JP2003262634A - DNA chip and DNA detection device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a DNA chip capable of shortening the hybridizing time of a specimen, such as blood. <P>SOLUTION: The DNA chip is provided with a substrate; a first optical waveguide layer formed on the surface of the substrate; gratings formed respectively on both end surfaces of the first optical waveguide layer; a second optical waveguide layer, which is formed on the first optical waveguide layer situated between the gratings and which is composed of a transparent conductive material at a refractive index higher than that of the first optical waveguide layer; a poly-L-lysine film formed on the second optical waveguide layer; and an electrode thin film, the one end of which is extended to the poly-L-lysine film and which generates an electric charge between itself and the second optical waveguide layer. <P>COPYRIGHT: (C)2003,JPO

Description

Detailed Description of the Invention

[0001]

TECHNICAL FIELD The present invention relates to a DNA chip and a DNA detection device.

[0002]

2. Description of the Related Art As a conventional DNA chip, one having a structure in which a poly-L-lysine film is formed on the surface of a slide glass is known. In order to detect the DNA of the target solution with such a DNA chip, the following procedure is performed. That is, for example, a plurality of single-stranded DNAs are immobilized on the poly-L-lysine film of the slide glass. Continuing,
A target solution is placed in the contact moisture chamber to the poly-L-lysine membrane and incubated at 65 ° C. for 10 to 20 minutes for hybridization. After hybridization, let the intercalator with dye marker act,
The DNA in the target solution is detected by optically reading the fluorescence from the DNA chip with a scanner.

[0003]

However, the conventional DNA chip has a problem that it takes a long time to hybridize.

The present invention is intended to provide a DNA chip capable of shortening the hybridization time of a specimen such as blood.

The present invention intends to provide a DNA detection device capable of simultaneously and in parallel identifying DNA in a plurality of specimens such as blood with high sensitivity and shortening the detection time. Is.

[0006]

A DNA chip according to the present invention comprises a substrate, a first optical waveguide layer formed on the surface of the substrate, and gratings formed on both end surfaces of the first optical waveguide layer. A second optical waveguide layer formed on the first optical waveguide layer located between the gratings, the second optical waveguide layer being made of a conductive material having a higher refractive index than that of the first optical waveguide layer, and the second optical waveguide layer. A poly-L-lysine film formed on the poly-L-lysine film; and an electrode thin film having one end extending on the poly-L-lysine film and generating an electric charge between the poly-L-lysine film and the second optical waveguide layer. To do.

Another DNA chip according to the present invention is a substrate, a first optical waveguide layer formed on the surface of the substrate, a grating formed on each end surface of the first optical waveguide layer, and the grating. A second optical waveguide layer formed on the first optical waveguide layer located between the first optical waveguide layer and made of a conductive material having a higher refractive index than the first optical waveguide layer and being transparent;
A poly-L-lysine film formed on the second optical waveguide layer,
One end extends over the poly-L-lysine film and surrounds at least the electrode thin film for generating charges with the second optical waveguide layer and the poly-L-lysine film located between the gratings. And a well of the above.

The DNA detection device according to the present invention comprises a substrate,
A plurality of first optical waveguide layers formed on the surface of the substrate, gratings formed on both end surfaces of each of the first optical waveguide layers, and on each of the first optical waveguide layers located between the gratings. Each formed on this first
A plurality of second optical waveguide layers made of a conductive material having a higher refractive index than the optical waveguide layers, a plurality of poly L lysine films respectively formed on the respective second optical waveguide layers, and one end of each of the poly L D including a plurality of electrode thin films extending on the lysine film and generating charges between the lysine film and the second optical waveguide layer
NA chip; laser element for making laser light incident on one end of each first optical waveguide layer of the DNA chip; the DNA
A light receiving element for receiving light emitted from the other end of each first optical waveguide layer of the chip; and a polygon mirror arranged between the DNA chip and the laser element.

