WO2016039149A1

WO2016039149A1 - Detection method and detection apparatus

Info

Publication number: WO2016039149A1
Application number: PCT/JP2015/074130
Authority: WO
Inventors: 幸登中村; 真紀子大谷; 鶴紀田村; 洋一青木
Original assignee: コニカミノルタ株式会社
Priority date: 2014-09-10
Filing date: 2015-08-27
Publication date: 2016-03-17
Also published as: JPWO2016039149A1; JP2019032342A; JP6587024B2

Abstract

Provided are a detection method and a detection apparatus by which a physical property of a liquid for detection containing particles or the amount of a substance to be detected can be detected quantitatively at a high S/N ratio with high accuracy. The detection method is a method for detecting a physical property of a liquid for detection which contains particles. The liquid for detection is supplied onto a total reflection surface of an analysis chip having a prism comprising a dielectric and including the total reflection surface, and, with the liquid for detection present on the total reflection surface, the total reflection surface is irradiated with light from the prism side at an incident angle equal to or greater than a critical angle so as to detect the quantity of scattered light emitted from the liquid for detection. The physical property of the liquid for detection is computed on the basis of the quantity of the scattered light.

Description

Detection method and detection apparatus

The present invention relates to a detection method and a detection apparatus for detecting physical properties of a liquid to be detected containing particles or an amount of a substance to be detected in a specimen.

If it is possible to detect (measure) a very small amount of a substance to be detected (a substance to be measured) such as blood protein or DNA in a clinical test or the like, the patient's condition is quickly grasped and treated. It becomes possible. For this reason, a method capable of detecting a minute amount of a substance to be detected with high sensitivity and quantity is demanded.

As a method for detecting a minute amount of a substance to be detected with high sensitivity and quantitatively, an attenuated total reflection (hereinafter also referred to as “ATR”) method is known. In this method, a prism having a total reflection surface is used. Further, the substance to be detected is arranged on the total reflection surface. When light incident on the prism is totally reflected by the total reflection surface, light oozes out of the prism from the total reflection surface. The ATR method utilizes the fact that this exuded light (generally called “evanescent light” or “near-field light”) is absorbed by a substance to be detected (see, for example, Patent Document 1).

The measurement device (detection device) described in Patent Document 1 has an ATR prism including an entrance surface, a total reflection surface, and an exit surface, and can measure cholesterol concentration. The arm of the subject is in close contact with the total reflection surface of the ATR prism. Light emitted from the light source is incident on the incident surface of the ATR prism. Incident light travels while repeating total reflection in the ATR prism and exits on the exit surface. During this time, the skin such as the arm that is in close contact with the total reflection surface absorbs the localized field light unique to the skin. In addition, the absorption of the localized field light varies depending on the cholesterol concentration of the subject. As a result, the measuring device described in Patent Document 1 can measure the cholesterol concentration of the subject by detecting light from the exit surface.

Further, as a method capable of detecting a very small amount of a substance to be detected with high sensitivity, surface plasmon resonance (hereinafter referred to as “SPR”) method and surface plasmon excitation enhanced fluorescence analysis method (Surface Plasmon-field enhanced Fluorescence Spectroscopy: (Hereinafter abbreviated as “SPFS”). These methods utilize the fact that surface plasmon resonance (SPR) occurs when a metal film is irradiated with light under predetermined conditions (see, for example, Patent Document 2).

Patent Document 2 describes a detection device that performs SPR or SPFS using an analysis chip having a prism, a metal film formed on one surface of the prism, and a capturing body fixed on the metal film. Yes. This detection device irradiates light on the back surface of the metal film through the prism to generate SPR in the metal film, and detects the substance to be detected using this SPR. The detection apparatus described in Patent Document 1 includes an angle adjustment unit that scans the incident angle of light on the metal film within a predetermined angle range, and the angle adjustment unit scans the incident angle of light on the metal film. The incident angle (hereinafter also referred to as “resonance angle”) that maximizes the SPR is determined.

JP 2012-132745 A International Publication No. 2014/076926

However, since the measuring apparatus described in Patent Document 1 detects the light emitted from the ATR prism, there is a problem that it is affected by background noise, particularly when the amount of a substance to be detected is very small. Becomes prominent.

Accordingly, a first object of the present invention is to provide a detection method (measurement method) and a detection apparatus capable of detecting the physical properties of a liquid to be detected containing particles or the amount of a substance to be detected in a specimen without being affected by background noise. (Measuring device) is to be provided.

Further, in the detection apparatus described in Patent Document 2, there may be a case where it is desired to irradiate laser light from a region outside the scanning range of the angle adjustment unit for various reasons. In such a case, it is conceivable to cope with the problem by widening the scanning range of the angle adjusting unit. However, when the scanning range of the angle adjusting unit is widened, there is a problem that the apparatus becomes large and the manufacturing cost and detection cost of the apparatus increase. Moreover, since the scanning range of an incident angle becomes wide, there exists a problem that detection time will become long.

Therefore, a second object of the present invention is a detection device having an angle adjustment unit that scans the incident angle of light with respect to a predetermined region of the analysis chip, and the detection chip has a predetermined value from outside the scanning range of the angle adjustment unit. To provide a detection device capable of irradiating light to an area.

In order to realize the first object described above, a detection method according to the first embodiment of the present invention is a method for detecting physical properties of a liquid to be detected including particles, which is made of a dielectric material, and is a total reflection surface. Providing the liquid to be detected on the total reflection surface of the analysis chip having a prism including: the critical reflection from the prism side to the total reflection surface in a state where the liquid to be detected exists on the total reflection surface Irradiating light at an incident angle equal to or greater than the angle, detecting the amount of scattered light emitted from the liquid to be detected, calculating the physical properties of the liquid to be detected based on the amount of scattered light, and Have

In order to achieve the first object described above, the detection device according to the first embodiment of the present invention is a device that detects the physical properties of the liquid to be detected including particles, and is made of a dielectric. A chip holder that detachably holds an analysis chip having a prism including a total reflection surface, a light irradiation unit that irradiates light from the prism side toward the total reflection surface at an incident angle greater than a critical angle, and the detection target A light detection unit that detects the amount of scattered light emitted from the liquid; and a processing unit that calculates physical properties of the liquid to be detected based on a detection result of the light detection unit.

Furthermore, in order to realize the second object described above, the detection apparatus according to the second embodiment of the present invention is generated in the analysis chip by irradiating light to the analysis chip to which the substance to be detected is attached. A detection device that detects the presence or amount of a substance to be detected by detecting a signal, a chip holder that detachably holds the analysis chip, and a light source that irradiates light to a predetermined region of the analysis chip An angle adjustment unit that relatively moves the chip holder and the light source to scan an incident angle of light emitted from the light source within a predetermined angle range with respect to the predetermined region; and the light source An angle switching unit that switches the incident angle of the light emitted from the light source with respect to the predetermined region so that the light emitted from the light enters the predetermined region with an incident angle smaller than the predetermined angle range. , Having a signal detection section for detecting a signal generated in the analysis chip.

According to the first embodiment of the present invention, it is possible to detect the physical property of the liquid to be detected containing the particles with high accuracy and quantitatively or the amount of the substance to be detected in the specimen with a high S / N ratio.

Further, according to the second embodiment of the present invention, it is possible to suppress the increase in the size of the apparatus, the increase in the manufacturing cost of the apparatus, the increase in the detection cost, and the increase in the detection time, and from outside the scanning range of the angle adjusting unit. It is possible to provide a detection device that can irradiate a predetermined region of the analysis chip with light.

FIG. 1 is a diagram illustrating a configuration of the SPFS apparatus according to the first embodiment. FIG. 2 is a flowchart illustrating an example of an operation procedure of the SPFS apparatus according to the first embodiment. FIG. 3 is a graph showing the relationship between the incident angle of excitation light and the amount of plasmon scattered light. 4A and 4B are graphs showing the relationship between the incident angle of excitation light and the amount of plasmon scattered light. FIG. 5 is a graph showing the relationship between the incident angle of excitation light and the coefficient of variation. FIG. 6 is a diagram illustrating a configuration of an SPR device according to a modification of the first embodiment. FIG. 7 is a diagram illustrating a configuration of the SPFS apparatus according to the second embodiment. 8A and 8B are diagrams for explaining switching of the incident angle of light by the angle switching unit. FIG. 9 is a flowchart illustrating an example of an operation procedure of the SPFS apparatus according to the second embodiment. FIG. 10 is a diagram illustrating a configuration of an SPR device according to a modification of the second embodiment.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. Here, a surface plasmon excitation enhanced fluorescence analyzer (SPFS apparatus) using SPFS will be described as a representative example of the detection apparatus (measurement apparatus) according to the present invention. In addition to detecting the amount of the substance to be detected in the specimen, the SPFS device according to the present embodiment determines the physical properties of the liquid to be detected (particle concentration and particle size in the liquid to be detected). It can also be detected. For example, the SPFS device according to the present embodiment can detect the hematocrit value of blood when a specimen containing red blood cells (particles) is used as the liquid to be detected. Therefore, in the following embodiment, when a sample containing at least a part of blood is used, not only the amount of the detected substance in the sample is detected but also the amount of the detected substance corrected by the hematocrit value is calculated. An SPFS device that can be calculated will be described.

