JP3687297B2 - Biosensor - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to a biosensor, and more particularly to a biosensor that detects the concentration of a substrate in a sample solution.
[0002]
[Prior art]
Conventionally, there are methods as described below for easily measuring the glucose concentration by a colorimetric method. First, when a body fluid is dropped onto a test paper impregnated with glucose oxidase, peroxidase, and a color reagent, glucose in the body fluid is oxidized by the action of glucose oxidase, and hydrogen peroxide is generated at the same time. Peroxidase acts on this hydrogen peroxide to generate active oxygen, and this active oxygen oxidizes the chromogen to cause coloration. This color is visually compared with a color chart, and the glucose concentration is qualitatively measured to determine whether or not the blood glucose level is high.
In addition, in order to quantitatively measure the glucose concentration, as shown in FIG. 9, the sample reaction layer 1b of the member 1 to be measured is composed of the substrate 1a from which the coloration result is obtained and the sample reaction layer 1b on the substrate 1a. The surface is irradiated with light 4 of a predetermined wavelength from a light source 2 comprising, for example, an LED or a semiconductor laser, the reflected light is received by the light receiving element 3, the intensity of the reflected light is converted into a glucose concentration, and glucose is There is a method to measure quantitatively.
[0003]
[Problems to be solved by the invention]
However, the method for visually determining the glucose concentration using the color chart as described above can only be used for qualitative measurement, and can be used only for primary screening applications, for example, and has a limited application range. It was.
[0004]
Further, in the method of measuring the reflection intensity described above, quantitative measurement can be performed, but if the member to be measured 1 is exposed and there is too much sample liquid, the sample liquid directly touches the light source 2 or the light receiving element 3. Therefore, there is a possibility that these optical instruments are soiled. For this reason, there exists a problem of having a bad influence on the light irradiation amount and light reception sensitivity of an optical apparatus. Further, in order to make it reflective, it is necessary to dispose the element obliquely, the optical path length becomes long, and there is a problem that the diffused light 5 from the member 1 to be measured cannot be received efficiently. When the sample reaction layer 1b is thickened to increase the reflection intensity of the sample reaction layer 1b in the member to be measured 1, the amount of sample liquid necessary for measurement becomes necessary as the thickness increases. Conversely, if the thickness of the sample reaction layer 1b is reduced so that measurement can be performed with a small amount of sample solution, the light traveling from the light source 2 is structurally inclined with respect to the member 1 to be measured. After being transmitted, reflection is likely to occur at the interface between the substrate 1a and the sample reaction layer 1b having different refractive indexes, causing irregular reflection in the member 11 to be measured, and the amount of light received by the light receiving element 3 becomes small. It was.
[0005]
The problem to be solved by the present invention lies in what means should be taken to obtain a biosensor with high light receiving efficiency with respect to emitted light and capable of highly accurate detection.
[0006]
[Means for Solving the Problems]
Therefore, the invention according to claim 1 is a biosensor,
A measuring device in which a light emitting unit and a light receiving unit are arranged to face each other through a measurement space;
A measurement cell in which a sample reaction layer is disposed on a light-transmitting substrate and a sample liquid introduction part that can be inserted into the measurement space is formed;
With
The sample solution introduction part is provided with a sample solution introduction port in a width direction perpendicular to the insertion direction of the measurement cell, and the width of the sample solution introduction part is wider than the width of the measurement space of the measurement device. It is a feature.
[0007]
In the first aspect of the invention, since the measurement cell can be inserted into the measurement space between the light emitting part and the light receiving part, the light irradiated from the light emitting part is colored by the sample reaction layer colored by the contact of the sample liquid. The colored light can be transmitted as it is without being reflected on the surface of the sample reaction layer and reach the light receiving portion. By adopting such a structure, a transmissive biosensor can be obtained, so that the sample reaction layer has a surface direction of the sample reaction layer out of the emitted light radiated in a plurality of traveling directions of the light emitting portion. The light can be arranged so that the amount of light traveling in a substantially vertical direction is maximized, and the irregular reflection of light on the sample reaction layer or the substrate can be suppressed to the minimum, and the light receiving efficiency can be improved. Moreover, the thickness of the sample reaction layer can be reduced by using a transmission type biosensor, and high-precision measurement can be performed with a small amount of sample solution. In addition, since the light-emitting part and the light-receiving part are arranged to face each other through the measurement space and the transmitted light from the sample reaction layer is received by the light-receiving part, the light-emitting part and the light-receiving part are separated from the sample reaction layer. As close as possible. For this reason, the optical path length can be shortened, and diffused light from the sample reaction layer can be received efficiently.
