JPH0829330A - Optical biosensor and production thereof - Google Patents

Abstract

PURPOSE:To provide a inexpensive optical biosensor easy to operate. CONSTITUTION:An optical waveguide 11 is formed on a slide glass substrate 12 and a frame 19 having two tanks 19a, 19b is arranged on the optical waveguide 11 and an org. electric field light emitting element 30 emitting exciting light is arranged in the part where the optical waveguide 11 is not positioned on the substrate 12. The org. electric field light emitting element 30 is formed into such a structure that a dielectric multilayered film mirror 13, a transparent electrode 14, a hole transport layer 15, a light emitting layer, an electron transport layer and a metal electrode 17 are successively laminated. An aromatic phenyldiamine layer is used as the hole transport layer 15 and an aluminum quinolinol complex layer is used as the light emitting layer and the electron transport layer.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an optical biosensor, and more particularly to an optical biosensor for quantifying a specific antigen from a sample solution containing various antigens easily and in a short time.

[0002]

2. Description of the Related Art Conventionally, the basic idea of an optical biosensor using an evanescent wave was announced by RM Sutherland et al. In 1984 (Biosensors, Oxford Sci.
ence Publications, Oxford, pp.655-678). According to this report, an antibody labeled with a fluorescent dye is immobilized on the surface of a planar waveguide or an optical fiber waveguide by covalent bonding, and the evanescent light beam undergoes multiple total internal reflections in the waveguide. The wave component is used to detect with high sensitivity the reaction between the antigen immobilized on the waveguide and the antibody in the sample solution. What is an evanescent wave?
This is a transmitted wave that exponentially decreases during total internal reflection at the boundary surface of light (Laser Handbook, "Laser Handbook" Ohmsha (1982) p.63). Since the evanescent wave has a characteristic penetration depth of a fraction of a wavelength in the water phase outside the waveguide, it photo-reacts with substances in close proximity to the interface, but only minimally with the solution body. do not do. The distance of this evanescent wave is about 1 μm from the glass surface, and when this light is used as excitation light, only the fluorescent dye bound to the glass surface can be detected. The planar type using an optical waveguide is more suitable than the fiber type in that the reagent is immobilized. In addition, the planar type can form a plurality of sensing portions such as a reference zone and a test zone in addition to the measurement zone.

Generally, in an optical biosensor, a monoclonal antibody labeled with a fluorescent dye called FITC is used. This is because the FITC dye has a long history of use in the field of biochemistry. Rhodamine fluorescent dyes are also known, but the fact is that they are not widely used. The wavelength of the light source for exciting the FITC dye is light in the range of 450 nm to 520 nm, and the fluorescence wavelength is in the range of 560 nm to 580 nm. Therefore, the conventional biosensor uses an argon laser as an excitation light source.

FIG. 9 shows a schematic diagram of an optical biosensor announced by Y. Zhou et al. Of University of Glasgow (Biosensors & Bio
electronics, 6 (1991) 595-607). As shown in FIG. 9, an optical waveguide 3 is formed on a substrate 9, and on the optical waveguide 3, an optically coupled optical coupling prism 2 and a frame 5 forming two tanks 5a and 5b are formed. Is provided. The light receiving elements 4a and 4b are arranged on the back surface side of the substrate 9 facing the tanks 5a and 5b of the frame 5, respectively. A light receiving element 4c is arranged on the end face side of the optical waveguide 3 where the optical coupling prism 2 is not located. 27 is bovine serum protein.

Next, the operation of this conventional example will be described.