[Embodiment 1]
In the first embodiment, a detection apparatus (SPFS apparatus) and a detection method for detecting the physical properties of a liquid to be detected including particles or the amount of a substance to be detected in a specimen without being affected by background noise will be described. . FIG. 1 is a schematic diagram showing a configuration of an SPFS apparatus 100 according to Embodiment 1 of the present invention. As shown in FIG. 1, the SPFS device 100 includes an excitation light irradiation unit 110 (light irradiation unit), a light detection unit 130 (first light detection unit and second light detection unit), a liquid feeding unit 140, and a conveyance. A unit 150 and a control unit 160 are included. The SPFS apparatus 100 is used with the analysis chip 10 mounted on the chip holder 154 of the transport unit 150. Therefore, the analysis chip 10 will be described first, and then each component of the SPFS device 100 will be described.

The analysis chip 10 includes a prism 20 having an incident surface 21, a total reflection surface 22, and an output surface 23, a metal film 30 formed on the total reflection surface 22, and a flow disposed on the total reflection surface 22 or the metal film 30. And a road lid 40. Usually, the analysis chip 10 is replaced for each analysis.

The prism 20 is made of a dielectric that is transparent to the excitation light α. As described above, the prism 20 has the entrance surface 21, the total reflection surface 22, and the exit surface 23. The incident surface 21 causes the excitation light α from the excitation light irradiation unit 110 to enter the prism 20. A metal film 30 is disposed on the total reflection surface 22. The excitation light α incident on the inside of the prism 20 is reflected on the back surface of the metal film 30 and becomes reflected light β (not shown). More specifically, the excitation light α is reflected at the interface (total reflection surface 22) between the prism 20 and the metal film 30 to become reflected light β. The emission surface 23 emits the reflected light β to the outside of the prism 20.

The shape of the prism 20 is not particularly limited. In the present embodiment, the shape of the prism 20 is a column having a trapezoidal bottom surface. The surface corresponding to one base of the trapezoid is the total reflection surface 22, the surface corresponding to one leg is the incident surface 21, and the surface corresponding to the other leg is the emission surface 23. The trapezoid serving as the bottom surface is preferably an isosceles trapezoid. Thereby, the entrance surface 21 and the exit surface 23 are symmetric, and the S wave component of the excitation light α is less likely to stay in the prism 20. The shape of the prism 20 is not particularly limited. In the present embodiment, the prism 20 has a trapezoidal upper base of 8 mm at the bottom and a height of 3 mm.

The incident surface 21 is formed so that the excitation light α does not return to the excitation light irradiation unit 110. When the light source of the excitation light α is a laser diode (hereinafter also referred to as “LD”), when the excitation light α returns to the LD, the excitation state of the LD is disturbed, and the wavelength and output of the excitation light α change. . Therefore, the angle of the incident surface 21 is set so that the excitation light α does not enter the incident surface 21 perpendicularly in an ideal scanning range centered on the resonance angle or the enhancement angle. Here, the “resonance angle” means the incident angle when the amount of the reflected light β emitted from the emission surface 23 is minimum when the incident angle of the excitation light α with respect to the metal film 30 is scanned. The “enhancement angle” refers to scattered light having the same wavelength as the excitation light α emitted above the analysis chip 10 when the incident angle of the excitation light α with respect to the metal film 30 is scanned (hereinafter referred to as “plasmon scattered light”). It means the incident angle when the light quantity of δ is maximized. In the present embodiment, the angle between the incident surface 21 and the total reflection surface 22 and the angle between the total reflection surface 22 and the output surface 23 are both about 80 °.

Note that the resonance angle (and the enhancement angle near the pole) is generally determined by the design of the analysis chip 10. The design factors are the refractive index of the prism 20, the refractive index of the metal film 30, the film thickness of the metal film 30, the extinction coefficient of the metal film 30, the wavelength of the excitation light α, and the like. The resonance angle and the enhancement angle are shifted by the substance to be detected (measurable substance) trapped on the metal film 30, but the amount is less than a few degrees.

The prism 20 has a considerable amount of birefringence. Examples of the material of the prism 20 include resin and glass. The material of the prism 20 is preferably a resin having a refractive index of 1.4 to 1.6 and a small birefringence.

The metal film 30 is disposed on the total reflection surface 22 of the prism 20. As a result, interaction between the photon of the excitation light α incident on the total reflection surface 22 under the total reflection condition and free electrons in the metal film 30 (surface plasmon resonance: hereinafter abbreviated as “SPR”). And local field light (evanescent light) can be generated on the surface of the metal film 30.

The material of the metal film 30 is not particularly limited as long as it is a metal that can cause surface plasmon resonance (SPR). Examples of the material of the metal film 30 include gold, silver, copper, aluminum, and alloys thereof. In the present embodiment, the metal film 30 is a gold thin film. The method for forming the metal film 30 is not particularly limited. Examples of the method for forming the metal film 30 include sputtering, vapor deposition, and plating. The thickness of the metal film 30 is not particularly limited, but is preferably in the range of 30 to 70 nm.

Also, the metal film 30 binds the substance to be detected directly or indirectly. Although not shown in FIG. 1, a capturing body for capturing a substance to be detected is immobilized on the surface of the metal film 30 that does not face the prism 20 (the surface of the metal film 30). Thereby, the metal film 30 can indirectly capture the substance to be detected. By immobilizing the capturing body, it becomes possible to selectively detect the substance to be detected. In the present embodiment, the capturing body is uniformly fixed in a predetermined region (reaction field) on the metal film 30. The type of capturing body is not particularly limited as long as it can capture the substance to be detected. In the present embodiment, the capturing body is an antibody or a fragment thereof that can specifically bind to the substance to be detected.

The flow path lid 40 is disposed on the metal film 30. When the metal film 30 is formed only on a part of the total reflection surface 22 of the prism 20, the flow path cover 40 may be disposed on the total reflection surface 22. A channel groove is formed on the back surface of the channel lid 40, and the channel lid 40 accommodates the liquid together with the metal film 30 (and the prism 20) and a channel (accommodating portion) 41 through which the liquid flows. Form. Examples of the liquid include a specimen (whole blood, plasma, serum, or a diluted solution thereof) containing a substance to be detected, a labeled liquid containing a capturing body labeled with a fluorescent substance, a reference liquid, a washing liquid, and the like. The metal film 30 is exposed in the flow channel 41, and the capturing body fixed to the metal film 30 is exposed in the flow channel 41. Both ends of the channel 41 are respectively connected to an inlet and an outlet (not shown) formed on the upper surface of the channel lid 40. When the liquid is injected into the flow path 41, the liquid contacts the capturing body.

The channel lid 40 is preferably made of a material that is transparent to signals such as fluorescence γ emitted from the metal film 30 and plasmon scattered light δ. An example of the material of the flow path lid 40 includes a resin. As long as the portion from which the fluorescent γ and the plasmon scattered light δ are extracted is transparent to the fluorescent γ and the plasmon scattered light δ, the other portion of the channel lid 40 may be formed of an opaque material. The flow path lid 40 is bonded to the metal film 30 or the prism 20 by, for example, adhesion using a double-sided tape or an adhesive, laser welding, ultrasonic welding, or pressure bonding using a clamp member.

As shown in FIG. 1, the excitation light α enters the prism 20 from the incident surface 21. The excitation light α that has entered the prism 20 enters the metal film 30 at a total reflection angle (an angle at which SPR occurs). By irradiating the metal film 30 with the excitation light α at an angle at which SPR occurs in this way, localized field light can be generated on the metal film 30. This localized field light excites a fluorescent substance that labels the substance to be detected present on the metal film 30, and emits fluorescence γ. The SPFS apparatus 100 detects (measures) the amount of the substance to be detected by detecting (measuring) the amount of the fluorescent γ emitted from the fluorescent substance.

Next, each component of the SPFS device 100 will be described. As described above, the SPFS device 100 includes the excitation light irradiation unit 110, the light detection unit 130, the liquid feeding unit 140, the transport unit 150, and the control unit 160.

The excitation light irradiation unit 110 functions as a light irradiation unit that irradiates the analysis chip 10 held by the chip holder 154 with the excitation light α. Here, “excitation light” is light that directly or indirectly excites a fluorescent substance. For example, the excitation light α is light that generates localized field light on the surface of the metal film 30 that excites the fluorescent material when the metal film 30 is irradiated through the prism 20 at an angle at which SPR occurs. Although details will be described later, the excitation light irradiation unit 110 irradiates the total reflection surface 22 with light at the first incident angle or the second incident angle from the prism 20 side. Here, the first incident angle is an incident angle when the amount of plasmon scattered light δ is detected in order to calculate the hematocrit value, and the second incident angle is used to calculate the amount of the substance to be detected. This is the incident angle when detecting the amount of fluorescence γ. The first incident angle and the second incident angle are both greater than or equal to the critical angle, but the first incident angle is smaller than the second incident angle. When detecting (measuring) the fluorescent γ or the plasmon scattered light δ, the excitation light irradiation unit 110 applies only the P wave on the metal film 30 to the incident surface 21 so that the incident angle on the metal film 30 is an angle causing SPR. Exit toward. The excitation light irradiation unit 110 includes a light source unit 111, a first angle adjustment unit 112, and a light source control unit 113.

The light source unit 111 emits collimated excitation light α having a constant wavelength and light amount so that the shape of the irradiation spot on the back surface of the metal film 30 is substantially circular. The light source unit 111 includes, for example, a light source of excitation light α, a beam shaping optical system, an APC mechanism, and a temperature adjustment mechanism (all not shown).

