction portion 19 is made thicker, the distance between the light irradiation prism 13 and the light receiving prism 14 becomes larger, and the living tissue gets deeper into the recessed portion 15, and living tissue in a deeper region can be measured. . In addition, if the light reduction portion 19 is made thinner, the distance between the light irradiation prism 13 and the light receiving prism 14 becomes smaller, and the living tissue in the surface layer can be further measured. As described above, the light reducing portion 19 also has a role as a spacer, and by setting the thickness of the light reducing portion 19 appropriately, it is possible to measure the living tissue at a desired depth.
- the tissue of the finger 18 includes the outermost surface epidermis 18a, the lower dermis 18b and the subcutaneous fat 18c.
- the tissue of the finger 18 includes the outermost surface epidermis 18a, the lower dermis 18b and the subcutaneous fat 18c.
- the concentration of glucose it is preferable to allow more light to pass through that portion of the dermis 18b, which is preferably measured between the epidermis 18a and the subcutaneous fat 18c.
- the distance through which light passes through the finger 18 may be set to, for example, about 1 to 2 mm when using an absorption wavelength of gonorucose with a wavelength of 16 OO nm. When it exceeds 3 mm, the amount of water absorption increases. Further, the angle of the substantially V character formed by the recess 15 (the angle formed by the first inclined portion and the second inclined portion) may be set to 90 degrees to 120 degrees.
- the optical measurement apparatus of the present embodiment can obtain the same effect as that of the above-described Embodiment 1, and can detect a large amount of light having passed through the dermis 18 b of the finger 18 with the light detector 17. it can. Further, in the optical element 12, a light reduction portion 19 having a function as a spacer is disposed between the light irradiation prism 13 and the light reception prism 14, and a distance between the light irradiation prism 13 and the light reception prism 14. By optimizing the depth of measurement to different individuals, it is possible to increase the amount of light passing through certain parts in the finger 18 and to increase the signal strength based on the light in the light detector 17. it can. Therefore, in the optical measurement device of the present embodiment, detection The S / N ratio of the emitted light can be increased, and highly accurate measurement of component concentration can be realized.
- FIG. 5 is a view showing the configuration of an optical measuring apparatus (component concentration measuring apparatus) according to Embodiment 3 of the present invention using the optical element (measuring element) of the present invention, and the arrows in the figure indicate the optical path. .
- the optical element will be described below.
- the description of the parts common to the second embodiment will be omitted.
- the light reduction unit 29 in the present embodiment also has a function as a spacer.
- a portion of the light irradiation prism 23 and the light receiving prism 24 facing the light reduction portion 29 which will be described later below the concave portion 25 is directed downward, but a portion between the light irradiation prism 23 and the light receiving prism 24 is It is composed of planar inclined parts 23b and 24b so as to increase the distance.
- a light reducing portion 29 whose trapezoidal cross section in a direction perpendicular to the inclined portions 23 b and 24 b is in contact with the inclined portions 23 b and 24 b is disposed between the light irradiation prism 23 and the light receiving prism 24.
- Adjustment means for adjusting the distance between the light irradiation prism 23 and the light reception prism 24 is provided on the side surface and the bottom surface of the light irradiation prism 23 and the light reception prism 24.
- the adjustment means includes a screw 21 as a moving element for moving the light reduction part 29 in the vertical direction, a holding part 26 holding the screw 21, and a gap between the holding part 26 and the light irradiation prism 23 and the light receiving prism 24. It is composed of provided deformable deformation elements 27 and 28.
- the screw 21 is disposed below the light reduction unit 29, and the light reduction unit 29 is pushed upward by pushing the light reduction unit 29 from below with the screw 21.
- the distance between the light emitting prism 23 and the light receiving prism 24 can be set small by decreasing the pressing amount, and the distance between the light emitting prism 23 and the light receiving prism 24 increases when the pressing amount is increased. It can be set.
- the deformation elements 27 and 28 elastically absorb the amount of displacement associated with the movement of the light emitting prism 23 and the light receiving prism 24.
- the light irradiation prism 23 and the light reception prism 24 are preferably fixed by tightening with screws from the side surface part, though not shown so that the light irradiation prism 23 and the light reception prism 24 do not move again. Moreover, you may fix using an adhesive agent.
- the moving element is not limited to this.
- a material having elasticity or a spring material can be used as the deformation elements 27 and 28, for example, a material having elasticity or a spring material can be used.
