JP2000171391A - Spr sensor cell and immune reaction measuring device using it - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an SPR sensor cell and an immune reaction measuring device using it capable of quickly making immune reaction measurement for plural specimens with a simple structure. SOLUTION: This SPR sensor cell 3 includes a hollow cylindrical specimen cell 5 for storing a designated specimen, a first cover member 7a and a second cover member 7b for sealing an opening of the specimen cell 5, and a sensor optical fiber 9 mounted on one of the cover members 7a, 7b, where one end face of the sensor optical fiber 9 is exposed to the outside, an SPR sensor part 9d is formed in the other end area of the sensor optical fiber 9, and the SPR sensor part 9d is dipped in the specimen.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an immunological reaction measuring device, and more particularly to a so-called surface plasmon resonance (Surface) device.
The present invention relates to an SPR sensor cell utilizing the phenomenon of Plasmon Resonance (hereinafter abbreviated as "SPR") and an immunoreaction measuring device using the same.

[0002]

2. Description of the Related Art Conventionally, in the field of biochemical analysis, immunoassay has been widely used as a method for detecting an extremely small amount of protein in a specimen. In this immunization method, a predetermined antigen concentration in a specimen is quantified by a specific immune reaction between an antigen (a protein to be detected) and an antibody (an antibody produced using the antigen). This immunization method can measure a sample in which a plurality of types of antigens are mixed without isolating the antigen to be detected. This is different from the chemical measurement method or the physical measurement method.

[0003] Among the immunization methods, there are various methods as described below. radio immunoassay: RIA (radioimmunoassay) enzyme immunoassay: EIA (enzyme immunoassay) fluoroimmunassay: FIA (fluorescence immunoassay)

[0004] Since the RIA method requires the use of an isotope, it has not been widely used recently. Also, EI
The method A is widely used at present because the immune reaction can be easily measured. Furthermore, the FIA method is positioned as a highly sensitive and highly accurate measurement method. Among the EIA methods, a method using a solid phase for antibody measurement, particularly ELISA (enzymelinke)
d immunosorbent assay), and the ELISA has the following two methods.

A. Indirect method: a method using an antigen as a solid phase b. Antibody capture method: a method using an anti-IgM antibody as a solid phase

[0006] The above-mentioned ELISA method is used for quantification of an antibody against a specific pathogen, quantification of an antibody against an allergen, and screening of a monoclonal antibody. The measurement kit used for the ELISA method includes:
Generally, a microplate in which 96 concave portions are formed is used, and an immunoreaction measurement is performed on this microplate. Therefore, a large number of samples can be measured at the same time, and in recent years, many automated immune reaction measuring devices have been on the market.

As reagent kits for ELISA, various reagent manufacturers provide various reagents. For example, there is tPA, an enzyme that acts indirectly in the direction of dissolving fibrin involved in blood coagulation and thrombus in blood. PAI-1 is an enzyme that suppresses tPA and acts in the direction of blood coagulation and thrombus formation.

By the way, a so-called SPR sensor is known as a sensor used in an immune reaction measuring device.
This SPR sensor is a sensor using the surface plasmon resonance phenomenon, and an immune reaction is measured based on the following principle.
That is, a metal thin film (such as gold or silver) having a thickness of about 50 nm is deposited on the bottom surface of the prism having a high refractive index. Then, predetermined light is incident from the prism side toward the metal thin film at an angle equal to or greater than the critical angle. Since the metal thin film is translucent at about 50 nm, the light incident from the prism side passes through the metal thin film, reaches the surface of the metal thin film on the side opposite to the prism, and reaches the surface of the metal thin film on the side opposite to the prism. Generate an evanescent field.

By adjusting the incident angle of light, the wave number of the evanescent field and the wave number of surface plasmon resonance can be matched, and surface plasmon resonance can be excited on the surface of the metal thin film. In this case, the wave number of surface plasmon resonance depends on the dielectric constant of the metal thin film and the refractive index of the substance fixed on the surface opposite to the prism when viewed from the metal thin film. Therefore, the refractive index and the dielectric constant with respect to the fixed substance can be checked. As described above, since the optical system and the sample are located on opposite sides of the metal thin film as a boundary, it is easy to construct a sensor.