The laser beam 1 is guided into the planar optical waveguide 3 by the optical coupling prism 2, the light beam is propagated by the multiple total internal reflection, and the excitation light and the fluorescence are detected by the light receiving elements 4a, 4b and 4c, respectively. . On the outer surface of the optical waveguide 3, a predetermined antibody 6 is fixed inside the tank 5a provided in the frame 5. Then, the blood containing the antigen 8 as the sample solution 10 and the solution containing the FITC-labeled antigen 7 are mixed and dropped on the antibody 6. This blood contains many antigens 8. The solution is allowed to react with the antibody 6 for several minutes. If the blood contains a large amount of the antigen to be detected that reacts with the antibody 6, the amount of the FITC-labeled antigen 7 that binds to the antibody 6 on the optical waveguide 3 becomes relatively small and binds to the antibody 6. The amount of antigen to be detected in blood is relatively high. That is, the concentration of the FITC dye is reduced on the surface of the optical waveguide 3. As a result, the fluorescence intensity of the FITC dye excited by the evanescent wave 23 decreases. If the blood contains no or less antigen to be detected, a large number of FITC-labeled antigens 7 will bind to the antibody 6 immobilized on the optical waveguide 3, and thus the amount of FITC-labeled excited. Will increase and the fluorescence intensity will increase. In the conventional device, the laser light source is chopped by the chopper device to give a specific modulation to the signal to be measured to distinguish it from noise. The noise is removed in synchronization with the modulation applied to the signal, and the lock is taken out of the signal. The in-amp measurement method is used.

Similarly, a group at the University of Glasgow provided a multi-type optical biosensor capable of simultaneously detecting many kinds of specimens by providing reaction vessels on the same substrate on which antigens respectively reacting with five kinds of antibodies were fixed. Reporting
(Y.Zhou, et al., Journal of Molecular Electronic, Vo
l 7,135-149 (1991)).

[0008]

The research on the optical biosensor using the evanescent wave has been actively conducted. However, in the above-mentioned conventional optical biosensor, since the argon gas laser is used as the excitation light source, the size of the light source is increased. However, it was difficult to reduce the element size of the optical biosensor. Moreover, since it is an element structure that optically couples the laser light source and the optical waveguide using a prism, it is difficult to adjust the coupling of the laser light source and the optical waveguide using the prism,
Cannot be used in ordinary households.

An inexpensive red semiconductor laser or blue semiconductor laser is also known as a laser light source. The red semiconductor laser cannot be used because the oscillation wavelength is too long to excite the fluorescent dye. Fluorescent dyes sensitive to red semiconductor lasers are being developed, but their characteristics are not sufficient. At present, the blue semiconductor laser cannot be used for the light source of the present invention because it is under research and development.

The present invention has been made in order to solve the above-mentioned problems, and pays attention to an organic electroluminescent device in which a blue end face type light emitting device can be easily manufactured, and an operation which can be used in general households is performed. It is an object of the present invention to provide an easy and inexpensive optical biosensor.

[0011]

In the present invention, the above object is to provide an optical waveguide having an antigen which reacts with a predetermined substance or an antibody which reacts with a predetermined substance immobilized on a surface thereof, and an organic electric field which emits excitation light. This is achieved by an optical biosensor characterized in that the light emitting element and the light emitting element are formed on the same substrate.

The above-mentioned object is that the organic electroluminescent device is
It is an edge emitting organic electroluminescent device, and is achieved by an optical biosensor in which an end face of the edge emitting organic electroluminescent device and an end face of an optical waveguide are combined and formed on a substrate.

The organic electroluminescence device has an edge emission type structure in which a dielectric multilayer mirror, a transparent electrode, a hole transport layer, a light emitting layer, an electron transport layer, and a metal electrode are laminated in this order on a substrate on which an optical waveguide is formed. It may be an organic electroluminescent device.

Further, the organic electroluminescence device has a structure in which a metal electrode, a hole transport layer, a light emitting layer, an electron transport layer, and a metal electrode are laminated in this order on a substrate on which an optical waveguide is formed. It may be an electric field element.

Further, according to the present invention, the above-mentioned object is to provide an optical waveguide having an antigen which reacts with a predetermined substance or an antibody which reacts with a predetermined substance immobilized on the surface thereof, and an organic electroluminescence device which emits excitation light. Is formed on the same substrate, and the end face of the optical waveguide and the end face of the organic electroluminescent device are optically coupled to each other.

Further, the organic electroluminescence device may be formed so as to be covered with an optical waveguide.

In the optical biosensor of the present invention, an optical waveguide is formed on a substrate, and then the optical waveguide at a portion where an organic electroluminescent device is formed is deleted from the substrate, and the dielectric multilayer film is formed on the portion where the optical waveguide is deleted. It can be manufactured by laminating a mirror, a transparent electrode, a hole transport layer, a light emitting layer, an electron transport layer and a metal electrode in this order to form an organic electroluminescent device.