- the material having elasticity is not particularly limited, and for example, acrylic rubber, urethane rubber, silicone rubber, fluororubber, styrene butadiene rubber, butadiene rubber, isoprene rubber, nitrile rubber, chloroprene rubber, butyl rubber and the like can be used.
- the material constituting the holding portion 26 is not particularly limited, but is preferably plastic or metal.
- the metal for example, aluminum or stainless steel is preferable.
- FIG. 6 is a view showing the configuration of an optical measuring apparatus (component concentration measuring apparatus) according to Embodiment 4 of the present invention using the optical element (measuring element) of the present invention, and the arrows in the figure indicate the optical path. .
- the optical element will be described below.
- the description of the portions common to the first embodiment will be omitted.
- the light irradiation prism 13 and the light reception prism 14 are combined via the spacer 39, and the space between the light irradiation prism 13 and the light reception prism 14 is reduced.
- the configuration is the same as that of the first embodiment except that the light portion 19 is provided.
- the refractive index of light at the force gap portion is smaller than the refractive index of the light irradiation prism 13 and the light receiving prism 14, the light passing through the light irradiation prism 13 is received without passing through the sample.
- the amount of light incident on the prism 14 can be reduced. And, it is possible to suppress the arrival of light unnecessary for detection, and it is possible to reliably suppress the decrease in measurement accuracy.
- FIG. 7 is a view showing the configuration of an optical measuring apparatus (component concentration measuring apparatus) according to a fifth embodiment of the present invention using the optical element (measuring element) of the present invention, and the arrows in the figure indicate the optical path. .
- the optical element will be described below.
- the description of the portions common to the second embodiment will be omitted.
- the light irradiation prism 13 and the light reception prism 14 are combined via the spacer 39, and the space between the spacer 39 and the light irradiation prism 13, and the spacer Between the light source 39 and the light receiving prism 14, a light reducing portion 19 formed of a film-like light shielding portion is provided.
- the spacer 39 has a rectangular parallelepiped shape, and the recess 15 is formed in a substantially V shape by a combination of the light irradiation prism 13, the light reception prism 14, the spacer 39, and the light reduction part 19. ing.
- planar first inclined portion 13a in contact with the sample in the light irradiation prism 13 and the planar second inclined portion 14a in contact with the sample in the light receiving prism 14 are disposed to face each other, and are respectively recessed
- the upper surface of the spacer 19 is located between the lower end of the first inclined portion 13a and the lower end of the second inclined portion 14a, and constitutes the bottom of the recess 15.
- the thickness (width) of the spacer 39 it is possible to easily change the optical path of the light passing through the recess 15. That is, if the spacer 39 is thickened, the distance between the light-emitting prism 13 and the light-receiving prism 14 is increased, and the biological tissue deeply penetrates into the concave portion 15, and the biological tissue at a deeper site can be measured. In addition, if the spacer 19 is thinned, the distance between the light irradiation prism 13 and the light reception prism 14 becomes smaller, and the surface tissue can be measured more. By appropriately setting the thickness of the spacer 39 in this manner, it is possible to measure the depth and the measured depth of the living tissue.
- the side surfaces of the recess 15 through which light passes are subjected to optical polishing of the first inclined portion 13a and the second inclined portion 14a to form smooth surfaces, and then to the first inclined portion 13a and the first inclined portion 13a. It can be easily formed by joining the light emitting prism 13 and the light receiving prism 14 with the spacer 39 in between so that the second inclined portions 14 a face each other.
- the first inclined portion 13a and the second inclined portion 13a may be used before the light irradiation prism 13 and the light receiving prism 14 are joined, in order to optically polish the first inclined portion 13a and the second inclined portion 14a of the planar shape, respectively. Can be easily smoothed.
- the material of the spacer 39 is not particularly limited, but a material that absorbs light used for measurement with high mechanical strength and transmits light immediately and is less likely to be reflected is preferable.
- the spacer 39 can be made to have a function as a light reducing portion as described above.
- the thickness (width) of the spacer 39, ie, between the light emitting prism 13 and the light receiving prism 14 is not particularly limited, for example, when measuring a living tissue, the absorption of water becomes too large if the optical path length is too long, so the distance is preferably 3 mm or less.
- the light reduction part 19 the one in the above embodiment can be adopted.