By applying the above principle, an SPR sensor for an immune reaction measuring device using an optical fiber has been developed (B
Manufactured by IACORE-trade name: BIACORE Probe). In the SPR sensor using this optical fiber, first, the clad on the outer peripheral surface of the distal end portion of the optical fiber is removed, and the end surface of the distal end of the optical fiber is cut or polished. Coated. Further, the outer peripheral surface of the tip region of the optical fiber is coated with a metal thin film (such as gold or silver). Further, the metal thin film on the outer peripheral surface of the distal end of the optical fiber is covered with a dielectric film, and the antibody used for the immunological reaction measurement is fixed on the dielectric film. Further, light from a predetermined light source can be introduced into the other end of the optical fiber.

A method for measuring the immune response of the SPR sensor having the above-described configuration will be described. First, as for light introduced into the optical fiber, light of a specific wavelength excites surface plasmon resonance at the tip of the optical fiber. The wavelength of the light that excites the surface plasmon resonance changes depending on the refractive indices of the dielectric film and the antibody. The intensity of light having a wavelength that causes surface plasmon resonance is attenuated. Therefore, by comparing the wavelength of light that attenuates the most before the immune reaction and the wavelength of light that attenuates the most after the immune reaction, the immune reaction can be measured.

[0012]

However, each of the above-mentioned prior arts has the following disadvantages. That is, when the SPR sensor is configured by an optical fiber, the SPR sensor and the immune reaction measuring device are conventionally configured by using one optical fiber. For this reason, when measuring the immune reaction of many kinds of specimens, or when performing the measurement of the immune reaction of multiple items for one specimen, the sensing unit of the optical fiber must be replaced each time. Therefore, there has been an inconvenience that it takes a long time to perform a series of immune reaction measurements.

Also, the SPR sensor cell and the immunoreactivity measuring device using the prism have the following disadvantages. That is, a prism type SPR sensor that emits light of a short wavelength is used as a light source. The immune reaction measurement is performed using the relationship between the incident angle of light and the light intensity. For this reason, there has been an inconvenience that a special drive unit for appropriately adjusting the incidence of light on the prism is required.

[0014]

An object of the present invention is to improve the disadvantages of the prior art and, in particular, to provide an SPR sensor cell capable of rapidly measuring the immunoreactivity of a plurality of specimens with a simple structure, and an immunoreactivity measurement device using the same. The purpose is to provide.

[0015]

In order to achieve the above object, according to the present invention, in order to construct an SPR sensor cell, a hollow cylindrical sample cell for storing a predetermined sample and an opening of the sample cell are provided. A first cover member and a second cover member for sealing the sensor, and a sensor optical fiber mounted on one of the cover members, and exposing one end end face of the sensor optical fiber to the outside from the cover member. In addition, an SPR sensor section is formed in the other end area of the sensor optical fiber, and the SPR sensor section is immersed in the sample.

With the above-described configuration, when measuring an immune reaction, a sample to be measured is first injected into a sample cell. The sample is injected using a micropipette by removing the first lid member or the second lid member, or through a through hole formed in the first lid member. This allows
The sample comes into contact with the SPR sensor section formed on the sensor optical fiber. An antibody (or antigen) is fixed to the SPR sensor via a dielectric film. Therefore, if an antigen (or antibody) specifically reacting with the aforementioned antibody (or antigen) is contained in the specimen, an immune reaction occurs.

When light is introduced into the sensor optical fiber when an immune reaction occurs, the light intensity of light of a specific wavelength is attenuated in response to the immune reaction. Therefore, by introducing light passing through the sensor optical fiber into the spectroscope and analyzing the wavelength distribution of the light, it is possible to measure an immune reaction.

[0018]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS One embodiment of the present invention will be described with reference to the drawings. First, FIG. 1A shows the S of the present embodiment.
It is sectional drawing which assembled the PR sensor cell 3. FIG. 2 shows a sensor optical fiber 9 used in the SPR sensor cell 3. FIG. 2 is an exploded perspective view of the SPR sensor cell 3, and FIG. The SPR sensor cell 3 includes a hollow cylindrical sample cell 5 and a first cell that seals one opening of the sample cell 5.
, A second lid member 7b for sealing the other opening, and a sensor optical fiber 9 mounted on the second lid member 7b. Hereinafter, these will be described in detail.

[Sample Cell] The sample cell 5 has a hollow cylindrical shape. The material of the sample cell 5 is plastic.
However, since the sample cell 5 is for storing a sample therein, as described later, the shape and material are not particularly limited. For example, the shape may be a square pole or a cone, or the material may be metal or glass.