Another DNA detection apparatus according to the present invention is a substrate, a plurality of first optical waveguide layers formed on the surface of the substrate, and gratings formed on both end surfaces of each of the first optical waveguide layers. And a plurality of second optical waveguide layers each formed on each of the first optical waveguide layers positioned between the gratings and made of a conductive material having a higher refractive index than the first optical waveguide layers, A plurality of poly-L-lysine films respectively formed on the second optical waveguide layer, and a plurality of one ends extending over the poly-L-lysine films for generating charges between the second optical waveguide layers Electrode thin film and a plurality of wells for at least surrounding each poly-L-lysine film located between the gratings.
NA chip; laser element for making laser light incident on one end of each first optical waveguide layer of the DNA chip; the DNA
A light receiving element for receiving light emitted from the other end of each first optical waveguide layer of the chip; and a polygon mirror arranged between the DNA chip and the laser element.

[0010]

BEST MODE FOR CARRYING OUT THE INVENTION The DNA chip and the DNA detection device of the present invention will be described below in detail with reference to the drawings.

(First Embodiment) FIG. 1 is a plan view showing a DNA chip used in the first embodiment, and FIG. 2 is shown in FIG.
2 is a sectional view taken along line II-II, and FIG. 3 is a sectional view taken along line III-III in FIG.

A substrate 1 made of glass, for example, has a plurality of first optical waveguide layers 2 having a higher refractive index than the substrate 1, for example, four first optical waveguide layers 2 formed on the surface in parallel with each other. These first optical waveguides 2 are formed, for example, by immersing in an ion exchange solution such as a molten salt of potassium nitrate at 380 to 400 ° C. to ion exchange high refractive index elements such as potassium and sodium. The grating 3 includes the first optical waveguide layer 2
Has a refractive index equal to or higher than that of the first optical waveguide layer 2 and is formed on both end surfaces of the respective first optical waveguide layers 2. These gratings 3 are made of photoresist, titanium oxide, zinc oxide, lithium niobate, GaAs, for example.

As shown in FIG. 2, the second optical waveguide layer 4 having a slanted end in the length direction has a higher refractive index than the first optical waveguide layer 2, and has a refractive index between the two gratings 3. Is formed on each of the first optical waveguide layers 2 located at. These second optical waveguide layers 4 are made of, for example, ITO.
Or it is made from a transparent conductive material such as tin oxide. The poly-L-lysine film 5 is formed on each flat surface of the second optical waveguide 4.

The protective film 6 is formed on the substrate 1 including the first optical waveguide layers 2 so that the periphery including the grating 3 and the poly-L-lysine film 5 are exposed. The protective film 6 is made of, for example, a fluororesin.

A plurality of, for example, four electrode thin films 7 are formed on the protective film 6 located between the first optical waveguide layers 2 to form the first thin film.
An extension 8 is formed in parallel with the optical waveguide layer 2 and extends on the poly-L-lysine film 5 near the center. These electrode thin films 7 are made of a metal such as Au, Pt, or Ti.

Another electrode thin film (reference electrode) 9 made of a metal such as Au, Pt, or Ti and a standard electrode 10 made of an Ag / AgCl thin film are formed on the protective film 6 located around the substrate 1. ing. That is, the electrode thin film 7, the reference electrode 9, and the standard electrode 10 form an electrochemical triode structure.

The planar heater 11 is formed on the back surface of the substrate 1 corresponding to each of the first optical waveguide layers 2. A thin film temperature sensor 12 for monitoring the temperature of the planar heater 11 is formed on the back surface of the substrate 1 adjacent to the planar heater 11.

Next, a DNA detection device equipped with the above-mentioned DNA chip 13 will be described with reference to FIG.