The type of the light source is not particularly limited, and is, for example, a laser diode (LD). Other examples of light sources include light emitting diodes, mercury lamps, and other laser light sources. When the light emitted from the light source is not a beam, the light emitted from the light source is converted into a beam by a lens, a mirror, a slit, or the like. When the light emitted from the light source is not monochromatic light, the light emitted from the light source is converted into monochromatic light by a diffraction grating or the like. Furthermore, when the light emitted from the light source is not linearly polarized light, the light emitted from the light source is converted into linearly polarized light by a polarizer or the like.

The beam shaping optical system includes, for example, a collimator, a band pass filter, a linear polarization filter, a half-wave plate, a slit, and a zoom means. The beam shaping optical system may include all of these or a part thereof. The collimator collimates the excitation light α emitted from the light source. The band-pass filter turns the excitation light α emitted from the light source into narrowband light having only the center wavelength. This is because the excitation light α from the light source has a slight wavelength distribution width. The linear polarization filter turns the excitation light α emitted from the light source into completely linearly polarized light. The half-wave plate adjusts the polarization direction of the excitation light α so that the P-wave component is incident on the metal film 30. The slit and zoom means adjust the beam diameter, contour shape, and the like of the excitation light α so that the shape of the irradiation spot on the back surface of the metal film 30 is a circle of a predetermined size.

The APC mechanism controls the light source so that the output of the light source is constant. More specifically, the APC mechanism detects the amount of light branched from the excitation light α with a photodiode (not shown) or the like. The APC mechanism controls the input energy by a regression circuit, thereby controlling the output of the light source to be constant.

The temperature adjustment mechanism is, for example, a heater or a Peltier element. The wavelength and energy of the light emitted from the light source may vary depending on the temperature. For this reason, the wavelength and energy of the light emitted from the light source are controlled to be constant by keeping the temperature of the light source constant by the temperature adjusting mechanism.

The first angle adjustment unit 112 adjusts the incident angle of the excitation light α with respect to the metal film 30 (the interface between the prism 20 and the metal film 30 (total reflection surface 22)). The first angle adjustment unit 112 relatively rotates the light source unit 111 and the chip holder 154 to irradiate the excitation light α at a predetermined incident angle toward a predetermined position of the metal film 30 via the prism 20. Let

For example, the first angle adjustment unit 112 rotates the light source unit 111 around an axis orthogonal to the optical axis of the excitation light α (an axis perpendicular to the paper surface of FIG. 1). At this time, the position of the rotation axis is set so that the position of the irradiation spot on the metal film 30 hardly changes even when the incident angle is scanned. By setting the position of the rotation center near the intersection of the optical axes of the two excitation lights α at both ends of the scanning range of the incident angle (between the irradiation position on the total reflection surface 22 and the incident surface 21), the irradiation position Can be minimized.

As described above, of the incident angles of the excitation light α to the metal film 30, the angle at which the amount of plasmon scattered light δ is maximum is the enhancement angle. By setting the incident angle of the excitation light α to the enhancement angle or an angle in the vicinity thereof, it becomes possible to detect (measure) high-intensity fluorescence γ. The basic incident condition of the excitation light α is determined by the material and shape of the prism 20 of the analysis chip 10, the thickness of the metal film 30, the refractive index of the liquid in the flow channel 41, etc. The optimum incident condition varies slightly depending on the type and amount of the light and the shape error of the prism 20. For this reason, it is preferable to obtain an optimal enhancement angle for each detection (measurement) of fluorescence γ.

The light source control unit 113 controls various devices included in the light source unit 111 to control the emission of the excitation light α from the light source unit 111. The light source control unit 113 includes, for example, a known computer or microcomputer including an arithmetic device, a control device, a storage device, an input device, and an output device.

The light detection unit 130 detects fluorescence γ generated by irradiating the metal film 30 with the excitation light α and plasmon scattered light δ generated by irradiating the metal film 30 with the excitation light α. The light detection unit 130 includes a light receiving unit 131, a position switching mechanism 132, and a first sensor control unit 133. In the present embodiment, one light detection unit 130 functions as a first light detection unit that detects plasmon scattered light δ generated by irradiation of the excitation light α to the metal film 30, and It also functions as a second light detection unit that detects fluorescence γ generated by irradiation with excitation light α.

The light receiving unit 131 is arranged in the normal direction of the metal film 30 of the analysis chip 10. The light receiving unit 131 includes a first lens 134, an optical filter 135, a second lens 136, and a first light receiving sensor 137.

The first lens 134 is, for example, a condensing lens, and condenses light emitted from the metal film 30. The second lens 136 is, for example, an imaging lens, and forms an image of the light collected by the first lens 134 on the light receiving surface of the first light receiving sensor 137. The optical path between both lenses is a substantially parallel optical path. The optical filter 135 is disposed between both lenses.

The optical filter 135 guides only the fluorescence component to the first light receiving sensor 137 and removes the excitation light component (plasmon scattered light δ) in order to detect the fluorescence γ with a high S / N ratio. Examples of the optical filter 135 include an excitation light reflection filter, a short wavelength cut filter, and a band pass filter. The optical filter 135 is, for example, a filter including a multilayer film that reflects a predetermined light component, or a color glass filter that absorbs a predetermined light component.

The first light receiving sensor 137 detects fluorescence γ and plasmon scattered light δ. The first light receiving sensor 137 can detect a weak fluorescence γ from a fluorescent substance that labels a very small amount of a substance to be detected, and has high sensitivity. The first light receiving sensor 137 is, for example, a photomultiplier tube (PMT) or an avalanche photodiode (APD).

The position switching mechanism 132 switches the position of the optical filter 135 on or off the optical path in the light receiving unit 131. Specifically, when the first light receiving sensor 137 detects fluorescence γ, the optical filter 135 is disposed on the optical path of the light receiving unit 131, and when the first light receiving sensor 137 detects plasmon scattered light δ, the optical filter 135 is disposed. Is arranged outside the optical path of the light receiving unit 131.

The first sensor control unit 133 detects the output value of the first light receiving sensor 137, manages the sensitivity of the first light receiving sensor 137 based on the detected output value, and the sensitivity of the first light receiving sensor 137 for obtaining an appropriate output value. Control changes and so on. The first sensor control unit 133 is configured by, for example, a known computer or microcomputer including an arithmetic device, a control device, a storage device, an input device, and an output device.

The liquid feeding unit 140 supplies a sample, a labeling liquid, a reference liquid, a cleaning liquid, and the like into the flow path 41 of the analysis chip 10 held by the chip holder 154. The liquid feeding unit 140 includes a liquid chip 141, a syringe pump 142, and a liquid feeding pump drive mechanism 143.

The liquid chip 141 is a container for storing a liquid such as a specimen, a labeling liquid, a reference liquid, or a cleaning liquid. As the liquid chip 141, a plurality of containers are usually arranged according to the type of liquid, or a chip in which a plurality of containers are integrated is arranged.

The syringe pump 142 includes a syringe 144 and a plunger 145 that can reciprocate inside the syringe 144. By the reciprocating motion of the plunger 145, the liquid is sucked and discharged quantitatively. If the syringe 144 can be replaced, the syringe 144 need not be cleaned. For this reason, it is preferable from the viewpoint of preventing contamination of impurities. When the syringe 144 is not configured to be replaceable, it is possible to use the syringe 144 without replacing it by adding a configuration for cleaning the inside of the syringe 144.

The liquid feed pump driving mechanism 143 includes a driving device for the plunger 145 and a moving device for the syringe pump 142. The drive device of the syringe pump 142 is a device for reciprocating the plunger 145, and includes, for example, a stepping motor. The drive device including the stepping motor is preferable from the viewpoint of managing the remaining liquid amount of the analysis chip 10 because it can manage the liquid feeding amount and liquid feeding speed of the syringe pump 142. For example, the moving device of the syringe pump 142 freely moves the syringe pump 142 in two directions, ie, an axial direction (for example, a vertical direction) of the syringe 144 and a direction crossing the axial direction (for example, a horizontal direction). The moving device of the syringe pump 142 is configured by, for example, a robot arm, a two-axis stage, or a turntable that can move up and down.

The liquid feeding unit 140 sucks various liquids from the liquid chip 141 and supplies them to the flow path 41 of the analysis chip 10. At this time, by moving the plunger 145, the liquid reciprocates in the flow path 41 in the analysis chip 10, and the liquid in the flow path 41 is stirred. As a result, it is possible to achieve a uniform concentration of the liquid and promotion of a reaction (for example, an antigen-antibody reaction) in the channel 41. From the viewpoint of performing such an operation, the analysis chip 10 and the syringe 144 are protected by a multilayer film, and the analysis chip 10 and the syringe 144 can be sealed when the syringe 144 penetrates the multilayer film. It is preferable to be configured.

The liquid in the channel 41 is again sucked by the syringe pump 142 and discharged to the liquid chip 141 and the like. By repeating these operations, reaction with various liquids, washing, and the like can be performed, and a target substance labeled with a fluorescent substance can be placed in the reaction field in the flow path 41.

The transport unit 150 transports and fixes the analysis chip 10 to the detection position or the liquid feeding position. Here, the “detection position (measurement position)” is a position where the excitation light irradiation unit 110 irradiates the analysis chip 10 with the excitation light α and the reflected light β generated thereby is detected by the second light receiving sensor 221 (implementation). This is a position where the light detection unit 130 detects fluorescence γ or plasmon scattered light δ. The “liquid feeding position” is a position where the liquid feeding unit 140 supplies a liquid into the flow channel 41 of the analysis chip 10 or removes the liquid in the flow channel 41 of the analysis chip 10. The transfer unit 150 includes a transfer stage 152 and a chip holder 154. The chip holder 154 is fixed to the transfer stage 152 and holds the analysis chip 10 in a detachable manner. The shape of the chip holder 154 is a shape that can hold the analysis chip 10 and does not obstruct the optical paths of the excitation light α, reflected light β, fluorescence γ, and plasmon scattered light δ. For example, the chip holder 154 is provided with an opening through which excitation light α and reflected light β pass. The transfer stage 152 moves the chip holder 154 in one direction and the opposite direction. The transport stage 152 also has a shape that does not obstruct the optical paths of the excitation light α, reflected light β, fluorescence γ, and plasmon scattered light δ. The transfer stage 152 is driven by, for example, a stepping motor.