Further, around each opening of the sample cell 5,
Predetermined flange portions 5a and 5b are formed. Of these flange portions 5a and 5b, the flange portion 5a on the first lid member 7a side is used.
Is used when the SPR sensor cell 3 is mounted on a cell fixing base (not shown) as described later. In the present embodiment, the flanges 5a and 5b are formed integrally with the sample cell 5. However, the flanges 5a and 5b are formed separately from the upper part of the hollow cylinder of the sample cell 5, and the collars 5
a and 5b may be joined to the sample cell 5.
In addition, if the cell fixing base has a special structure and can fix the sample cell 5 reliably, the flange portions 5a and 5b can be omitted.

[Each Lid Member] The lid members 7a and 7b seal the respective openings of the sample cell 5, and have a circular shape substantially equal to the inner diameter of the opening of the sample cell 5. As a specific shape, the first lid member 7a includes a fitting portion 7a1 fitted into the inside of the sample cell 5, a disk-shaped locking portion 7a2 that comes into contact with the flange portion 5a of the sample cell 5, and Consists of However, in the present embodiment, the fitting portion 7a1 and the locking portion 7a2 are integrally formed of plastic.

Here, the first lid member 7a is not particularly formed with a through hole or the like. However, in the case where the sample is injected into the SPR sensor cell 3 without removing the first lid member 7a, the following configuration is also desirable. That is, as shown in FIG. 1B, a through hole 7ab is formed in the first lid member 7aa. The reason why the through-hole 7ab is formed is to inject the sample from the through-hole 7ab and at the same time to bleed the air in the sample cell 5 from the through-hole 7ab.

The through hole 7ab formed in the first lid member 7aa only needs to be able to discharge the air in the sample cell 5 while injecting the sample. Therefore, the shape of the through hole 7ab does not need to be cylindrical. May be formed in a tapered shape.

The first lid member is made of a material having a light transmittance which is transparent or equivalent to a transparent one. This is because, as described later, the light incident on the sensor optical fiber passes through the first lid member and is incident on a spectroscope described later. However, the above-described sample injection through hole 7a
b may also serve as a light transmitting hole. in this way,
By providing the light transmitting hole, it is not necessary to configure the first lid member with a transparent member.

On the other hand, the specific shape of the second lid member 7b is substantially the same as that of the first lid member 7a. That is, the second lid member 7b includes a fitting portion 7b1 fitted into the sample cell 5 and a disk-shaped locking portion 7b2 that comes into contact with the flange portion 5b of the sample cell 5 described above. However, in the present embodiment, the fitting portion 7b1 and the locking portion 7b2 are integrally formed of plastic.

Further, an optical fiber fixing hole 7c for fixing the sensor optical fiber 9 is formed substantially in the center of the second lid member 7b. The optical fiber fixing hole 7c is
When the sensor optical fiber 9 is fixed, the sensor optical fiber 9
Reaches the vicinity of the first lid member 7a through the sample cell 5. This sensor optical fiber 9 is used as an SPR sensor, and will be described later in detail.

As described above, the lid members 7a and 7b are made of plastic in the present embodiment, but may be made of other materials (metal, glass, ceramics, etc.). Further, the surfaces of the lid members 7a and 7b may be covered with a light absorbing agent (for example, black ink). This is to prevent unnecessary light from entering the sample cell 5 from each of the lid members 7a and 7b, and to improve the accuracy of the immune reaction measurement.
However, even in this case, it is necessary to configure the position where the light is emitted from the sensor optical fiber 9 so that the light can be transmitted.

Although one optical fiber fixing hole 7c is formed in the second lid member 7b, the present invention is not limited to this. That is, a plurality of sensor optical fibers may be fixed. By immobilizing different antibodies (or antigens) on the surfaces of a plurality of optical fibers for sensors, and bringing the samples into contact with the optical fibers for sensors, it is possible to measure a variety of immunoreactions for one type of sample. Can be performed quickly.

[Sensor Optical Fiber] As shown in FIG. 2, the SPR sensor of this embodiment is a sensor optical fiber 9
It is constituted by. FIG. 2 shows an optical fiber 9 for a sensor.
The difference in thickness of each part is
It is emphasized for clarity. The sensor optical fiber 9 used in the present embodiment is a general one. That is, at the center of the sensor optical fiber 9, there is a core 9a for transmitting light. The outer peripheral surface of the core 9a is covered with a clad 9b having a different refractive index from the core. Further, a primary coating 9c as a protective film is formed on the outer peripheral surface of the clad 9b.