In this DNA detection device, a laser element (for emitting a laser beam) arranged on one end face side (right end face side) of the DNA chip 13 at which one end of the plurality of first optical waveguide layers 2 is exposed is provided. For example, a semiconductor laser having a wavelength of 650 nm) 21 is provided. A collimator lens 22, a polarizing plate 23 and a polygon mirror 24 are sequentially arranged on the laser light emitting side of the laser element 21. A galvanometer mirror may be used instead of the polygon mirror 24. A first cylinder lens 25 is arranged on the laser light emitting side of the polygon mirror 24 so as to be parallel to the right end surface of the DNA chip 13. The second cylinder lens 26 has the other end face side (left end face side) of the DNA chip 13 where the other ends of the plurality of first optical waveguide layers 2 are exposed.
It is located in. A second polarizing plate 27 and a light receiving element 28 are sequentially arranged on the laser light emitting side of the second cylinder lens 26.

In the DNA detection device, the D
The NA chip 13 is attachable and detachable, and a storage portion (not shown) is provided at the arrangement position.

Next, the above-mentioned DNA chip and DNA
The operation of the detection device will be described.

Single-stranded DNA is immobilized on each poly-L-lysine film 5 of the DNA chip 13. In this case, even if the single-stranded DNA immobilized on each poly-L-lysine membrane 5 is the same,
May be different. Further, the number of single-stranded DNA immobilized on each poly-L-lysine membrane 5 is not limited to one, and may be plural.

For example, a target solution such as blood, which is a sample, is contained in a plate (not shown) having a plurality of wells arranged in the same manner as each poly-L-lysine film 5 of the DNA chip 13, and the DNA chip is used. 13 is turned upside down and each poly-L-lysine membrane 5 on which the single-stranded DNA is immobilized is brought into contact with the target solution in the well. At this time, a voltage is supplied to the planar heater 11 on the back surface of the substrate 1 to generate heat, and the substrate 1 is heated to, for example, 65 ° C. and incubated. At the same time, the reference electrode 10 is, for example, 0.2
By applying a voltage of up to 0.3 V, a current flows between a plurality of electrode thin films 7, for example, four electrode thin films 7 and reference electrodes 9. 2 Electric charges are generated between the photoconductive layer 2 and the photoconductive layer 2. For this reason,
The charged DNA in the target solution of each well is attracted and concentrated toward the second photoconductive layer 2, that is, toward the poly-L-lysine film 5 located on the second photoconductive layer 2. As a result, the single-stranded DNA immobilized on each poly-L-lysine membrane 5 and the DNA in the target solution are hybridized in a short time.

The hybridized DNA chip 13 was incorporated into the DNA detection apparatus shown in FIG.
An intercalator with a dye marker is caused to act on the hybridized DNA of 3) to develop color.

In this state, as shown in FIG. 4, a laser beam having a wavelength of 650 nm is emitted from the laser element 21 to the polygon mirror 24 which is rotationally driven through the collimator lens 22 and the polarizing plate 23. At this time, the laser light is collimated by the collimator lens 22, adjusted so that the light intensities in the TE and TM modes are equalized by the polarizing plate 23, reflected by the polygon mirror 24 that is driven to rotate, and reflected by the four of the DNA chips 13. It is distributed toward the first optical waveguide layer 2. The distributed laser light is incident on the back surface side of the substrate 1 where the first optical waveguide layer 2 of the DNA chip 13 is located as shown in FIG. 5, and passes through the substrate 1 at the interface between the grating 3 and the first optical waveguide layer 2. It is refracted and propagated through the first optical waveguide layer 2. The laser light propagating through the first optical waveguide layer 2 has two modes (TM mode, TM mode) at the interface with the second optical waveguide layer 4 having a higher refractive index than the first optical waveguide layer 2.
TE mode), and propagates through the first and second optical waveguide layers 2 and 4. At this time, the poly-L-lysine film 5
The intensity of the light propagating through the second optical waveguide layer 4 directly below the poly-L-lysine film 5 changes due to changes (for example, changes in absorbance) due to hybridization and color development in (1). Thus, the light propagating through the first and second optical waveguide layers 2 and 4 is recombined and interferes at the interface between the optical waveguide layers 2 and 4 at the opposite end of the second optical waveguide layer 4. The change in the intensity of the light propagating through the second optical waveguide layer 4 can be amplified. As a result, the single-stranded DNA in the poly-L-lysine film 5 hybridizes with the DNA in the target solution, and minute changes in the light propagating through the second optical waveguide layer 4 due to the coloring caused by the dye marking also cause the second cylinder lens. It becomes possible to detect with the light receiving element 28 through 26 and the second polarizing plate 27. In addition, such a detection operation is performed by the DNA chip 13 described above.
In the plurality (four) of the first optical waveguide layers 2 simultaneously, in parallel, the DNA is identified.