The control unit 160 controls the first angle adjustment unit 112, the light source control unit 113, the position switching mechanism 132, the first sensor control unit 133, the liquid feed pump drive mechanism 143, and the transport stage 152. The control unit 160 also functions as a processing unit that determines whether the sample is a sample containing blood, that is, whether the sample is blood or a diluted solution of blood, based on the detection result of the light detection unit 130. To do. Furthermore, the control unit 160 also functions as a processing unit that calculates the hematocrit value of blood contained in the sample based on the detection result of the light detection unit 130. The control unit 160 includes, for example, a known computer or microcomputer including an arithmetic device, a control device, a storage device, an input device, and an output device.

Next, the detection operation of the SPFS device 100 (detection method according to Embodiment 1 of the present invention) will be described. As described above, the SPFS device 100 according to the first embodiment detects the physical property (blood hematocrit value) of a specimen (a liquid to be detected) containing red blood cells (particles) and detects the amount of a substance to be detected in the specimen. To do. The SPFS apparatus 100 corrects the amount of the substance to be detected in the specimen using the hematocrit value.

FIG. 2 is a flowchart showing an example of an operation procedure of the SPFS device 100. Steps S20 to S30 (mainly step S30) correspond to the physical property detection method for the liquid to be detected according to the first embodiment. Steps S20 to S80 (mainly steps S30 and S60 to S80) correspond to the detection target substance detection method (measurement method) according to the first embodiment.

First, preparation for detection is performed (step S10). Specifically, the analysis chip 10 is installed in the chip holder 154 of the SPFS device 100. Further, when a humectant is present in the flow channel 41 of the analysis chip 10, the humectant is removed by washing the flow channel 41 so that the capturing body can appropriately capture the substance to be detected.

Next, a reference value used in the calculation of the hematocrit value (step S30) is detected (step S20). Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the liquid feeding position. Thereafter, the control unit 160 operates the liquid feeding unit 140 to introduce the reference liquid in the liquid chip 141 into the flow path 41 of the analysis chip 10. The reference solution is a buffer solution such as phosphate buffered saline (PBS), Tween 20-containing Tris buffered saline (TBS-T), HEPES buffered saline (HBS), or the like. Next, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the detection position. Then, the control unit 160 operates the excitation light irradiation unit 110 and the light detection unit 130 to irradiate the back surface (total reflection surface 22) of the metal film 30 with the excitation light α and the plasmon scattered light δ of the reference liquid. Detect the amount of light. At this time, the incident angle (first incident angle) of the excitation light α with respect to the metal film 30 (total reflection surface 22) is smaller than the incident angle (second incident angle) of the excitation light α in step S70. More specifically, the incident angle (first incident angle) of the excitation light α with respect to the metal film 30 (total reflection surface 22) is preferably greater than the critical angle and less than the enhancement angle (for example, 71 °). It is more preferable that the angle is not less than 64 ° and not more than 64 °. As will be described later, the hematocrit value can be detected with high accuracy by setting the incident angle of the excitation light α to be not less than the critical angle and less than the enhancement angle, more preferably not less than the critical angle and not more than 64 °. Because you can. The control unit 160 arranges the optical filter 135 outside the light path of the light receiving unit 131. The controller 160 operates the excitation light irradiation unit 110 to irradiate the excitation light α at a predetermined incident angle (first incident angle), and operates the light detection unit 130 to operate the plasmon scattered light δ of the reference liquid. The amount of light is detected. This detection value is recorded in the control unit 160 as the light amount (reference value) of the plasmon scattered light δ of the reference liquid.

Next, the hematocrit value of blood contained in the specimen is calculated (step S30). Further, by performing this step, the substance to be detected is captured on the metal film 30 by the antigen-antibody reaction in the flow path 41 (primary reaction).

Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the liquid feeding position. Thereafter, the controller 160 operates the liquid feeding unit 140 to remove the reference liquid in the flow channel 41 of the analysis chip 10 and introduce the sample in the liquid chip 141 into the flow channel 41 (total reflection surface). 22 and the metal film 30). In the flow channel 41, the substance to be detected is captured on the metal film 30 by the antigen-antibody reaction (primary reaction). Next, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the detection position. Thereafter, the control unit 160 operates the excitation light irradiation unit 110 and the light detection unit 130 so that the specimen (a liquid to be detected containing particles) is present on the total reflection surface 22 and the metal film 30. The back surface (total reflection surface 22) 30 is irradiated with excitation light α, and the amount of plasmon scattered light δ of the specimen is detected. This detection value is recorded in the control unit 160 as the light amount (detection value) of the plasmon scattered light δ of the specimen. At this time, the incident angle (first incident angle) of the excitation light α applied to the metal film 30 is the same as the incident angle when the reference value is detected (step S20). As described above, also in the detection of the amount of plasmon scattered light δ of the specimen, the incident angle (first incident angle) of the excitation light α with respect to the metal film 30 (total reflection surface 22) is the excitation light α in step S70. Is smaller than the incident angle (second incident angle). More specifically, the incident angle (first incident angle) of the excitation light α with respect to the metal film 30 (total reflection surface 22) is preferably greater than the critical angle and less than the enhancement angle, and is greater than the critical angle and greater than 64 °. The following is more preferable.

Thereafter, the control unit 160 calculates the physical property of the specimen (the liquid to be detected), that is, the hematocrit value of the blood, based on the detection result of the light detection unit 130. Specifically, the amount of plasmon scattered light δ of the specimen is calculated by subtracting the reference value from the detection value. Next, the control unit 160 applies the amount of the plasmon scattered light δ of the specimen described above to a calibration curve prepared in advance, and calculates the hematocrit value of blood contained in the specimen. In addition, the control part 160 can also calculate the density | concentration and magnitude | size of the particle | grains (red blood cell) contained in a sample (detected liquid) by using a suitable calibration curve.

Next, the enhancement angle used in the measurement of the optical blank value (step S50) and the detection of fluorescence γ (step S70) is measured (step S40). Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the liquid feeding position. Thereafter, the control unit 160 operates the liquid feeding unit 140 to remove the sample from the analysis chip 10, and then introduces the reference liquid in the liquid chip 141 into the flow channel 41 of the analysis chip 10. Next, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the detection position. The controller 160 operates the excitation light irradiation unit 110 to irradiate a predetermined position of the metal film 30 (total reflection surface 22) with the excitation light α, and the first angle adjustment unit 112 causes the metal film 30 (total reflection surface) to be irradiated. The incident angle (for example, 71 ° ± 3 °) of the excitation light α with respect to 22) is scanned. In addition, the control unit 160 controls the first sensor control unit 133 so that the first light receiving sensor 137 detects the plasmon scattered light δ from the vicinity of the metal film 30 (total reflection surface 22). Plasmon scattered light δ from the vicinity of the metal film 30 (total reflection surface 22) reaches the first light receiving sensor 137. As a result, the control unit 160 obtains data including the relationship between the incident angle of the excitation light α and the intensity of the plasmon scattered light δ. Then, control unit 160 analyzes the data and determines an incident angle (intensification angle; 71 ° in the first embodiment) at which the intensity of plasmon scattered light δ is maximized.

Next, the optical blank value used in the detection of fluorescence γ (step S70) is measured (step S50). Here, the “optical blank value” means the amount of background light emitted above the analysis chip 10 in the detection of the fluorescence γ (step S70). Specifically, the light detection unit 130 is operated to irradiate the metal film 30 with the excitation light α, and the output value (optical blank value) of the first light receiving sensor 137 is recorded. At this time, the control unit 160 operates the first angle adjustment unit 112 to set the incident angle of the excitation light α to the enhancement angle (second incident angle). Further, the control unit 160 controls the position switching mechanism 132 to arrange the optical filter 135 in the optical path of the light receiving unit 131. This detected value is recorded in the control unit 160 as an optical blank value.

Next, the target substance captured on the metal film 30 is labeled with a fluorescent substance (secondary reaction; step S60). Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the liquid feeding position. Thereafter, the control unit 160 operates the liquid feeding unit 140 to remove the reference solution from the analysis chip 10, and then removes the liquid (labeled solution) containing the capture body labeled with the fluorescent substance from the flow path of the analysis chip 10. 41. In the flow channel 41, the detection target substance captured on the metal film 30 is labeled with a fluorescent substance by the antigen-antibody reaction. Thereafter, the labeling liquid in the flow path 41 is removed, and the inside of the flow path 41 is cleaned with a cleaning liquid.

Next, the amount of fluorescence γ is detected to obtain a detection value (first signal value) indicating the amount of the substance to be detected in the specimen (step S70). Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the detection position. Thereafter, the control unit 160 operates the excitation light irradiation unit 110 and the light detection unit 130 to irradiate the back surface (total reflection surface 22) of the metal film 30 with the excitation light α, and outputs the first light receiving sensor 137. Record the value. At this time, the control unit 160 operates the first angle adjustment unit 112 to set the incident angle (second incident angle) of the excitation light α to the enhancement angle. Further, the control unit 160 controls the position switching mechanism 132 to arrange the optical filter 135 in the optical path of the light receiving unit 131. The controller 160 subtracts the optical blank value from the detection value, and calculates the amount of fluorescence γ indicating the amount of the substance to be detected in the sample.