The material of the core 9a is a general one. Specifically, it is glass or transparent plastic. The cladding 9b is also made of glass or plastic. Further, the primary coating 9c is made of plastic.
The material of the core 9a is not particularly limited as long as it can transmit light. That is, any material having a predetermined transparency can be applied to the present invention.

One end region of the sensor optical fiber 9 (FIG. 1)
(A) is an SPR sensor section 9d. More specifically, after the primary coating 9c and the cladding 9b are removed, the outer peripheral surface of the core 9a is coated with a metal thin film 9e. Various materials can be considered as the material of the metal thin film 9e. In the present embodiment, Au is used as an example. However, the material is not limited as long as it causes the surface plasmon resonance phenomenon. For example, Ag, Pt, etc. can be used. Vapor deposition or the like is used to form the metal thin film 9e.

Further, a dielectric film 9f is fixed on the surface of the metal thin film 9e formed on the outer peripheral surface of the core 9a.
An antibody (or antigen) 9g is immobilized on the surface of the dielectric film 9f. The antibody (or antigen) 9g formed on the surface of the dielectric film 9f is appropriately selected according to the antigen (or antibody) to be measured.

As described above, the sensor optical fiber 9 is inserted into the optical fiber fixing hole 7c formed in the second lid member 7b, and is fixed to the lid member 7 with an adhesive. As a means for fixing the sensor optical fiber 9, in addition to the adhesive, the sensor optical fiber 9 may be directly fused to the cover member 7, or the sensor optical fiber 9 may be simply inserted. When the sensor optical fiber 9 is simply inserted, the lid member 7 and the sample cell 5 can be used again. However, in this case, in consideration of the leakage of the specimen, it is desirable to take measures such as waterproofing the joint between the second lid member 7b and the optical fiber 9 for the sensor, or attaching a so-called O-ring. .

Here, in the sensor optical fiber according to the present embodiment, no special processing is applied to both ends. However, a metal thin film for reflection may be formed at the tip (upper end in FIG. 2) of the sensor optical fiber 9. this is,
It functions as a mirror for reflecting the light that has traveled inside the core 9a. For example, Ag, Al, or the like is used as a material of the metal thin film serving as a mirror. However, the material of the metal thin film serving as a mirror is not particularly limited as long as it can reflect light. As described above, by forming the metal thin film on the end of the sensor optical fiber 9, the light incident on the sensor optical fiber 9 is returned. Thus, by providing the spectroscope also on the light source side, the wavelength distribution of reflected light can be measured. Therefore, it is not necessary to form the first lid member with a transparent member or to provide a light transmitting hole.

[Immune Reaction Measuring Apparatus] Next, an immune reaction measuring apparatus 1 using the above-described SPR sensor cell 3 will be described with reference to FIG. The main components of the immune response measurement device 1 according to the present embodiment include a light source 11 that emits light for measuring an immune response, the above-described SPR sensor cell 3, and a device that receives light transmitted through the SPR sensor cell 3. A spectroscope 13 for analyzing the wavelength distribution.

[Light Source] The light source 11 emits light of a wide band wavelength, and specifically, a halogen lamp, a xenon lamp, or the like is used. The immunoreaction measuring device 1 of the present invention analyzes the change in the wavelength distribution of light before and after the immune reaction among the light transmitted through the SPR sensor cell 3, and thereby measures the immune reaction. Therefore, it is desirable that the light source 11 emits light having a stable wavelength distribution. The light source 11 may use a light source other than the above-described halogen lamp or xenon lamp as long as it can emit light having a high-band wavelength distribution.

Downstream of the light source 11, the condenser lens 1
5a, a receptacle 17, an optical connector 19 and a light source optical fiber 21 are provided. The light source optical fiber 21 further includes an optical connector 22 and a receptacle 23.
Is connected. Therefore, the light emitted from the light source 11 is condensed by the condenser lens 15, enters the receptacle 17, and is emitted through the optical connector 19, the optical fiber for light source 21 and the receptacle 23.
A condenser lens 15b is provided on the downstream side of the receptacle 23 (above the upper part of FIG. 4A).
It faces the PR sensor cell 3.