Further, in the optical biosensor of the present invention, an optical waveguide is formed on a substrate, and then the optical waveguide of a portion where an organic electroluminescent element is formed is deleted from the substrate, and a metal electrode is formed on the portion where the optical waveguide is deleted. A hole transport layer, a light emitting layer, an electron transport layer, and a metal electrode are laminated in this order to form an organic electroluminescent device.

[0019]

In the optical biosensor of the present invention, the light beam generated by the organic electroluminescent element is guided into the optical waveguide,
The light beam is propagated by multiplex total internal reflection, and the excitation light and the fluorescence are respectively detected by the light receiving element. On the antibody immobilized on the surface of the optical waveguide, blood containing a sample solution containing an antigen and a solution containing a FITC-labeled antigen are mixed and dropped. Blood contains many antigens, and if the blood contains many antigens to be detected that react with antibodies, the amount of FITC-labeled antigen bound to the antibodies on the optical waveguide is relatively small. Therefore, the amount of the antigen to be detected that binds to the antibody on the optical waveguide becomes relatively large. That is, the concentration of the FITC dye is reduced on the surface of the optical waveguide. as a result,
The fluorescence intensity of the FITC dye excited by the evanescent wave decreases. If blood does not contain or contains less antigen to be detected, a large number of FITC-labeled antigens will be bound to the antibody immobilized on the optical waveguide, and the amount of FITC-labeled excited will be large. And the fluorescence intensity increases.

[0020]

EXAMPLES Examples of the optical biosensor of the present invention will be described below with reference to the drawings.

Normally, the organic electroluminescent device outputs light through the ITO transparent electrode. An organic electroluminescent device having an optical resonator structure is used as a light source of the optical biosensor of the present invention. The organic electroluminescent device has two types of structures. One is an aromatic diamine (PDA) layer which is a hole transporting layer, in which an ITO transparent electrode is formed on a dielectric multilayer mirror.
This is a structure in which an aluminum quinolinol complex (8-hydorxyquinolinealuminum, Alq ₃ ) layer capable of obtaining high-luminance light emission and an In electrode are laminated in this order. The other is a structure in which an organic light emitting layer is sandwiched between two metal electrodes that also serve as a charge injection and a mirror. Due to the confinement effect of the optical resonator structure composed of the dielectric multilayer film and the metal electrode, light emission with a narrow half width can be obtained. By controlling the cavity length, it is possible to take out light emission of any wavelength. Therefore, by precisely measuring the thickness of the organic electroluminescent layer,
Monochromatic light of 515 nm, which is the optimum excitation wavelength of the FITC fluorescent dye, can be easily obtained. An end face output type organic light emitting device having a resonator structure is formed by coupling with a waveguide, and monochromatic light is guided to the optical waveguide. The FI bound by reacting with the antibody immobilized on the waveguide by the evanescent wave exuding from the optical waveguide
A TC-labeled light source is excited to detect fluorescence. Specifically, fluorescence is collected by a lens system, detected by a high-sensitivity photodiode or a light receiving element such as a photoelectron multiplier, and an optical signal is converted into an electric signal for determination. In the present invention, the drive voltage of the organic electroluminescent element is applied in pulses to measure with high sensitivity by the lock-in amplifier method.

Example 1 FIG. 1 shows an optical biosensor of this example.

The optical waveguide 11 is formed on the slide glass substrate 12.
Are formed, and two tanks 19 are formed on the optical waveguide 11.
A frame 19 forming a and 19b is arranged. The light receiving elements 24a and 24b are arranged on the back surface side of the substrate 12 of the frame 19 which faces the tanks 19a and 10b. Further, a light receiving element 24c is arranged on one end surface side of the optical waveguide 11. An organic electroluminescent device 3 that emits excitation light in a portion of the substrate 12 where the optical waveguide 11 is not located
0 is set. The organic electroluminescent device 30 includes a dielectric multilayer film mirror 13, a transparent electrode 14, and an aromatic phenyldiamine (PDA) layer 1 represented by the structural formula of FIG.
5, an aluminum quinolinol complex (Alq ₃ ) layer 16 represented by the structural formula of FIG. 2A, and an electrode 17 of an indium or magnesium silver alloy are laminated.

Next, the manufacturing process of the optical sensor of this embodiment will be described.