The calculated amount of fluorescence γ is converted into the amount of fluorescence γ indicating the amount of the substance to be detected in the liquid component of the specimen using the blood hematocrit value calculated in step S30 (step S80). Specifically, in the case where the specimen is undiluted blood, the calculated fluorescence γ is calculated by multiplying the calculated amount of fluorescence γ by the conversion coefficient c ₁ represented by the following equation (1). Is converted into the amount of fluorescence γ indicating the amount of the substance to be detected. On the other hand, when the specimen is a diluted blood solution, the calculated fluorescence γ is multiplied by the conversion coefficient c ₂ represented by the following equation (2), so that the calculated light intensity of the fluorescence γ It converts into the light quantity of fluorescence (gamma) which shows quantity. Finally, the amount (second signal value) of the substance to be detected in the liquid component of the specimen corresponding to the amount of fluorescence γ is obtained.

Here, Ht is a hematocrit value, and df is a dilution rate of the diluent.

By the above procedure, the amount (second signal value) of the substance to be detected in the liquid component of the specimen can be detected.

In the above description, after the detection of the reference value (step S20), the light quantity of the plasmon scattered light δ with the sample introduced is detected. However, before the reference value is detected (step S20), the amount of plasmon scattered light δ in a state where the sample is introduced may be detected. The detection of the reference value (step S20) may be performed after the primary reaction (step S30) or the measurement of the optical blank value (step S50). Further, the measurement of the optical blank value (step S50) may be performed after the detection of the reference value (step S20).

[Experiment 1]
In Experiment 1, the relationship between the incident angle of the excitation light α to the metal film 30 and the amount of plasmon scattered light δ in samples having different hematocrit values was examined. For comparison, the relationship between the incident angle of the excitation light α to the metal film 30 and the amount of plasmon scattered light δ in the specimen (serum) not containing red blood cells was also examined. FIG. 3 is a graph showing the relationship between the incident angle of the excitation light α to the metal film 30 and the amount of plasmon scattered light δ. The horizontal axis of FIG. 3 is the incident angle (°) of the excitation light α to the metal film 30, and the vertical axis is the light quantity (count) of the plasmon scattered light δ. In FIG. 3, the white circle symbol indicates the experimental result when blood having a hematocrit value of 60% is used, and the black triangular symbol indicates the experimental result when blood having a hematocrit value of 43% is used. The white triangle symbol indicates the experimental result when blood with a hematocrit value of 35% is used, and the black circle symbol indicates the experimental result when serum (hematocrit value is 0%) is used. Yes.

As shown in FIG. 3, when the incident angle of the excitation light α to the metal film 30 is not less than the enhancement angle (71 °), the light amount difference of the plasmon scattered light δ is small between the samples. On the other hand, when the incident angle of the excitation light α was not less than the critical angle and less than the enhancement angle (71 °), the light amount difference of the plasmon scattered light δ was large between samples having different hematocrit values. From this result, it is understood that the incident angle of the excitation light α when detecting the hematocrit value is preferably smaller than the enhancement angle.

[Experiment 2]
In Experiment 2, the case where the incident angle of the excitation light α to the metal film 30 is smaller than the enhancement angle will be described in more detail. The incident angle of the excitation light α to the metal film 30 and the plasmon scattered light in the samples having different hematocrit values. The relationship between δ and the amount of light was examined. Also in this experiment, for comparison, the relationship between the incident angle of the excitation light α to the metal film 30 and the amount of plasmon scattered light δ in plasma was also examined. 4A and 4B are graphs showing the relationship between the incident angle of the excitation light α to the metal film 30 and the amount of plasmon scattered light δ. 4A and 4B, the horizontal axis represents the incident angle (°) of the excitation light α to the metal film 30, and the vertical axis represents the light quantity (count) of the plasmon scattered light δ. FIG. 4B is a graph obtained by subtracting the light amount of plasmon scattered light δ when Tween20-containing Tris buffered saline (TBS-T) is used from the light amount of each plasmon scattered light δ in FIG. 4A. The black circle symbols shown in FIG. 4A show the experimental results when using Tween20-containing Tris-buffered saline (TBS-T). The white circle symbols shown in FIGS. 4A and 4B show the experimental results when using plasma, and the black triangular symbols show the experimental results when using blood with a hematocrit value of 50%. The white triangle symbol indicates the experimental result when blood having a hematocrit value of 40% is used.

As shown in FIG. 4B, the smaller the incident angle of the excitation light α to the metal film 30, the greater the difference in the amount of plasmon scattered light δ between specimens having different hematocrit values. From this result, it can be seen that the incident angle of the excitation light α when detecting the hematocrit value is preferably smaller if it is equal to or greater than the critical angle.

[Experiment 3]
In Experiment 3, the relationship between the incident angle of the excitation light α to the metal film 30 and the variation in the amount of plasmon scattered light δ in the specimen having the same hematocrit value was examined. In Experiment 3, for five specimens having a hematocrit value adjusted to 50%, the plasmon scattered light δ varies when the incident angle of the excitation light α on the metal film 30 is 62 °, 64 °, 66 °, and 68 °. Investigated about. In Experiment 3, the coefficient of variation CV was used as an index of variation. FIG. 5 is a graph showing the relationship between the incident angle of the excitation light α to the metal film 30 and the coefficient of variation CV. The horizontal axis of FIG. 5 is the incident angle (°) of the excitation light α to the metal film 30, and the vertical axis indicates the coefficient of variation CV (%).

As shown in FIG. 5, when the incident angle of the excitation light α to the metal film 30 is 64 ° or less, the coefficient of variation CV is 10% or less (broken line in FIG. 5). From this result, it is understood that the incident angle of the excitation light α when detecting the hematocrit value is preferably smaller than 64 ° if it is equal to or larger than the critical angle.

Thus, the hematocrit value can be accurately detected by irradiating the metal film 30 with the excitation light α at an incident angle smaller than the enhancement angle. The reason is presumed as follows (not limited to this).

First, the component Ex in the direction parallel to the metal film 30 of the electric field E of the excitation light α (x direction; see FIG. 1) is expressed by Expression (3).

Here, θ (°) is an incident angle of the excitation light α to the metal film 30. Therefore, the light intensity ratio R of the component in the direction parallel to the metal film 30 of the excitation light α on the metal film 30 is expressed by the formula (4).

That is, when the incident angle θ of the excitation light α with respect to the metal film 30 decreases, the component Ex in the direction parallel to the metal film 30 of the electric field E in the irradiation region increases.

Further, the component Ez of the electric field E of the excitation light α in the direction perpendicular to the metal film 30 (z direction; see FIG. 1) is proportional to the factor expressed by the equation (5).

Here, ω (1 / s) is the angular frequency of the excitation light α, z (m) is the distance from the metal film 30 in the direction perpendicular to the metal film 30, v is the speed of light in the specimen (m / s), n Is the refractive index of the specimen with respect to the prism. That is, when the incident angle θ of the excitation light α with respect to the metal film 30 decreases, the attenuation of the component Ez in the direction perpendicular to the metal film 30 of the electric field E in the irradiation region decreases. That is, the reach of the electric field Ez in the direction perpendicular to the metal film 30 increases.

As a result, the amount of scattered light (plasmon scattered light δ) increases. In addition, when a scatterer (red blood cell in the present embodiment) having a particle size of about the wavelength of the excitation light α or more is present in the vicinity of the metal film 30, the component of the scattered light traveling toward the first light receiving sensor 137 according to the Mie scattering theory. Increase. As a result, it is considered that the amount of scattered light (plasmon scattered light δ) directed toward the first light receiving sensor 137 increases.

As described above, when the SPFS device 100 according to the present embodiment detects physical properties (particle concentration, particle size, etc., hematocrit value in this embodiment) of a specimen (liquid to be detected) containing particles. The incident angle (first incident angle) of the excitation light α is made smaller than the incident angle (second incident angle) of the excitation light α when detecting the amount of the substance to be detected in the specimen. As a result, the physical properties (hematocrit value in the present embodiment) of the specimen (the liquid to be detected) and the amount of the substance to be detected in the specimen can be detected with high accuracy, and as a result, the hematocrit value is corrected. The amount of the substance to be detected can be calculated with high accuracy. Further, the SPFS apparatus 100 according to the present embodiment does not require a new apparatus for detecting the hematocrit value. Thereby, the apparatus cost can also be suppressed without increasing the size of the SPFS apparatus 100.

[Modification of Embodiment 1]
The detection device according to the modification of the first embodiment is an SPR device 200 using the SPR method. Therefore, the same components as those of the SPFS device 100 according to Embodiment 1 are denoted by the same reference numerals, and description thereof is omitted.

FIG. 6 is a diagram illustrating a configuration of an SPR device 200 according to a modification of the first embodiment. As shown in FIG. 6, the SPR device 200 according to the modification of the first embodiment includes an excitation light irradiation unit 110 (light irradiation unit), a reflected light detection unit 220 (second light detection unit), and a light detection unit. 130 (first light detection unit), a liquid feeding unit 140, a transport unit 150, and a control unit 160. In the modification of the first embodiment, unlike the first embodiment, the light detection unit 130 is only the first light detection unit that detects the plasmon scattered light δ generated by the irradiation of the excitation light α to the metal film 30. Functions (does not function as a second light detection unit). In the modification of the first embodiment, the newly provided reflected light detection unit 220 functions as a second light detection unit that detects the reflected light β generated by irradiating the metal film 30 with the excitation light α.