[0008]
According to a second aspect of the invention, a biosensor according to claim 1, wherein the measuring cell has a substrate over the sample reaction layer, a spacer is interposed between the substrate, the spacer forms the A sample liquid is introduced along the sample liquid inlet.
[0009]
In the invention according to claim 2, since the sample reaction layer exists between the substrates, the light emitting portion and the light receiving portion are not directly touched, and the light emitting portion and the light receiving portion are not contaminated with the sample liquid. For this reason, the substrate concentration can be measured with higher accuracy. Since the sample solution is introduced into the groove formed by the spacer, for example, by narrowing the groove, the sample solution can be reliably guided to the sample reaction layer by capillary action.
[0010]
The invention according to claim 3 is the biosensor according to claim 2, wherein the sample liquid inlet of the measurement cell is exposed from the measurement device in a state where the measurement cell is inserted into the measurement device. Yes.
[0011]
In the invention according to claim 3, the sample solution introduction port can be provided at a position away from the light emitting unit and the light receiving unit. For this reason, it can suppress that a light emission part and a light-receiving part are soiled with a sample liquid. Moreover, after inserting a measurement cell into a measuring apparatus, a sample liquid can be introduce | transduced from a sample liquid inlet and can be measured.
[0012]
A fourth aspect of the present invention is the biosensor according to any one of the first to third aspects, wherein the measuring device includes a pair of the light emitting unit and the light receiving unit facing each other through the measurement space. However, a plurality of pairs are arranged, and a plurality of sample reaction layers are arranged at positions corresponding to the pair of the light emitting unit and the light receiving unit in the measurement cell.
[0013]
In the invention according to claim 4, the substrate concentration in a plurality of sample reaction layers can be measured independently. For this reason, it is possible to measure a plurality of kinds of substrate concentrations by one measurement, and it is possible to obtain a biosensor capable of performing an efficient measurement.
According to a fifth aspect of the present invention, the circumference surrounding the measurement space of the measuring device is the light of the light emitting part, and the light colored by the color reaction due to the contact of the sample liquid with the sample reaction layer. It has a characteristic of reflecting.
[0014]
DETAILED DESCRIPTION OF THE INVENTION
Hereinafter, details of the biosensor according to the present invention will be described based on each embodiment shown in the drawings.
(Embodiment 1)
FIG. 1 is a sectional view showing Embodiment 1 of a biosensor according to the present invention, and FIG. 2 is a plan view thereof. Moreover, Fig.3 (a) is a top view which shows the measurement cell used for the biosensor of this embodiment, FIG.3 (b) is XX sectional drawing of Fig.3 (a).
[0015]
As shown in FIG. 1, the biosensor 11 of the present embodiment includes a measurement device 12 and a measurement cell 13.
[0016]
In the measuring device 12, an insertion gap 14 for inserting the measurement cell 13 is formed at the distal end portion 12A, and the light emitting element 15 as a light emitting portion and the light receiving element as a light receiving portion are opposed to each other with the insertion gap 14 interposed therebetween. 16 are arranged. The light emitting element 15 is, for example, an LED serving as a light source. As the light receiving element 16, various photosensors that perform photoelectric conversion can be used. Note that the width dimension W1 of the distal end portion 12A of the measuring device 12 is set to a dimension narrower than the width dimension W2 of the sample liquid introducing portion 13A of the measurement cell 13 to be described later. Has a property of reflecting light colored by a color reaction. Further, the light emitting element 15 and the light receiving element 16 are connected to a detection control unit (not shown), and a detection value in the detection control unit is displayed on a display device (not shown).