Therefore, the first of the structures shown in FIGS.
According to the DNA chip of the embodiment, the hybridization time of the DNA in the target solution, which is the sample, to the single-stranded DNA immobilized on the poly-L-lysine film 5 can be significantly shortened.

Further, by providing the planar heater 11 and the thin film temperature sensor 12 on the back surface of the substrate 1, and controlling the heating temperature to the substrate 1 while monitoring the temperature of the planar heater 11 by the thin film temperature sensor 12, it is possible to use the conventional method. As described above, hybridization can be performed without using a moisture chamber.

Further, according to the DNA detection apparatus in which the DNA chips shown in FIGS. 1 to 3 having a plurality of chip units are incorporated as shown in FIG. 4, the DNAs of a plurality of specimens can be simultaneously identified in parallel with high sensitivity. In addition, the detection time can be shortened.

In the first embodiment described above, the first optical waveguide layer 2 in which the second optical waveguide layer 4 and the poly-L-lysine film 5 are laminated constitutes one chip unit, and a plurality of the chip units are arranged on the substrate 1. However, the DNA chip may be configured by disposing only one chip unit on the substrate.

In the above-described first embodiment, the contact operation between the single-stranded DNA immobilized on each poly-L-lysine film 5 and the target solution as the sample is performed in the same manner as for each poly-L-lysine film 5 of the DNA chip 13. Although this was performed using a plate having a plurality of wells arranged, for example, a filter paper impregnated with a target solution as a sample may be directly contacted with each poly-L-lysine membrane 5 on which single-stranded DNA is immobilized. .

(Second Embodiment) FIG. 6 is a plan view showing a DNA chip used in this second embodiment, and FIG.
7 is a sectional view taken along line VII-VII of FIG. 8, and FIG. 8 is a sectional view taken along line VIII-VIII of FIG. The same members as those in FIGS. 1 to 3 are designated by the same reference numerals and the description thereof will be omitted.

In this DNA chip 13, a frame 15 to which three partitions 14 parallel to each other are integrally attached is provided on a protective film 6 on which an electrode thin film 7 having an extending portion 8 is formed, via an adhesive agent. For example, four wells 16 having the poly-L-lysine film 5 exposed at the bottom are formed.

Next, a DNA detection device equipped with the above-mentioned DNA chip 13 will be described with reference to FIG.

In this DNA detecting device, a laser element (for emitting a laser beam) arranged on one end face side (right end face side) of the DNA chip 13 where one end of the plurality of first optical waveguide layers 2 is exposed ( For example, a semiconductor laser having a wavelength of 650 nm) 21 is provided. A collimator lens 22, a polarizing plate 23 and a polygon mirror 24 are sequentially arranged on the laser light emitting side of the laser element 21. A galvanometer mirror may be used instead of the polygon mirror 24. A first cylinder lens 25 is arranged on the laser light emitting side of the polygon mirror 24 so as to be parallel to the right end surface of the DNA chip 13. The second cylinder lens 26 has the other end face side (left end face side) of the DNA chip 13 where the other ends of the plurality of first optical waveguide layers 2 are exposed.
It is located in. A second polarizing plate 27 and a light receiving element 28 are sequentially arranged on the laser light emitting side of the second cylinder lens 26.