The reflected light detection unit 220 detects the amount of the reflected light β generated by irradiating the analysis chip 10 with the excitation light α in order to measure the resonance angle. The reflected light detection unit 220 includes a second light receiving sensor 221, a second angle adjustment unit 222, and a second sensor control unit 223.

The second light receiving sensor 221 is arranged on the optical path of the light reflected by the analysis chip 10 and detects the amount of the reflected light β. The type of the second light receiving sensor 221 is not particularly limited. For example, the second light receiving sensor 221 is a photodiode (PD).

The second angle adjustment unit 222 adjusts the position (angle) of the second light receiving sensor 221 according to the incident angle of the excitation light α with respect to the metal film 30. The second angle adjustment unit 222 relatively moves the second light receiving sensor 221 and the chip holder 154 so that the reflected light β is incident on the second light receiving sensor 221.

The second sensor control unit 223 detects the output value of the second light receiving sensor 221, manages the sensitivity of the second light receiving sensor 221 based on the detected output value, and the sensitivity of the second light receiving sensor 221 for obtaining an appropriate output value. Control changes and so on. The second sensor control unit 223 includes, for example, a known computer or microcomputer including an arithmetic device, a control device, a storage device, an input device, and an output device.

Unlike the SPFS device 100 according to the first embodiment, the SPR device 200 according to the modification of the first embodiment reflects the reflected light reflected by the total reflection surface 22 in order to detect the amount of the substance to be detected in the specimen. The amount of β light is detected. Specifically, the control unit 160 operates the excitation light irradiation unit 110 and the reflected light detection unit 220 to irradiate the back surface of the metal film 30 with the excitation light α and records the output value of the second light receiving sensor 221. To do. On the other hand, the SPR device 200 according to the present embodiment detects scattered light from the specimen in the same manner as the SPFS apparatus 100 according to the first embodiment in order to detect the physical properties of the specimen (liquid to be detected) containing particles. Detect the amount of light. As described above, the light detection unit 130 does not detect the light amount of the fluorescence γ and detects only the scattered light (plasmon scattered light δ), and thus does not include the position switching mechanism 132 and the optical filter 135.

Even in the SPR device 200 according to the modification of the first embodiment, the hematocrit value can be detected with high accuracy by reducing the incident angle of the excitation light α to the metal film 30. In the modification of the first embodiment, the measurement of the optical blank value (step S50) and the secondary reaction (step S60) in the first embodiment are not necessary.

As described above, the SPR device 200 according to the modification of the first embodiment has the same effect as the SPFS device 100 according to the first embodiment.

In each of the above embodiments, the SPFS device 100 and the SPR device 200 using the analysis chip 10 having the metal film 30 in order to use surface plasmon resonance (SPR) have been described. However, the detection device according to the present invention is described. The detection method may be a detection device and a detection method using the analysis chip 10 that does not have the metal film 30. In this case, the specimen (the liquid to be detected) is provided not on the metal film 30 but on the total reflection surface 22. Even in this case, the scattered light is emitted from the specimen (the liquid to be detected) on the total reflection surface 22 by the localized field formed by the total reflection of light on the total reflection surface 22. The reflected light β (first signal) including information about the amount of the substance to be detected is detected by the total reflection measurement (ATR) method or the like without using SPR. In addition, when detecting the physical property (eg, hematocrit value) of the liquid to be detected, the ATR method detects light including background light, whereas in the detection method according to the present invention, scattering emitted from the liquid to be detected is detected. Detect light. Therefore, the detection method according to the present invention can eliminate the influence of background noise as compared with the ATR method and the like, and can detect the physical properties of the liquid to be detected and the amount of the substance to be detected with higher accuracy. Can do.

Further, in each of the above embodiments, an example in which a hematocrit value is detected as a physical property of a specimen (a liquid to be detected including particles) has been described. The physical properties are not limited to this. In the detection method and the detection apparatus according to the present invention, for example, the particle size and the concentration of particles in the liquid to be detected can be detected as the physical properties of the liquid to be detected.

[Embodiment 2]
The detection apparatus according to the second embodiment is different from the detection apparatus according to the first embodiment in that the excitation light irradiation unit 310 includes the angle switching unit 114. Therefore, the same components as those of the SPFS device 100 according to Embodiment 1 are denoted by the same reference numerals, and description thereof is omitted. The detection device according to Embodiment 3 is a detection device that detects a substance to be detected by detecting a signal generated by irradiating light.

FIG. 7 is a schematic diagram showing a configuration of a surface plasmon excitation enhanced fluorescence analyzer (SPFS apparatus) 300 according to Embodiment 3 of the present invention. As shown in FIG. 7, the SPFS device 300 includes an excitation light irradiation unit 310 including an angle switching unit 114, a light detection unit (signal detection unit) 130, a liquid feeding unit 140, a transport unit 150, and a control unit. 160.

The angle switching unit 114 of the excitation light irradiation unit 310 switches the incident angle of the excitation light α with respect to the metal film 30. The angle switching unit 114 is used when the first angle adjusting unit 112 is not scanning the incident angle of the excitation light α. The angle switching unit 114 is emitted from the light source so that the excitation light α emitted from the light source enters a predetermined region of the metal film 30 with an incident angle smaller than the angle range scanned by the first angle adjustment unit 112. The incident angle of the excitation light α with respect to a predetermined region of the metal film 30 is switched.

FIG. 8 is a diagram for explaining switching of the incident angle of light by the angle switching unit 114. FIG. 8A is an explanatory diagram when the angle switching unit 114 is arranged on the light source side, and FIG. 8B is an explanatory diagram when the angle switching unit 114 is arranged on the side opposite to the light source. The angle switching unit 114 causes the excitation light α emitted from the light source unit 111 to enter the metal film 30 at an incident angle smaller than the angle range scanned by the first angle adjustment unit 112. The excitation light α whose optical path is switched by the angle switching unit 114 is used for detection of a hematocrit value to be described later.

The position of the angle switching unit 114 is not particularly limited as long as the excitation light α emitted from the light source unit 111 can be incident on the metal film 30 at an incident angle smaller than the scanning range of the first angle adjustment unit 112. The angle switching part 114 may be arrange | positioned at the light source side, and may be arrange | positioned at the opposite side to a light source. Specifically, in the present embodiment, as shown in FIG. 8A, the angle switching unit 114 is arranged on the light source side. That is, in the present embodiment, the angle switching unit 114 is disposed on the optical path of the excitation light α between the light source unit 111 and the prism 20. The excitation light α emitted from the light source unit 111 is switched by the angle switching unit main body 115 so that the incident angle with respect to the metal film 30 is smaller than the scanning range of the first angle adjusting unit 112 and is irradiated to the metal film 30. . As illustrated in FIG. 8B, the angle switching unit 114 may be disposed on the optical path of the reflected light β. In this case, the reflected light β reflected by the metal film 30 is again incident on the metal at an incident angle smaller than the reflected angle of the reflected light β of the excitation light α incident at the smallest incident angle in the scanning range of the first angle adjustment unit 112. The optical path can be switched so as to enter the film 30.

The angle switching unit 114 includes an angle switching unit main body 115 and a moving mechanism 116. The angle switching unit main body 115 switches the incident angle of the excitation light α emitted from the light source unit 111 with respect to the metal film 30. The angle switching unit main body 115 has a plurality of reflecting surfaces. The excitation light α emitted from the light source unit 111 is reflected off the optical path by the first reflecting surface, and is outside the scanning range of the first angle adjustment unit 112 by the second reflecting surface, and from the scanning range. It is further reflected to enter at a small incident angle. The configuration of the angle switching unit main body 115 is not particularly limited as long as it has a plurality of reflecting surfaces and can switch the optical path of the excitation light α as described above. Examples of the angle switching unit main body 115 include a prism and a plurality of mirrors (mirror surfaces). In the present embodiment, the angle switching unit main body 115 is a plurality of mirrors.

The moving mechanism 116 switches the position of the angle switching unit main body 115 on or off the optical path of the excitation light α emitted from the light source. Specifically, when switching the optical path of the excitation light α, the moving mechanism 116 arranges the angle switching unit main body 115 on the optical path of the excitation light α emitted from the light source unit 111. When the optical path of the excitation light α is not switched, the moving mechanism 116 arranges the angle switching unit main body 115 outside the optical path of the excitation light α emitted from the light source unit 111.

Next, the detection operation of the SPFS device 300 will be described. FIG. 9 is a flowchart illustrating an example of an operation procedure of the SPFS apparatus 300.

First, preparation for detection is performed (step S110). Specifically, the analysis chip 10 is installed in the chip holder 154 of the SPFS apparatus 300. Further, when a humectant is present in the flow channel 41 of the analysis chip 10, the humectant is removed by washing the flow channel 41 so that the capturing body can appropriately capture the substance to be detected.

Next, the control unit 160 operates the moving mechanism 116 to place the angle switching unit main body 115 on the optical path of the excitation light α (step S120). Then, the reference value used in the calculation of the hematocrit value (step S150) is detected (step S130).