- the first and second inclined portions may be curved to form a substantially U-shaped recess.
- the first sloped portion and the second sloped portion may be stepped to form a stepped recess.
- the force sample described for the case where the sample is a finger is not particularly limited thereto.
- living tissues such as lips, forearms and ears can also be measured.
- the present invention can also measure a fluid which is not limited to this.
- a flow path through which the sample liquid flows in is connected to the side surface corresponding to the recess 15 of the first measurement cover 20a, and a flow path through which the sample liquid flows out to the side surface corresponding to the recess 15 of the second measurement cover 20b.
- the components in the fluid can be easily measured by connecting them and making the recess 15 a passage through which the sample liquid flows.
- optical element and the optical measurement device of the present invention can be suitably used, for example, in a device that measures the concentration of components such as liquid, solution, fluid, and biological tissue.
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Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
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EP06712829A EP1845365A4 (en) | 2005-02-02 | 2006-02-01 | OPTICAL ELEMENT AND OPTICAL MEASURING DEVICE THEREWITH |
US11/547,164 US7598483B2 (en) | 2005-02-02 | 2006-02-01 | Optical element and optical measurement device using the optical element |
JP2006524569A JP4177871B2 (ja) | 2005-02-02 | 2006-02-01 | 光学素子およびそれを用いた光学測定装置 |
Applications Claiming Priority (4)
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JP2005026576 | 2005-02-02 | ||
JP2005-026576 | 2005-02-02 | ||
JP2005034988 | 2005-02-10 | ||
JP2005-034988 | 2005-02-10 |
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WO2006082859A1 true WO2006082859A1 (ja) | 2006-08-10 |
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PCT/JP2006/301686 WO2006082859A1 (ja) | 2005-02-02 | 2006-02-01 | 光学素子およびそれを用いた光学測定装置 |
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US (1) | US7598483B2 (ja) |
EP (1) | EP1845365A4 (ja) |
JP (1) | JP4177871B2 (ja) |
WO (1) | WO2006082859A1 (ja) |
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JP2012105809A (ja) * | 2010-11-17 | 2012-06-07 | Fujitsu Ltd | 生体成分測定装置及び生体成分測定方法 |
JP2018061675A (ja) * | 2016-10-12 | 2018-04-19 | セイコーエプソン株式会社 | 検出装置および測定装置 |
CN112240745A (zh) * | 2019-07-16 | 2021-01-19 | 松下知识产权经营株式会社 | 受光器、投光器以及光电传感器 |
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JP5295584B2 (ja) * | 2008-02-14 | 2013-09-18 | 国立大学法人 筑波大学 | 血流計測装置及び血流計測装置を用いた脳活動計測装置 |
JP4553954B2 (ja) * | 2008-04-25 | 2010-09-29 | 株式会社日本自動車部品総合研究所 | 血中成分濃度測定装置及び血中成分濃度測定方法 |
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CN101953683B (zh) * | 2009-07-14 | 2014-12-10 | 国立大学法人筑波大学 | 血流测量装置及使用该血流测量装置的脑活动测量装置 |
US9289177B2 (en) | 2011-01-20 | 2016-03-22 | Nitto Denko Corporation | Sensing device, a method of preparing a sensing device and a personal mobile sensing system |
EP2543839A1 (fr) * | 2011-07-04 | 2013-01-09 | Inergy Automotive Systems Research (Société Anonyme) | Dispositif de mesure de la concentration d'urée |
EP3111842A1 (en) * | 2015-06-30 | 2017-01-04 | Nokia Technologies Oy | An apparatus comprising a light detector, a light source and optics |
KR102574086B1 (ko) | 2018-02-21 | 2023-09-04 | 삼성전자주식회사 | 라만 프로브 |
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JP2018061675A (ja) * | 2016-10-12 | 2018-04-19 | セイコーエプソン株式会社 | 検出装置および測定装置 |
CN112240745A (zh) * | 2019-07-16 | 2021-01-19 | 松下知识产权经营株式会社 | 受光器、投光器以及光电传感器 |
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EP1845365A1 (en) | 2007-10-17 |
JP4177871B2 (ja) | 2008-11-05 |
EP1845365A4 (en) | 2009-07-01 |
US7598483B2 (en) | 2009-10-06 |
JPWO2006082859A1 (ja) | 2008-06-26 |
US20080265145A1 (en) | 2008-10-30 |
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