In the DNA detection device, the D
The NA chip 13 is attachable and detachable, and a storage portion (not shown) is provided at the arrangement position.

Next, the above-mentioned DNA chip and DNA
The operation of the detection device will be described.

Single-stranded DNA is immobilized on each poly-L-lysine film 5 at the bottom of the well 16 of the DNA chip 13.
In this case, the single chain D immobilized on each poly-L-lysine membrane 5
NA may be the same or different. Further, the number of single-stranded DNA immobilized on each poly-L-lysine membrane 5 is not limited to one, and may be plural.

In each well 16 of the DNA chip 13 is shown in FIG.
As shown in 0, a target solution 17 such as blood, which is a sample, is housed, and a voltage is supplied to the planar heater 11 on the back surface of the substrate 1 to generate heat, and the temperature of the substrate 1 is heated to, for example, 65 ° C. Incubate. At the same time, by applying a voltage of, for example, 0.2 to 0.3 V to the standard electrode 10, a plurality of, for example, four electrode thin films 7 and reference electrodes 9 are applied.
Since a current flows between the electrode thin film 7 and each of the electrode thin films 7, an electric charge is generated between the extended portion 8 of each electrode thin film 7 and the second photoconductive layer 2 made of a conductive material. Therefore, the target solution 1 of each well 16
The charged DNA in 7 is attracted and concentrated toward the second photoconductive layer 2, that is, toward the poly-L-lysine film 5 located on the second photoconductive layer 2. Therefore, the single-stranded DNA immobilized on each poly-L-lysine membrane 5 and the DNA in the target solution are hybridized in a short time.

The hybridized DNA chip 13 was incorporated into the DNA detection device shown in FIG.
An intercalator with a dye marker is caused to act on the hybridized DNA of 3) to develop color.

In such a state, as in the first embodiment described above, laser light having a wavelength of 650 nm, for example, is emitted from the laser element 21, collimated by the collimator lens 22, and the TE and TM mode light intensities are obtained by the polarizing plate 23. Are adjusted so that they are the same, and the four first optical waveguide layers 2 of the DNA chip 13 are reflected by the polygon mirror 24 that is rotationally driven.
Sort towards. Figure 1 shows the distributed laser light.
As shown in 0, the first optical waveguide layer 2 of the DNA chip 13 is incident on the back surface side of the substrate 1 where the first optical waveguide layer 2 is located.
Are propagated and are divided into two modes (TM mode and TE mode) at the interface with the second optical waveguide layer 4 having a higher refractive index than the first optical waveguide layer 2, and the first and second optical waveguide layers 2 , 4
Propagate. At this time, the intensity of light propagating through the second optical waveguide layer 4 directly below the poly-L-lysine film 5 changes due to a change (for example, a change in absorbance) due to hybridization and color development in the poly-L-lysine film 5. Like this,
The light propagating through the second optical waveguide layers 2 and 4 is recombined and interferes at the interface between the optical waveguide layers 2 and 4 at the end portion on the opposite side of the second optical waveguide layer 4. Layer 4
It is possible to amplify a change in the intensity of the light propagating through. As a result, the single-stranded DNA in the poly-L-lysine film 5 hybridizes with the DNA in the target solution, and minute changes in the light propagating through the second optical waveguide layer 4 due to the coloring caused by the dye marking also cause the second cylinder lens. It becomes possible to detect with the light receiving element 28 through 26 and the second polarizing plate 27. Further, such a detecting operation is simultaneously and in parallel performed in the plurality (four) of the first optical waveguide layer 2 and the second optical waveguide layer 4 of the DNA chip 13 to identify the DNA.