Slide glass substrate 1 made of soda glass
2 to 6 at 370 ° C. molten solution of potassium nitrate (KNO ₃ ).
Soak for 0 minutes, then wash with warm water. At this time, the potassium ion concentration is 0.05 mol%. As a result, on the slide glass substrate 12, potassium is diffused, potassium is taken in, the refractive index is increased, and the optical waveguide 11 having a film thickness of 1 μm that traps light is formed. Then, the optical waveguide in the portion where the organic electroluminescent element 30 is formed on the substrate 12 is etched and removed by the photolithography method. Twenty-five layers of TiO ₂ and SiO ₂ are alternately laminated on the portion where the optical waveguide is removed to form a dielectric multilayer mirror layer 13. The reflectance of the dielectric multilayer mirror layer 13 near 500 nm was set to 100%. Dielectric multilayer mirror layer 13
A transparent electrode 14 such as ITO having a thickness of 0.4 μm was formed on the upper surface by sputter deposition. And the degree of vacuum is 10 ^-8 torr
Aromatic phenyldiamine (PDA) layer 15, which is a hole transport material, and an aluminum quinolinol complex (Al that functions as a light emitting layer and an electron transport layer) are formed by an organic molecular beam deposition method.
q ₃ ) layer 16 is formed. Both the triphenyldiamine layer and aluminum quinolinol complex layer have a thickness of 70 nm
And Further, the upper electrode 17 was formed by co-evaporation of magnesium and silver 1:10, which also served as a mirror, to form an organic electroluminescent device 30. In addition, it was designed and formed so as to confine light having a wavelength of 500 nm. On the outer surface of the optical waveguide 11, polymethylmethacrylate (PMM
The polymer thin film of A) is formed by spin coating so as to have a film thickness of 1 μm, and is used as the bottoms of the tanks 19a and 19b. The refractive index of this PMMA is smaller than that of the optical waveguide.
On top of this, the frame 19 of the two tanks 19a and 19b is placed on the PMM.
It was formed by screen printing of A.

Next, the operation of this embodiment will be described.

The end face of the light emitting layer 16 of the organic electroluminescent device 30 and the end face of the optical waveguide 11 are connected to each other, and when electric power is applied to the organic electroluminescent device 30, the organic electroluminescent device 30.
Excitation light is emitted from the light emitting layer 16. This excitation light is guided into the optical waveguide 11 and propagates in the optical waveguide 11 by multiple internal total reflection. The antibody 18 is placed in the tank 19a whose bottom is the PMMA thin film, which is within the characteristic penetration depth outside the optical waveguide 11.
Is fixed, and the sample solution 20 is placed on the antibody 18.
The blood containing the antigen 21 and the solution containing the FITC-labeled antigen 22 are mixed and added dropwise. The antibody 18 reacts with the antigen 21 or the FITC-labeled antigen 22 contained in the sample solution 20. The FITC-labeled component is excited by the evanescent wave 23 that is the excitation light to emit fluorescence. This light emission is collected by a lens and is detected by the light receiving element 24a through a filter that cuts the excitation light. For example, it can be obtained by subtracting the excitation light detected by the light receiving element 24c from the fluorescence intensity detected by the light receiving element 24a. The fluorescence from the tank 19b in which the bovine serum protein 27 as the reference is arranged is guided to the light receiving element 24b by the optical waveguide 11 and compared with the fluorescence of the light receiving element 24a.
Bovine serum protein antigen includes antigen 2 contained in sample solution 20.
1 or FITC-labeled antigen 22 does not bind, and is suitable for comparison.

Although the antibody is fixed in the tank here, the antigen may be fixed. As the antigen in this case, an allergen, a residual pesticide or a virus can be used.

Needless to say, in the case of detecting a plurality of specimens, it is possible to provide a plurality of reaction layers and immobilize the antigen.

Embodiment 2 This embodiment will be described with reference to FIG. It should be noted that the same components as those in FIG.

FIG. 3 shows an element structure in which an organic light emitting layer is sandwiched by using two metal electrodes which serve as charge injection and a mirror as a light emitting element. In this case, the electrode 25 made of aluminum or gold-silver alloy and the electrode 26 made of silver or silver-magnesium alloy serve as mirrors.

Next, a manufacturing process of the optical waveguide and the organic electroluminescent device will be described with reference to FIGS.