Downstream of the SPR sensor cell 3, that is, the spectroscope 1
On the third side, a condenser lens 25b, a receptacle 27,
An optical connector 29 and a spectrometer optical fiber 31 are provided. Further, an optical connector 32 and a receptacle 33 are connected further downstream of the optical fiber 31 for a spectroscope,
A condenser lens 25a is provided to face the receptacle 33. That is, the light transmitted through the SPR sensor cell 3 passes through the optical connector 32 through the spectroscope optical fiber 31. Then, the light is emitted from the receptacle 33 and enters the condenser lens 25a. In the condenser lens 25a,
The light is appropriately condensed and guided to the spectroscope 13.

[Spectroscope] The spectroscope 13 analyzes the wavelength distribution of light transmitted through the SPR sensor cell 3. SP
When the surface plasmon resonance phenomenon occurs in the R sensor cell 3, the intensity of light of a specific wavelength is attenuated. This decaying wavelength varies with the immune response. Therefore, by measuring the change in the wavelength distribution of the reflected light by the spectroscope 13, an immune reaction measurement can be performed.

FIG. 4B shows another example of the immune reaction measuring device. The same parts as those in the above embodiment will be described using the same reference numerals. In this example, the light emitted from the light source 11 is directly incident on the condenser lens 15b. The condensing lens 15b has a role of condensing light and making it incident on the SPR sensor cell 3. On the other hand, regarding the spectroscope 13 side,
A condensing lens 15b is provided downstream of the SPR sensor cell 3, and the condensed light is introduced into the spectroscope.

[Operation] Next, the operation of the immune reaction measuring apparatus 1 according to the present invention will be described in more detail with reference to FIG. First, light emitted from the light source 11 is condensed by the condensing lens 15 a and introduced into the receptacle 17. The light incident on the receptacle 17 is incident on the light source optical fiber 21 via the optical connector 19. Further, the light incident on the light source optical fiber 21 passes through the optical connector 22 and the receptacle 23, and is condensed by the condenser lens 15b.
Is incident on.

The light incident on the condenser lens 15b is condensed and incident on the sensor optical fiber 9 in the SPR sensor cell 3. When light is introduced into the sensor optical fiber, a surface plasmon resonance phenomenon occurs in the SPR sensor section. Thereby, the light intensity of the light of the predetermined wavelength corresponding to the immune reaction is attenuated.

The light incident on the sensor optical fiber 9 is:
The light exits from the other end of the optical fiber for the sensor again, passes through the condenser lens 25b, the receptacle 27, the optical connector 29, and the optical fiber 31 for the spectroscope, and enters the optical connector 32. Further, the light incident on the condenser lens 25a from the optical connector 32 through the receptacle 33 is guided to the spectroscope 13 as it is.

The spectroscope 13 analyzes the wavelength distribution of the incident light. Here, the immune response can be measured by comparing the wavelength distribution when no immune response has occurred and the wavelength distribution after the immune response has occurred. To measure the wavelength distribution when no immune response has occurred, use the SPR
Light is incident on the sensor cell 3 without a sample, and the wavelength distribution at this time is measured. Thus, the wavelength distribution when a specific antigen (or antibody) is fixed on the surface of the dielectric film can be determined.

[Other Embodiments] FIG. 5A shows another example of the immunological reaction measuring apparatus of the present invention. Here, the same components as those in the above-described embodiment will be described with the same reference numerals. This immunoreaction measurement device 1c is different from the above-described immunoreaction measurement device 1 in that it further includes a condenser lens 14a and a plurality of optical fibers 14b between the light source 11 and the condenser lens 15a. . Other basic components are common. Thus, the plurality of optical fibers 14a
Is provided, light having a high light intensity can be supplied to the SPR sensor cell 3.