Specifically, the control unit 160 operates the moving mechanism 116 to place the angle switching unit main body 115 on the optical path of the excitation light α. Further, the control unit 160 operates the transport stage 152 to move the analysis chip 10 to the liquid feeding position. Thereafter, the control unit 160 operates the liquid feeding unit 140 to introduce the reference liquid in the liquid chip 141 into the flow path 41 of the analysis chip 10. The reference solution is a buffer solution such as phosphate buffered saline (PBS), Tween 20-containing Tris buffered saline (TBS-T), HEPES buffered saline (HBS), or the like. Next, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the detection position. And the control part 160 operates the light detection unit 130, and detects the light quantity of the plasmon scattered light (delta) of a reference | standard liquid. At this time, the incident angle of the excitation light α irradiated on the metal film 30 is smaller than the scanning angle of the first angle adjustment unit 112. More specifically, the incident angle of the excitation light α irradiated on the metal film 30 is preferably less than the enhancement angle (for example, 71 °), more preferably not less than the critical angle and not more than 64 °. This is because, as described above, the hematocrit value can be detected with high accuracy by setting the incident angle of the excitation light α to be less than the enhancement angle, and more preferably by setting the incident angle to be not less than the critical angle and not more than 64 °. The control unit 160 arranges the optical filter 135 outside the light path of the light receiving unit 131. The controller 160 operates the light detection unit 130 to detect the light amount of the plasmon scattered light δ while irradiating the excitation light α with a predetermined incident angle smaller than the scanning angle of the first angle adjustment unit 112. This detection value is recorded in the control unit 160 as the light amount (reference value) of the plasmon scattered light δ of the reference liquid.

Next, in the flow channel 41, a substance to be detected is captured on the metal film 30 by an antigen-antibody reaction (primary reaction; step S140). Thereafter, a hematocrit value of whole blood contained in the sample is calculated (step S150).

Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the liquid feeding position. Thereafter, the controller 160 operates the liquid feeding unit 140 to remove the reference liquid in the flow channel 41 of the analysis chip 10 and introduce the sample in the liquid chip 141 into the flow channel 41. In the flow channel 41, the substance to be detected is captured on the metal film 30 by the antigen-antibody reaction (primary reaction). Next, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the detection position. Thereafter, the control unit 160 operates the light detection unit 130 to detect the amount of plasmon scattered light δ. This detected value is recorded in the control unit 160. In the detection of the amount of the plasmon scattered light δ, the incident angle of the excitation light α applied to the metal film 30 is smaller than the scanning angle of the first angle adjustment unit 112. As described above, the incident angle of the excitation light α applied to the metal film 30 is preferably not less than the critical angle and not more than 64 °.

Thereafter, the control unit 160 calculates a hematocrit value of whole blood from the detected value. Specifically, the light quantity of the plasmon scattered light δ of the whole blood is calculated by subtracting the reference value from the detection value. Next, the control unit 160 calculates the hematocrit value of the whole blood contained in the specimen by applying the above-described light amount of the plasmon scattered light δ of the whole blood to a calibration curve prepared in advance.

Next, the control unit 160 operates the moving mechanism 116 to arrange the angle switching unit main body 115 outside the optical path of the excitation light α (step S160). Next, after removing the specimen from the analysis chip 10, the control unit 160 operates the liquid feeding unit 140 to introduce the reference liquid in the liquid chip 141 into the flow path of the analysis chip 10. Thereafter, the control unit 160 measures the enhancement angle (step S170). While irradiating the predetermined position of the metal film 30 (total reflection surface 22) with the excitation light α, the incident angle (71 ° ± 3) of the excitation light α with respect to the metal film 30 (total reflection surface 22) by the first angle adjustment unit 112. Scan °). In addition, the control unit 160 controls the first sensor control unit 133 so that the first light receiving sensor 137 detects the plasmon scattered light δ from the metal film 30 (the surface of the metal film 30 and its vicinity). Plasmon scattered light δ from the metal film (the surface of the metal film 30 and its vicinity) reaches the first light receiving sensor 137. As a result, the control unit 160 obtains data including the relationship between the incident angle of the excitation light α and the intensity of the plasmon scattered light δ. Then, the control unit 160 analyzes the data and determines an incident angle (intensification angle: 71 °) at which the intensity of the plasmon scattered light δ is maximized.

Next, the optical blank value is measured (step S180). Here, the “optical blank value” means the amount of background light emitted above the analysis chip 10 in the detection of fluorescence γ (step S200). Specifically, the control unit 160 operates the excitation light irradiation unit 310 to irradiate the metal film 30 with the excitation light α and records the output value (optical blank value) of the first light receiving sensor 137. At this time, the control unit 160 operates the first angle adjustment unit 112 to set the incident angle of the excitation light α to the enhancement angle. Further, the control unit 160 controls the position switching mechanism 132 to arrange the optical filter 135 in the optical path of the light receiving unit 131. This detected value is recorded in the control unit 160 as an optical blank value.

Next, the substance to be detected captured on the metal film 30 is labeled with a fluorescent substance (secondary reaction; step S190). Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the liquid feeding position. Thereafter, the control unit 160 operates the liquid feeding unit 140 to introduce a liquid (labeled liquid) containing a capturing body labeled with a fluorescent substance into the flow channel 41 of the analysis chip 10. In the flow channel 41, the detection target substance captured on the metal film 30 is labeled with a fluorescent substance by the antigen-antibody reaction. Thereafter, the labeling liquid in the flow path 41 is removed, and the inside of the flow path is cleaned with a cleaning liquid.

Next, the amount of fluorescence γ is detected to obtain a detection value indicating the amount of the substance to be detected in the sample (step S200). Specifically, the control unit 160 operates the transfer stage 152 to move the analysis chip 10 to the detection position. Thereafter, the control unit 160 operates the excitation light irradiation unit 310 and the light detection unit 130 to irradiate the metal film 30 with the excitation light α and record the output value of the first light receiving sensor 137. At this time, the control unit 160 operates the first angle adjustment unit 112 to set the incident angle of the excitation light α to the enhancement angle. Further, the control unit 160 controls the position switching mechanism 132 to arrange the optical filter 135 in the optical path of the light receiving unit 131. The controller 160 subtracts the optical blank value from the detection value, and calculates the amount of fluorescence γ indicating the amount of the substance to be detected in the sample.

The calculated amount of fluorescence γ is converted into the amount of fluorescence γ indicating the amount of the substance to be detected in the liquid component of the specimen using the hematocrit value of whole blood calculated in step S140 (step S210). Specifically, in the case where the specimen is whole blood that has not been diluted, the calculated fluorescence is obtained by multiplying the calculated amount of fluorescence γ by the conversion coefficient c ₁ represented by the above formula (1). The amount of γ is converted into the amount of fluorescence γ indicating the amount of the substance to be detected. On the other hand, when the sample is a diluted solution of whole blood, the calculated fluorescence γ is multiplied by the conversion coefficient c ₂ represented by the above-described equation (2), thereby calculating the light amount of the calculated fluorescence γ. It converts into the light quantity of the fluorescence (gamma) which shows the quantity. Finally, the amount of the substance to be detected corresponding to the amount of fluorescence γ is obtained. With the above procedure, the amount of the substance to be detected in the liquid component of the specimen can be detected.

In the above description, after the detection of the reference value (step S130), the light quantity of the plasmon scattered light δ in the state where the specimen is introduced is detected. However, the light quantity of the plasmon scattered light δ in a state where the specimen is introduced may be detected before the detection of the reference value (step S130). The detection of the reference value (step S130) may be performed after the primary reaction (step S140) or the measurement of the optical blank value (step S180). Further, the measurement of the optical blank value (step S180) may be performed after the detection of the reference value (step S130).

As described above, according to the SPFS apparatus 300 according to the present embodiment, the angle of the excitation light α is smaller than the scanning range of the first angle adjustment unit 112 on the optical path of the excitation light α irradiated from the light source unit 111. An angle switching unit 114 that switches to an angle can be arranged. Thereby, it is possible to irradiate a predetermined region of the analysis chip 10 from outside the scanning range without increasing the size of the SPFS device 300. Further, the hematocrit value can be detected with high accuracy, and the amount of the substance to be detected can be corrected with high accuracy using the hematocrit value.

[Modification of Embodiment 2]
The detection device according to the modification of the second embodiment is an SPR device 400 using the SPR method. Therefore, the same components as those of the SPFS device 300 according to the modification of the second embodiment are denoted by the same reference numerals, and the description thereof is omitted.

FIG. 10 is a diagram illustrating a configuration of an SPR device 400 according to a modification of the second embodiment. As shown in FIG. 10, the SPR device 400 according to the modification of the second embodiment includes an excitation light irradiation unit 310, a reflected light detection unit 220, a light detection unit 130, a liquid feeding unit 140, a transport unit 150, and a control unit. 160.

The second angle adjustment unit 222 adjusts the position (angle) of the second light receiving sensor 221 according to the incident angle of the excitation light α with respect to the metal film 30. The second angle adjusting unit 222 relatively rotates the second light receiving sensor 221 and the chip holder 154 so that the reflected light β is incident on the second light receiving sensor 221.

Thus, even in the SPR device 400 according to the fourth embodiment, the hematocrit value can be detected with high accuracy by reducing the incident angle of the excitation light α to the metal film 30 by the angle switching unit 114.

Also in the modification of the second embodiment, the angle switching unit 114 may be disposed on the opposite side to the light source unit 111. In this case, the reflected light β reflected by the metal film 30 is again at a smaller angle than the reflected light β of the excitation light α incident at the smallest incident angle in the scanning range of the first angle adjustment unit 112, and the back surface of the metal film 30 again. The optical path can be switched so as to be incident on.