Slide glass substrate 1 made of soda glass
2 to 6 at 370 ° C. molten solution of potassium nitrate (KNO ₃ ).
After soaking for 0 minutes, wash with warm water. At this time, the potassium ion concentration is 0.05 mol%. As a result, FIG.
As shown in a, a film thickness of 1 μm is formed on the slide glass substrate 12.
The optical waveguide 11 of m is formed. Then, the optical waveguide 1
1. A resist is applied on the surface by spin coating. Except where the light source is provided, ultraviolet rays are exposed and the unexposed areas are peeled off. As shown in FIG. 4b, the portion where the light source is located is etched with acid to scrape the optical waveguide portion. As shown in FIG. 4c, gold and silver are simultaneously vapor-deposited to form the lower electrode 25,
Next, as shown in FIG. 4d, aromatic phenyldiamine (PDA), which is a hole transport material, is formed by an organic molecular beam deposition method.
A layer 15 and an aluminum quinolinol complex (Alq ₃ ) layer 16 which also serves as a light emitting layer and an electron transporting layer are formed. P
Both the DA layer 15 and the Alq ₃ layer 16 had a thickness of 175 nm. As shown in FIG. 4e, the upper electrode 26 was formed on the Alq ₃ layer 16 by a co-evaporation method of silver and magnesium so as to overlap the end portion of the optical waveguide. By overlapping the upper electrode 26 on the end of the optical waveguide, the escape of light to the outside is reduced and the optical coupling efficiency is improved. FIG. 5 shows a plan view seen from above.

On the outer surface of the optical waveguide 11, polymethylmethacrylate (PMM) was used as described in Example 1.
The polymer thin film of A) was formed by a spin coating method so as to have a film thickness of 1 μm, and then the frame 19 in which two tanks were disposed was formed by screen printing with this thin film as a bottom. Antibody 18 and bovine serum protein 2 in each of the two tanks
7 is fixed.

An output light intensity of 300 mWcm ^-2 is obtained, and the direction of the output light is concentrated within 10 degrees above and below the substrate surface. In addition, as a hole transport layer between the metal electrodes, as shown in FIG.
Triphenylamine (TP having a structural formula as shown in (d)
AC), a light emitting layer (PQ) having a structural formula as shown in FIG.
When P) was sandwiched, the emission wavelength was 460 nm, and the output intensity was 300 mWcm ⁻² . (It should be noted that similar output light characteristics can be obtained in Example 1 as well.) FIG. 5 is a diagram of the waveguide viewed from above. Since the second embodiment has a simple optical resonator structure in which the light emitting layer and the hole transport layer are sandwiched by the metal electrodes 25 and 26 also serving as mirrors, the expensive dielectric multilayer mirror 13 as in the first embodiment is not required. Therefore, the cost can be reduced.

Embodiment 3 This embodiment will be described with reference to FIG. The same components as those in FIGS. 1 and 3 are designated by the same reference numerals and the description thereof will be omitted.

Gold and silver are simultaneously vapor-deposited on a part of the glass substrate 12 which is soda glass to form the lower electrode 25.
Then, an aromatic phenyldiamine (PDA) layer 15, which is a hole transport material, and an aluminum quinolinol complex (Alq ₃ ) layer 16, which also functions as a light emitting layer and an electron transport layer, are formed by an organic molecular beam deposition method. PDA layer 15 and Al
The thickness of each of the q ₃ layers 16 was 175 nm. The upper electrode 26 was formed on this by the co-evaporation method of silver and magnesium, and the organic electroluminescent element 30 was formed. Next, a polymer thin film 28 of polymethylmethacrylate (PMMA) is formed on the slide glass substrate 12 so as to cover the end face of the organic electroluminescent element 30 by a spin coating method so as to have a film thickness of 2 μm, and an optical waveguide is formed. 11 was formed. Optical waveguide 11
The outer surface of the has a smaller refractive index than PMMA, for example,
Form a thin film of polycarbonate by spin coating,
The bottom of the tank. A frame 19 was formed on this by screen printing. The antibody 18 and the bovine serum protein 27 are immobilized in the two tanks, respectively.