Therefore, the second structure shown in FIGS.
According to the DNA chip of the embodiment, the hybridization time of the DNA in the target solution, which is the sample, to the single-stranded DNA immobilized on the poly-L-lysine film 5 can be significantly shortened. Therefore, the DNA detection device incorporating this DNA chip can identify the DNA with high sensitivity and shorten the detection time.

Further, the planar heater 11 and the thin film temperature sensor 12 are provided on the back surface of the substrate 1, and the heating temperature for the substrate 1 is controlled while the temperature of the planar heater 11 is monitored by the thin film temperature sensor 12. As described above, hybridization can be performed without using a moisture chamber.

Further, according to the DNA detection apparatus in which the DNA chip 13 shown in FIGS. 6 to 8 having a plurality of chip units is incorporated as shown in FIG. 9, the DNAs of a plurality of specimens can be identified simultaneously in parallel with high sensitivity. And the detection time can be shortened.

Furthermore, the DNA chip 13 has a plurality of wells 16 each capable of containing a target solution 17,
Moreover, since the planar heater 11 is provided on the back surface of the substrate 1, it is possible to carry out hybridization in a state in which the DNA chip 13 is incorporated in the DNA detection device as shown in FIG. Information can be detected.

In the second embodiment described above, the well 1
The first optical waveguide layer 2 in which the poly-L-lysine film 5 and the second optical waveguide layer 4 are laminated under 6 is set as one chip unit, and a plurality of this chip unit are arranged on the substrate 1, but only one chip unit is formed on the substrate. Alternatively, the DNA chip may be arranged in the above.

[0046]

As described above in detail, according to the present invention, it is possible to provide a DNA chip capable of shortening the hybridization time of a specimen such as blood.

Further, according to the present invention, DNA in a plurality of specimens such as blood can be simultaneously identified in parallel with high sensitivity, and the detection time can be shortened.
A detection device can be provided.

[Brief description of drawings]

FIG. 1 is a plan view showing a DNA chip used in a first embodiment of the present invention.

FIG. 2 is a sectional view taken along line II-II in FIG.

FIG. 3 is a sectional view taken along the line III-III in FIG.

FIG. 4 is a plan view showing a DNA detection device used in the first embodiment of the present invention.

FIG. 5 is a cross-sectional view for explaining the operation of the DNA detection device according to the first embodiment of the present invention.

FIG. 6 is a plan view showing a DNA chip used in the second embodiment of the present invention.

7 is a sectional view taken along line VII-VII of FIG.

8 is a sectional view taken along the line VIII-VIII in FIG.

FIG. 9 is a plan view showing a DNA detection device used in the second embodiment of the present invention.

FIG. 10 is a cross-sectional view for explaining the operation of the DNA detection device according to the second embodiment of the present invention.

[Explanation of symbols]

1 ... substrate, 2 ... the first optical waveguide layer, 3 ... Grating, 4 ... a second optical waveguide layer, 5 ... Poly L lysine film, 6 ... protective film, 7 ... Electrode thin film, 11 ... A sheet heater, 13 ... DNA chip, 14 ... partition, 15 ... frame, 16 ... well, 17 ... Target solution (sample), 21 ... Laser element, 24 ... Polygon mirror, 28 ... Light receiving element.

Front page continuation (51) Int.Cl. ⁷ Identification code FI theme code (reference) G01N 21/01 G01N 21/78 Z 21/78 37/00 102 37/00 102 G02B 6/12 A G02B 6/122 C12N 15/00 F (72) Inventor Ichiro Higashino 33 Shinisogo-cho, Isogo-ku, Yokohama-shi, Kanagawa F-term (reference) 2T052 AA07 BA02 BB13 CA22 CE02 EA04 EB01 FA17 FA19 FA20 FA32 FA33 GA03 GA05 GA06 GE06 GE09 2G059 AA05 BB04 BB12 CC16 DD03 DD13 DD16 EE01 EE09 FF12 GG01 GG04 HH02 HH06 JJ05 JJ11 JJ13 JJ17 JJ19 KK01 2H047 KA02 KA13 KB03 KB06 KB08 LA01 MA01 RA01 4B14 A20B20A20A19 4B024 A19 CA09 KB03 KB06