As described above, the SPR device 400 according to the present embodiment has the same effects as the SPFS device 100 according to the third embodiment.

In the second embodiment and the modification of the second embodiment, the example is shown in which the SPRS device 300 and the SPR device 400 using SPR are used as the detection device, but the analysis chip in which the metal film 30 is not disposed. You may apply to the detection system which uses. In this case, the detection apparatus detects (measures) the total reflection measurement (ATR) method or the like without using SPR, but the same effects as those of the second embodiment and the modification of the second embodiment can be obtained.

This application claims priority based on Japanese Patent Application No. 2014-184189 filed on September 10, 2014 and Japanese Patent Application No. 2014-184197 filed on September 10, 2014. The contents described in the application specification and the drawings are all incorporated herein.

The detection (measuring device) according to the present invention can detect (measure) a substance to be detected (measurable substance) in blood with high reliability, and is useful for clinical examinations, for example.

DESCRIPTION OF SYMBOLS 10 Analysis chip 20 Prism 21 Incident surface 22 Total reflection surface 23 Output surface 30 Metal film 40 Channel cover 41

Channel

100, 300

SPFS apparatus

110, 310 Excitation light irradiation unit 111 Light source unit 112 First angle adjustment unit 113 Light source control unit 114 angle switching unit 115 angle switching unit main body 116 moving mechanism 130 light detection unit 131 light receiving unit 132 position switching mechanism 133 first sensor control unit 134 first lens 135 optical filter 136 second lens 137 first light receiving sensor 140 liquid feeding unit 141 Liquid chip 142 Syringe pump 143 Liquid feed pump drive mechanism 144 Syringe 145 Plunger 150 Transport unit 152 Transport stage 154 Chip holder 160

Control unit

200, 400 SPR device 220 Shako detection unit 221 second light receiving sensor 222 second angle adjusting section 223 second sensor controller α excitation light β reflected light γ fluorescent δ plasmon scattered light

Claims

A method for detecting physical properties of a liquid to be detected containing particles,
Providing the liquid to be detected on the total reflection surface of the analysis chip made of a dielectric and having a prism including the total reflection surface;
In the state where the liquid to be detected is present on the total reflection surface, light is irradiated from the prism side to the total reflection surface at an incident angle greater than a critical angle, and the amount of scattered light emitted from the liquid to be detected is calculated. Detecting step;
Calculating physical properties of the liquid to be detected based on the amount of scattered light;
A detection method.
The analysis chip further includes a metal film disposed on the total reflection surface,
The liquid to be detected is provided on the metal film;
The detection method according to claim 1.
The detection method according to claim 1 or 2, wherein the physical property of the liquid to be detected is a concentration of the particles in the liquid to be detected.
The liquid to be detected includes at least a part of blood,
The physical property of the liquid to be detected is a hematocrit value of blood in the liquid to be detected.
The detection method according to claim 3.
The detection method according to claim 1 or 2, wherein the physical property of the liquid to be detected is the size of the particles in the liquid to be detected.
A method for detecting an amount of a substance to be detected in a specimen containing at least a part of blood,
The analyte is provided on the total reflection surface of an analysis chip made of a dielectric and having a prism including a total reflection surface, and the target substance contained in the sample is directly or indirectly provided on the total reflection surface. Bonding to
In the state where the sample is present on the total reflection surface, light is irradiated from the prism side to the total reflection surface at a first incident angle equal to or greater than a critical angle, and the amount of scattered light emitted from the sample is detected. And determining a hematocrit value of the blood using a detection value of the amount of the scattered light,
In a state where the substance to be detected is directly or indirectly bonded to the total reflection surface and the sample is not present on the total reflection surface, a first angle greater than a critical angle is formed from the prism side to the total reflection surface. Irradiating light at an incident angle of 2, and detecting the amount of fluorescent light emitted from the fluorescent substance that labels the substance to be detected or the amount of reflected light reflected by the total reflection surface, and detecting the quantity of the target in the specimen. Obtaining a first signal value indicative of the amount of the detection substance;
Using the hematocrit value of the blood to convert the first signal value into a second signal value indicating the amount of the substance to be detected in the liquid component of the specimen;
Have
The first incident angle is smaller than the second incident angle;
Detection method.
The analysis chip further includes a metal film disposed on the total reflection surface,
The specimen is provided on the metal film;
The detection method according to claim 6, wherein the first incident angle is equal to or greater than a critical angle with respect to the total reflection surface and less than an enhancement angle at which a plasmon scattered light amount from the metal film is maximized.
The detection method according to claim 7, wherein the first incident angle is not less than a critical angle with respect to the total reflection surface and not more than 64 °.
An apparatus for detecting physical properties of a liquid to be detected containing particles,
A chip holder made of a dielectric material and detachably holding an analysis chip having a prism including a total reflection surface;
A light irradiator that irradiates light at an incident angle greater than a critical angle from the prism side toward the total reflection surface;
A light detection unit for detecting the amount of scattered light emitted from the liquid to be detected;
A processing unit that calculates physical properties of the liquid to be detected based on a detection result of the light detection unit;
Including a detection device.
The detection apparatus according to claim 9, wherein the physical property of the liquid to be detected is a concentration of the particles in the liquid to be detected.
The liquid to be detected includes at least a part of blood,
The physical property of the liquid to be detected is a hematocrit value of blood in the liquid to be detected.
The detection device according to claim 10.
10. The detection device according to claim 9, wherein the physical property of the liquid to be detected is the size of the particles in the liquid to be detected.
An apparatus for detecting the amount of a substance to be detected in a specimen containing at least a part of blood,
A chip holder made of a dielectric material and detachably holding an analysis chip having a prism including a total reflection surface;
A light irradiation unit configured to irradiate light from the prism side at a first incident angle or a second incident angle that is greater than a critical angle with respect to the total reflection surface;
A first light detection unit for detecting the amount of scattered light emitted from the vicinity of the total reflection surface;
A second light detection unit that detects the amount of fluorescent light emitted from the fluorescent substance that labels the substance to be detected, or the amount of reflected light reflected by the total reflection surface;
Based on the detection result of the first light detection unit, the hematocrit value of the blood in the sample is calculated, and based on the detection result of the second light detection unit, the detection target substance in the sample is calculated. A first signal value indicating the amount is calculated, and the first signal value is converted into a second signal value indicating the amount of the substance to be detected in the liquid component of the sample based on the hematocrit value. A processing unit;
Have
The processor is
When the light is incident on the total reflection surface from the prism side at the first incident angle in a state where the specimen is present on the total reflection surface, the first light detection unit is Based on the amount of scattered light emitted from the vicinity of the detected total reflection surface, the hematocrit value is calculated,
In a state where the substance to be detected is directly or indirectly bonded to the total reflection surface and the sample is not present on the total reflection surface, the light irradiation unit is moved from the prism side to the total reflection surface. The amount of fluorescence emitted from the vicinity of the total reflection surface detected by the second light detection unit when light is incident at the second incident angle, or the reflection reflected by the total reflection surface Calculate the first signal value based on the amount of light,
The first incident angle is smaller than the second incident angle;
Detection device.
The detection device according to claim 13, wherein the first light detection unit and the second light detection unit are the same light detection unit.
The analysis chip further includes a metal film disposed on the total reflection surface,
The substance to be detected binds directly or indirectly to the metal film,
The first incident angle is equal to or greater than a critical angle with respect to the total reflection surface and less than an enhancement angle at which the amount of plasmon scattered light from the metal film is maximized.
The detection device according to claim 13 or claim 14.
The detection device according to claim 15, wherein the first incident angle is not less than a critical angle with respect to the total reflection surface and not more than 64 °.
A detection device that detects the presence or amount of a substance to be detected by irradiating light to the analysis chip to which the substance to be detected is attached and detecting a signal generated in the analysis chip,
A chip holder for detachably holding the analysis chip;
A light source for irradiating light on a predetermined region of the analysis chip;
An angle adjustment unit that relatively moves the chip holder and the light source and scans an incident angle of light emitted from the light source within a predetermined angle range with respect to the predetermined region;
An angle switching unit that switches an incident angle of the light emitted from the light source with respect to the predetermined region so that the light emitted from the light source enters the predetermined region with an incident angle smaller than the predetermined angle range;
A signal detection unit for detecting a signal generated in the analysis chip;
A detection device.
The detection device according to claim 17, wherein the angle switching unit is disposed on an optical path between the light source and the analysis chip, or is disposed on an optical path of light reflected by the analysis chip.
The detection device according to claim 18, wherein the angle switching unit has a plurality of reflection surfaces.
The detection device according to claim 19, wherein the angle switching unit is a plurality of mirror surfaces or prisms.
The analysis chip includes a prism and a metal film that is disposed on one surface of the prism and to which the detection target material is directly or indirectly attached on the opposite side of the surface facing the prism.
The light source irradiates light on the back surface of the metal film through the prism,
The angle adjustment unit scans an incident angle of light emitted from the light source within the predetermined angle range with respect to a back surface of the metal film,
The angle switching unit is configured to make the light emitted from the light source incident on the back surface of the metal film so that the light emitted from the light source is incident on the back surface of the metal film at an incident angle smaller than the predetermined angle range. Switch corners,
The signal detection unit detects plasmon scattered light emitted from the vicinity of the metal film and fluorescence emitted from a fluorescent substance that labels the substance to be detected.
The detection device according to any one of claims 17 to 20.
The detection apparatus according to claim 21, wherein an incident angle of light with respect to the back surface of the metal film switched by the angle switching unit is not less than a critical angle and not more than 64 °.