[0017]
The measurement cell 13 includes a lower substrate 17, a sample reaction layer 18, spacers 19 (19 </ b> A and 19 </ b> B), and an upper substrate 20. The lower substrate 17 is a transparent substrate made of, for example, a resin film or glass, and a sample reaction layer 18 containing glucose oxidase, peroxidase, and a color reagent is disposed and formed on the intermediate portion of the substrate. As shown in FIGS. 3A and 3B, the spacer 19 is composed of spacers 19A and 19B which are separately arranged at positions sandwiching the sample reaction layer 18, and the width dimension of the sample reaction layer 18 is the spacer 19A. , 19B are set to be the same as the mutual interval. A transparent upper substrate 20 is bonded on the spacer 19 in the same manner as the lower substrate 17. In such a measurement cell 13, the lower substrate 17 and the upper substrate 20 have the same shape, and the sample liquid introduction part 13A inserted into the insertion gap 14 of the distal end part 12A of the measurement apparatus 12 described above, and the sample A gripping portion 13B that protrudes in the direction opposite to the insertion direction is formed from an intermediate portion of the liquid introduction portion 13A. In the sample liquid introduction part 13A, a sample liquid introduction gap 21 which is a gap between the spacer 19A and the spacer 19B constituting the spacer 19 is formed so as to penetrate in the width direction. In this state, the sample reaction layer 18 is disposed in the middle portion of 21. As will be described later, in order to measure the absorbance, the sample reaction layer 18 is preferably a transparent gel-like layer. However, even if the sample reaction layer 18 is opaque, it should be transparent by absorbing the sample liquid. That's fine. Moreover, even if it is not completely transparent, it is sufficient if the light transmission amount changes significantly by reaction with a sample solution having a predetermined glucose concentration.
[0018]
Next, a measurement procedure in the case of measuring the substrate concentration in the sample solution using the biosensor 11 having such a configuration will be described.
[0019]
First, the gripping part 13B of the measurement cell 13 is picked by hand, and the measurement cell 13 in which no sample liquid is present in the sample liquid introduction gap 21 is inserted into the insertion gap 14 at the tip of the measurement apparatus 12. At this time, the measurement cell 13 maximizes the amount of light that travels substantially perpendicularly to the surface direction of the sample reaction layer 18 out of the emitted light radiated in a plurality of traveling directions of the light emitting element 15. Are arranged as follows. In other words, the sample reaction layer 18 is arranged so that the surface of the sample reaction layer 18 intersects perpendicularly to the line segment connecting the light emitting element 15 and the light receiving element 16. For this reason, irregular reflection of light in the measurement cell 13 can be suppressed to a minimum.
Then, light in a predetermined wavelength region is irradiated from the light emitting element 15, and the amount of light transmitted through the measurement cell 13 is measured by the light receiving element 16.
[0020]
Next, sample liquid such as urine is dropped from one opening of the sample liquid introduction gap 21 of the sample liquid introduction part 13A, or the sample liquid is attached to the opening, thereby causing the sample liquid by capillary action. Is sucked into the sample reaction layer 18. A predetermined time elapses with the sample solution adhering to the sample reaction layer 18, and the color reagent of the sample reaction layer 18 is colored to a predetermined color corresponding to the glucose concentration. Again, light in a predetermined wavelength region is irradiated from the light emitting element 15, and the amount of light transmitted through the measurement cell 13 through the sample reaction layer 18 colored by the light receiving element 16 is measured. In this way, the absorbance can be obtained from the light amount ratio before and after the injection of the sample solution and converted to the glucose concentration in the sample solution. Such calculation of absorbance and display of the glucose concentration are performed by a detection control unit or a display device (not shown).