FIG. 5B shows another example of the immune reaction measuring device. The immunological reaction measuring apparatus 1d is different from the immunological reaction measuring apparatus described above in that a fused optical fiber array 14c, an optical connector 14d, and an adapter 14e are provided between the condenser lens 14a and the optical connector 19. The device is different from the device 1 and other basic components are common.
In the fusion type optical fiber array 14c, three optical fibers are bundled into one, and the confluence is joined to each other by heating and melting. Then, three optical fibers are connected to the light source 1
An optical connector 14d is fixed to the other one of the optical fibers so as to correspond to the condensing lens 14a on one side. In this way, by providing three optical fibers on the light source 11 side, light having a higher intensity than the case of one optical fiber is output to the SPR sensor cell 3.
Can be supplied to

FIG. 6 shows a plurality of SPR sensor cells 3r and 3r.
The immune response measuring device 1e in the case of sequentially performing an immune response measurement for a, 3b,... Immune reaction measurement device 1e
Are the same as those described above, but a plurality of SPR sensor cells 3r, 3
a. 3b are different. Then, at the time of actual immune reaction measurement, the sensor cell fixing base 41 is movable.

FIG. 6 shows an S for reference.
This shows a state where the PR sensor cell 3r is positioned at a position facing the condenser lens 15b. In this figure, the sensor cell fixing base 41 is shown as a cross section. As described above, the reference SPR sensor cell 3r is for measuring the wavelength distribution when no immune reaction occurs. Therefore, S for reference
The PR sensor cell 3r does not contain a sample or an antibody (or antigen) fixed to a sensor optical fiber.
A sample that does not contain an antigen (or antibody) that specifically reacts with Next, an immune reaction measurement of the first SPR sensor cell 3a is performed. Sensor cell fixing base 41
Are movable in the horizontal direction. Therefore, the first
The second SPR sensor cell 3a is positioned at a position facing the condenser lens 15b. And the first SP
Light is introduced into the R sensor cell 3a to measure an immune reaction.

After the immunoreactivity measurement has been performed on the first SPR sensor cell 3a, the sensor cell fixing base 41 is further moved to position the second SPR sensor cell 3b at a position facing the condenser lens 15b. . Then, an immune reaction measurement is performed. In FIG. 6, as an example, six S
The PR sensor cells 3a, 3b...
1. Therefore, after the completion of the measurement of the six types of immune reactions, the measurement of the immune reactions is performed using another SPR sensor cell. Note that the number of SPR sensor cells is an example, and is not particularly limited to six.

FIG. 7 is a perspective view showing the sensor cell fixing base 43. FIG. 7 shows a sensor cell fixing base 43 on which one SPR sensor cell 3 can be placed. Sensor cell fixing base 4
No. 3 has a plate-like upper surface, and an SPR
A sensor cell fixing hole 43a into which the sensor cell is inserted is formed. FIG. 8 shows eight SPR sensor cells 3a simultaneously.
3 shows a sensor cell fixing base 45 on which the sensor cell mounting table 45 can be placed. As described above, by mounting the plurality of SPR sensor cells 3a to 3h, other types of immune reaction measurement can be performed quickly.

FIGS. 9 and 10 also show a sensor cell fixing base on which a plurality of SPR sensor cells can be mounted. 9 (A), 9
(B) shows the arrangement of the SPR sensor cells in two rows, and FIGS. 10 (B) and 10 (B) show the arrangement on the circumference. When the sensor cell fixing table 47 shown in FIG. 9B is moved, it is necessary to perform the parallel movement twice. On the other hand, in the sensor cell fixing table 49 shown in FIGS. 10A and 10B, the immune reaction measurement can be performed for each SPR sensor cell by rotating the sensor cell fixing table 49 itself. Note that a solenoid, a stepping motor, a micromotor, or the like is used for moving (rotating) the sensor cell fixing table 49.

[0052]

As described above, in the SPR sensor cell of the present invention, a hollow cylindrical sample cell for storing a predetermined sample, a first lid member and a second cover member for sealing the opening of the sample cell are provided. And an optical fiber for a sensor attached to one of the lid members. An end surface of one end of the optical fiber for the sensor is exposed to the outside from the lid member, and the other end region of the optical fiber for the sensor is provided. The SPR sensor part was formed in the sample, and the SPR sensor part was immersed in the sample. By configuring the SPR sensor cell in this manner, the SPR sensor cell can be configured at low cost and small size. Also,
Since the SPR sensor cell itself is independent of other components of the immune response measuring device, replacement of the SPR sensor cell can be easily performed.

In addition, since the replacement of the SPR sensor cell is simple, there is an excellent effect that an immunoreaction measurement for a plurality of types of specimens can be performed quickly. Furthermore, since only the SPR sensor cell can be discarded, there is an excellent effect that the usability and hygiene reliability can be improved.