In this device structure, it is difficult to form a proper end face although it is an end face bond, so the optical coupling efficiency is poor, but the device manufacturing process is simplified and the cost can be reduced. Although an organic polymer optical waveguide is used here for cost reduction, a quartz waveguide may be formed by a sputtering method instead of the organic polymer.

Using the optical biosensor shown in FIG. 3, the fluorescent dye-labeled antigen was reacted with the antibody immobilized on the substrate to compare the fluorescence intensities. FIG. 7 shows the result.

The concentration of the fluorescently labeled antigen was changed from 1 μg / ml to 1
The fluorescence intensity was measured while changing it to 0 μg / ml. As a result, the fluorescence intensity increased with the increase of the light source concentration. In addition, the fluorescence intensity at each light source concentration was measured when the unlabeled antigen was added while the concentration of the fluorescently labeled antigen was kept constant at 5 μg / ml. FIG. 8 shows the result. Thus, it was confirmed that the fluorescence intensity was changed by the unlabeled antigen.

[0041]

According to the optical biosensor of the present invention, an optical waveguide having an antigen that reacts with a predetermined substance or an antibody that reacts with a predetermined substance immobilized on its surface, and an organic electroluminescence device that emits excitation light. Since it is formed on the same substrate, it is possible to realize a compact optical biosensor that integrates a light source and an optical waveguide, and because optical adjustment is not required, handling at the time of use is simple and it can be used in general households. Can be used.

Further, the organic electroluminescent device has an end face light emission structure in which a dielectric multilayer mirror, a transparent electrode, a hole transport layer, a light emitting layer, an electron transport layer, and a metal electrode are laminated in this order on a substrate on which an optical waveguide is formed. Since it is a type organic electroluminescent device, the light source can be manufactured at low cost and the cost can be reduced.

Further, the organic electroluminescence device has a structure in which a metal electrode, a hole transport layer, a light emitting layer, an electron transport layer and a metal electrode are laminated in this order on a substrate on which an optical waveguide is formed. Since it is an element, an expensive dielectric multi-layer film mirror is not required, and the cost can be further reduced.

An optical waveguide having an antigen that reacts with a predetermined substance or an antibody that reacts with a predetermined substance immobilized on the surface thereof and an organic electroluminescent device that emits excitation light are formed on the same substrate. Since the end faces of the organic electroluminescent device and the end faces of the organic electroluminescent device are optically coupled, light can be efficiently guided from the end face of the light emitting device to the end face of the optical waveguide on the same substrate. Even a non-coherent light source can be used satisfactorily.

Further, by forming the organic electroluminescent device so that the optical waveguide covers it, the device manufacturing process can be simplified and the cost can be reduced.

[Brief description of drawings]

FIG. 1 is a schematic structural diagram of an optical biosensor according to a first embodiment of the present invention.

FIG. 2 is a diagram showing a structural formula of a material used for each layer of an organic electroluminescence device.

FIG. 3 is a schematic structural diagram of an optical biosensor according to a second embodiment of the present invention.

FIG. 4a is a view showing a manufacturing process of the optical biosensor according to the second embodiment of the present invention.

FIG. 4b is a diagram showing a manufacturing process of the optical biosensor according to the second embodiment of the present invention.

FIG. 4c is a diagram showing a manufacturing process of the optical biosensor according to the second embodiment of the present invention.

FIG. 4d is a view showing a manufacturing process of the optical biosensor according to the second embodiment of the present invention.

FIG. 4e is a diagram showing a manufacturing process of the optical biosensor according to the second embodiment of the present invention.

FIG. 5 is a view from above of FIG. 4e.

FIG. 6 is a structural diagram showing an optical biosensor according to a third embodiment of the present invention.

FIG. 7 is a diagram showing the results of examining the characteristics of an optical biosensor using a fluorescently labeled antigen.

FIG. 8 is a diagram showing the results of examining the characteristics of an optical biosensor using a fluorescently labeled antigen.

FIG. 9 is a schematic structural diagram of a conventional optical biosensor.