[0021]
In the present embodiment, since the optical systems on the emission side and the incident side are linearly opposed and arranged, the optical element can be arranged close to the measurement cell. For this reason, at the time of absorbance measurement, as shown in FIG. 4, the optical path length L can be shortened, and as a result, light loss due to the generation of diffused light from the sample reaction layer 18 can be minimized. At the same time, the traveling direction of light toward the light emitting element 15 and the sample reaction layer 18 is substantially perpendicular to or in accordance with the surface direction of the sample reaction layer 18, so that the gas filled in the upper substrate 20 and the sample liquid introduction gap 21 and Even if adjacent members of the sample liquid, the sample reaction layer 18 colored by the sample liquid, and the lower substrate 17 have different refractive indexes, the light colored by the coloration is received by the light receiving element 16. The light loss is small because it goes straight ahead. The tip portion 12A that covers the entire measurement portion of the measurement cell 13 from above and below has the property of reflecting the light from the light emitting element 15, so that the light receiving element 16 can receive a large amount of light. For this reason, the light from the light emitting element 15 can be efficiently received by the light receiving element 16, and the measurement accuracy can be improved and the power consumption of the light source of the light emitting element 15 can be reduced. In addition, since the sample reaction layer 18 of the measurement cell 13 is disposed in the interior of the sample introduction gap 21 and the direction in which the sample liquid is introduced and the direction in which the measurement cell 13 is inserted into the measurement device 12 are perpendicular, the light emitting element 15 and the light receiving element Since the sample liquid does not directly touch an optical element such as 16, the element is not contaminated, and there is an advantage that maintenance of the measuring apparatus 12 is easy. Since the reflection at the sample reaction layer 18 is not required, the sample reaction layer 18 can be made thin, and a small amount of sample solution can be sufficiently measured.
[0022]
In Embodiment 1 described above, potassium iodide, 4-aminoantipyrine, O-tolidine, tetramethylbenzidine, or the like can be used as the color sample. Further, it is desirable to use a light source in an optimum wavelength range that can take a large dynamic range according to each sample.
[0023]
Further, if another oxidase such as lactate oxidase is used instead of glucose oxidase, the concentration of lactic acid in the sample solution can be measured. Thus, if the enzyme reacts with a substrate to generate hydrogen peroxide, the substrate concentration corresponding to each enzyme can be measured. As such an oxidase, alcohol oxidase, cholesterol oxidase or the like can be used.
[0024]
Furthermore, if a color reaction without using an enzyme, for example, a color reaction caused by binding of tetrabromophenol blue to a protein is detected, it can be used as a protein measuring apparatus. In addition, if a reagent used in the urine test paper method is used, occult blood, bilirubin, urobilinogen, ketone bodies, nitrites, leukocytes, specific gravity, PH and the like can be measured. Any reagent that causes a color reaction can be applied to the present embodiment.
[0025]
Furthermore, in this embodiment, it is also possible to measure the substrate concentration in solutions such as river water and beverages as well as body fluids such as blood, urine, sweat and tears as reagent solutions.
[0026]
(Embodiment 2)
Next, Embodiment 2 of the biosensor according to the present invention will be described with reference to FIG. In addition, in this embodiment, the same part as the said Embodiment 1 is attached | subjected to the same code | symbol, and description is abbreviate | omitted.
[0027]
In the present embodiment, the configuration of the measurement cell 13 constituting the biosensor 11 is substantially the same as that of the first embodiment. In particular, in the present embodiment, the spacer 19 (19A, 19B) is formed of a transparent material. . Further, the measuring device 12 includes a pair of a light emitting element 15A and a light receiving element 16A, and a pair of the light emitting element 15B and the light receiving element 16B facing each other across the insertion gap 14 along the insertion direction of the insertion gap 14. Two pairs of photocouplers are arranged. Note that the light emitting element 15A and the light emitting element 15B have the same light emission output. Then, as shown in FIG. 5, the sample reaction layer 18 is located in the inner space of the insertion gap 14 and the light receiving element 16 </ b> B with the measurement cell 13 being inserted into the insertion gap 14 of the measurement device 12. It is set to be located between. Further, in this state, a portion (lower substrate 17, spacer 19A, upper substrate 20) of the measurement cell 13 on the gripping portion 13B side is inserted between the light emitting element 15A and the light receiving element 16A. .
[0028]
A procedure for measuring the substrate concentration in the sample solution using the biosensor 11 having such a configuration will be described below. First, the measurement cell 13 is inserted into the insertion gap 14 at the tip of the measurement device 12. Next, the sample solution is dropped on one sample solution introduction portion 13A of the measurement cell 13, or the sample solution introduction portion 13A is brought into contact with the sample solution, and the sample solution is guided to the sample reaction layer 18 by capillary action. And after predetermined time progress, the light of the same wavelength range is irradiated from light emitting element 15A, 15B, and the light quantity is measured with light receiving element 16A, 16B corresponding to each light emitting element 15A, 15B. The light receiving element 16A measures the amount of light transmitted through the upper and lower substrates 17 and 20 and the spacer 19A, and the light receiving element 16B measures the amount of light transmitted through the upper and lower substrates 17 and 20 and the sample reaction layer 18. The measurement data obtained by these light receiving elements 16A and 16B is compared with a detection control unit (not shown) to determine the absorbance, and as a result, converted into a glucose concentration, and the glucose concentration is displayed on the display device. It has become.