Claims (8)

[Claims] 1. A substrate, a first optical waveguide layer formed on the surface of the substrate, gratings formed on both end surfaces of the first optical waveguide layer, and the first optical waveguide layer located between the gratings. A second optical waveguide layer formed on the optical waveguide layer and made of a conductive material having a refractive index higher than that of the first optical waveguide layer, and a poly-L-lysine film formed on the second optical waveguide layer; Is provided on the poly-L-lysine film, and an electrode thin film for generating an electric charge between the poly-L-lysine film and the second optical waveguide layer is provided. 2. The first optical waveguide layer, the grating formed on both end surfaces of the first optical waveguide layer,
The second optical waveguide layer, the poly-L-lysine film and the electrode thin film form one chip unit, and the chip unit is formed on the surface of the substrate such that the first optical waveguide layers are parallel to each other. Item 1. A DNA chip according to item 1. 3. A substrate, a first optical waveguide layer formed on the surface of the substrate, gratings formed on both end surfaces of the first optical waveguide layer, and the first optical waveguide located between the gratings. A second optical waveguide layer formed on the optical waveguide layer and made of a conductive material having a refractive index higher than that of the first optical waveguide layer and transparent; a poly-L-lysine film formed on the second optical waveguide layer; To extend over the poly-L-lysine film, and to surround at least the poly-L-lysine film located between the grating and an electrode thin film for generating charges between the poly-L-lysine film and the second optical waveguide layer. A DNA chip having a well. 4. The first optical waveguide layer, the grating formed on both end surfaces of the first optical waveguide layer,
The second optical waveguide layer, the poly-L-lysine film, the electrode thin film and the well constitute one chip unit, and the chip unit is formed on the surface of the substrate such that the first optical waveguide layers are parallel to each other. The DNA chip according to claim 3. 5. The DNA chip according to claim 3, wherein the well is formed by mounting a synthetic resin frame on the substrate. 6. The D according to claim 1, further comprising a heater arranged on the back surface of the substrate.
NA chip. 7. A substrate, a plurality of first optical waveguide layers formed on the surface of the substrate, gratings respectively formed on both end surfaces of each of the first optical waveguide layers, and located between the gratings. The first optical waveguide layer is formed on each of the first optical waveguide layers.
A plurality of second optical waveguide layers made of a conductive material having a higher refractive index than the optical waveguide layers, a plurality of poly L lysine films respectively formed on the respective second optical waveguide layers, and one end of each of the poly L D including a plurality of electrode thin films extending on the lysine film and generating charges between the lysine film and the second optical waveguide layer
NA chip; laser element for making laser light incident on one end of each first optical waveguide layer of the DNA chip; the DNA
A DNA detection device comprising: a light receiving element for receiving light emitted from the other end of each first optical waveguide layer of the chip; and a polygon mirror arranged between the DNA chip and the laser element. 8. A substrate, a plurality of first optical waveguide layers formed on the surface of the substrate, a grating formed on each end surface of each of the first optical waveguide layers, and located between the gratings. The first optical waveguide layer is formed on each of the first optical waveguide layers.
A plurality of second optical waveguide layers made of a conductive material having a higher refractive index than the optical waveguide layers, a plurality of poly L lysine films respectively formed on the respective second optical waveguide layers, and one end of each of the poly L A plurality of electrode thin films extending over the lysine film for generating charges between the second optical waveguide layer and a plurality of electrode thin films for surrounding at least the poly-L lysine films positioned between the gratings. Chip with a well; a laser element for injecting laser light into one end of each first optical waveguide layer of the DNA chip; light emitted from the other end of each first optical waveguide layer of the DNA chip And a polygon mirror arranged between the DNA chip and the laser element.