[Explanation of symbols]

11 Optical Waveguide 12 Substrate 13 Dielectric Multilayer Mirror 14 Transparent Electrode 15 Aromatic Phenyldiamine (PDA) Layer 16 Aluminum Quinolinol Complex (Alq ₃ ) Layer 17 Indium Electrode 18 Antibody 19 Frame 20 Sample Liquid 21 Antigen 22 FITC Labeled Antigen 23 Evanescent Wave 24a, 24b, 24c Photodetector 25 Lower metal electrode 26 Upper metal electrode

Claims (14)

[Claims] 1. An optical waveguide in which an antigen that reacts with a predetermined substance or an antibody that reacts with a predetermined substance is immobilized on the surface and an organic electroluminescence device that emits excitation light are formed on the same substrate. An optical biosensor characterized by. 2. The optical biosensor according to claim 1, wherein the organic electroluminescent device is an edge emitting organic electroluminescent device. 3. The optical biosensor according to claim 2, wherein the end face of the edge emitting organic electroluminescent device and the end face of the optical waveguide are combined and formed on a substrate. 4. The edge emitting organic electroluminescent device comprises a dielectric multilayer mirror, a transparent electrode, a hole transport layer, a light emitting layer, an electron transport layer and a metal electrode, which are laminated in this order on a substrate having an optical waveguide formed thereon. The optical biosensor according to claim 2, wherein the optical biosensor is formed in a structure. 5. The edge emitting organic electroluminescence device is formed in a structure in which a metal electrode, a hole transport layer, a light emitting layer, an electron transport layer, and a metal electrode are laminated in this order on a substrate having an optical waveguide formed thereon. The optical biosensor according to claim 2, wherein: 6. An optical waveguide having an antigen reactive with a predetermined substance or an antibody reactive with a predetermined substance immobilized on its surface and an organic electroluminescent device for emitting excitation light are formed on the same substrate, and an end face of the optical waveguide is formed. An optical biosensor, characterized in that the end faces of the organic electroluminescent device are optically coupled to each other. 7. The optical biosensor according to claim 1, wherein the organic electroluminescent element is formed so as to be covered with an optical waveguide. 8. The organic electroluminescent device is formed in a structure in which a metal electrode, a hole transport layer, a light emitting layer, an electron transport layer, and a metal electrode are laminated in this order on a substrate having an optical waveguide formed thereon. The optical biosensor according to claim 7. 9. An optical waveguide is formed on a substrate, and then the optical waveguide at a location where an organic electroluminescent device is to be formed is deleted from the substrate, and a dielectric multilayer film mirror is formed at the portion where the optical waveguide is deleted.
A transparent electrode, a hole transport layer, a light emitting layer, an electron transport layer, and a metal electrode are laminated in this order to form an organic electroluminescent device, and an antigen that reacts with a predetermined substance or an antibody that reacts with a predetermined substance is formed. A method for manufacturing an optical biosensor, in which an optical waveguide immobilized on a surface and an organic electroluminescent element that emits excitation light are formed on the same substrate. 10. The method for manufacturing an optical biosensor according to claim 9, wherein the light emitting layer and the electron transporting layer are composed of one layer. 11. An optical waveguide is formed on a substrate, and then the optical waveguide at a portion where an organic electroluminescent device is to be formed is removed from the substrate, and a metal electrode, a hole transport layer, and a light emitting layer are removed at the portion where the optical waveguide is removed. , An electron transport layer, and a metal electrode are laminated in this order to form an organic electroluminescence device, and an optical waveguide having an antigen that reacts with a predetermined substance or an antibody that reacts with a predetermined substance immobilized on the surface, and excitation. A method for manufacturing an optical biosensor, in which an organic electroluminescent element that emits light is formed on the same substrate. 12. The method for manufacturing an optical biosensor according to claim 11, wherein the light emitting layer and the electron transporting layer are composed of one layer. 13. The method for manufacturing an optical biosensor according to claim 9, wherein the end faces of the optical waveguide and the end faces of the organic electroluminescent element are formed so as to be optically coupled to each other. 14. A metal electrode, a hole transporting layer, a light emitting layer, an electron transporting layer, and a metal electrode are laminated in this order on a substrate to form an organic electroluminescent device, which is in contact with the substrate and the organic electroluminescent device is formed. An optical waveguide in which an antigen that reacts with a predetermined substance or an antibody that reacts with a predetermined substance is immobilized on the surface, and an organic electroluminescent device that emits excitation light, characterized by forming a thin-film optical waveguide so as to cover it. A method for manufacturing an optical biosensor in which the same is formed on the same substrate.