[Brief description of the drawings]

FIG. 1 is a cross-sectional view showing an SPR sensor cell according to an embodiment of the present invention. FIG. 1A shows a case where a through hole is not formed in a first lid member, and FIG. The case where a through hole is formed in the first lid member is shown.

2A and 2B show an optical fiber for a sensor used in the SPR sensor cell disclosed in FIG. 1, FIG. 2A is an overall perspective view, and FIGS. 2B and 2C are FIGS. 3) shows a cross-sectional view of each part.

3 shows an exploded view of the SPR sensor cell disclosed in FIG. 1, and FIGS. 3 (A) to 3 (D) show perspective views and FIG.
(E) to FIG. 3 (H) show sectional views.

FIG. 4 is a schematic explanatory view showing an immunoreaction measurement device using the SPR sensor cell disclosed in FIG. 1; FIG. 4A shows a case where an optical fiber is used for relaying light;
Indicates a case where no optical fiber is used.

FIG. 5 is a schematic explanatory view showing another example of the immunoreaction measurement device using the SPR sensor cell disclosed in FIG. 1;
5A shows a case where light from a light source is transmitted by a plurality of optical fibers, and FIG. 5B shows a case where light from a light source is transmitted by a fusion optical fiber.

FIG. 6 is a diagram showing an overall view of an immunoreaction measurement device of the present invention, particularly showing a case where a plurality of SPR sensor cells are mounted on a sensor cell fixing base.

7 is a perspective view showing a sensor cell fixing base used in the immunoreaction measurement device of the present invention. FIG. 7 (A) shows a state where an SPR sensor cell is not placed, and FIG. 7 (B) shows an SPR sensor cell. This shows a state where the sensor cell is mounted.

FIG. 8 is a perspective view showing another example of a sensor cell fixing table used in the immunoreaction measurement device of the present invention. FIG. 8A shows a sensor cell fixing table on which a plurality of SPR sensor cells can be placed in a line. FIG. 8B shows a state where a plurality of SPR sensor cells are mounted.

FIG. 9 is a perspective view showing another example of a sensor cell fixing base used in the immune reaction measuring device of the present invention. FIG. 9A shows a sensor cell fixing base capable of mounting a plurality of SPR sensor cells in two rows. FIG. 9B shows a state where a plurality of SPR sensor cells are mounted.

FIG. 10 is a perspective view showing another example of a sensor cell fixing base used in the immunoreaction measurement device of the present invention.
FIG. 10A shows a sensor cell fixing base on which a plurality of SPR sensor cells can be placed on a circumference, and FIG.
This shows a state where the sensor cell is mounted.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Immune reaction measuring device 3 SPR sensor cell 5 Sample cell 7a 1st lid member 7b 2nd lid member 7ab Through-hole 9 Sensor optical fiber 9d SPR sensor part 9e Metal thin film 41 Sensor cell fixing stand

Claims (5)

[Claims] 1. A hollow cylindrical sample cell for storing a predetermined sample, a first lid member and a second lid member for sealing an opening of the sample cell, and one of these lid members A sensor optical fiber to be exposed, and an end face of one end of the sensor optical fiber is exposed to the outside, and an SPR is provided at the other end region of the sensor optical fiber.
An SPR sensor cell, wherein a sensor unit is formed and the SPR sensor unit is immersed in the sample. 2. The SP according to claim 1, wherein a through hole for injecting the sample is formed in the lid member.
R sensor cell. 3. The SPR sensor cell according to claim 1, wherein the SPR sensor unit is made of a metal thin film of Au, Ag, or Pt coated on a core of the sensor optical fiber. 4. A hollow cylindrical sample cell for storing a predetermined sample, a first lid member and a second lid member for sealing an opening of the sample cell, and one of these lid members An SPR sensor cell including a sensor optical fiber mounted on the SPR sensor cell; a light source that emits light in a predetermined wavelength band to the SPR sensor cell; A spectroscope for analysis, wherein one end of the optical fiber for sensor is exposed to the outside and the other end of the optical fiber for sensor is provided with an SPR.
An immunoreaction measurement device, wherein a sensor unit is formed and the SPR sensor unit is immersed in the sample. 5. An immunity comprising a plurality of said SPR sensor cells, each of said SPR sensor cells being mounted on a predetermined sensor cell fixing base, and allowing said sensor cell fixing base to be freely movable in the arrangement direction of the SPR sensor cells. Reaction measurement device.