[0029]
The material of the spacer 19A described above is preferably a material having the same light transmittance as that of the sample liquid, but it is sufficient that the light transmittance ratio between the sample liquid and the spacer 19A is known even with a material having a different light transmittance. In this case, the absorbance may be obtained by adding the transmittance ratio between the sample liquid and the spacer 19A to the light quantity measurement results by the light receiving elements 16A and 16B.
[0030]
In this embodiment, since the spacer 19A is formed of a transparent material, it has a structure in which the amount of light transmitted through the sample reaction layer 18 and the spacer portion can be measured at the same time, and the time for measuring the reference transmitted light separately from the sample liquid transmitted light. Since it can be omitted, the measurement time can be shortened.
[0031]
(Embodiment 3)
FIG. 6 shows Embodiment 3 of the biosensor according to the present invention. In the description of the configuration of the present embodiment, the same parts as those of the first embodiment are denoted by the same reference numerals, and the description thereof is omitted.
[0032]
In the present embodiment, a concave portion 17A is formed in a portion where the sample reaction layer 18 of the lower substrate 17 of the measurement cell 13 is disposed, and the sample reaction layer 18 is formed in the concave portion 17A. This is the same as the first embodiment.
[0033]
In the present embodiment, the substrate concentration in the sample solution can be measured by performing the same measurement procedure as in the first embodiment. In particular, in the present embodiment, since the recess 17A that accommodates the sample reaction layer 18 is formed in the lower substrate 17, when the sample solution flows along the sample solution introduction gap 21, the reagent in the recess 17A is transferred to the sample solution. Therefore, the sample reaction layer 18 can be localized between the light emitting element 15 and the light receiving element 16 in a reliable state without being caused to flow into the osmotic flow. For this reason, the biosensor of this embodiment has an advantage that measurement with high efficiency and accuracy can be performed.
[0034]
In the present embodiment, the recess 17A is formed in the lower substrate 17, but as shown in FIGS. 7A and 7B, between the lower substrate 17 and the upper substrate 20 of the measurement cell 13. Alternatively, the first spacer 22 and the second spacer 23 may be interposed between the first spacer 22 and the first spacer 22 so as to have an opening 22 </ b> A for accommodating the sample reaction layer 18. The second spacer 23 is divided into two parts before and after the insertion direction so as to sandwich the opening 22A of the first spacer 22, and the sum of the thicknesses of the first spacer 22 and the second spacer 23 is as described above. It is set similarly to the thickness of the spacer 19 in the first embodiment.
[0035]
(Embodiment 4)
FIGS. 8A to 8C show Embodiment 4 of the biosensor according to the present invention. 8A is a plan view of the measurement cell 13 of the biosensor 11 of the present embodiment, FIG. 8B is a YY cross-sectional view of FIG. 8A, and FIG. It is sectional drawing which shows the state cut | disconnected in the orthogonal | vertical direction with respect to the insertion direction of the measurement cell 13 which shows the state which inserted the cell 13. FIG. In addition, in this embodiment, the same code | symbol is attached | subjected to the same part as above-mentioned Embodiment 1, and description is abbreviate | omitted.
[0036]
In this embodiment, as shown in FIGS. 8B and 8C, two recesses 17B and 17C are formed in the lower substrate 17 of the measurement cell 13, and the sample reaction layer 18A is formed in each of the recesses 17B and 17C. , 18B are accommodated and arranged. Here, the sample reaction layer 18A includes glucose oxidase, peroxidase, and a color sample as in the first embodiment. The sample reaction layer 18B includes cholesterol oxidase, peroxidase, and a color sample. In addition, the other structure in the measurement cell 13 is the same as that of the said Embodiment 1. FIG. Thus, glucose and cholesterol can be measured simultaneously.
[0037]
Further, on the measurement device 12 side corresponding to the measurement cell 13 having the above-described configuration, the measurement cell 13 is inserted into the insertion gap 14 so as to face each other with the sample reaction layers 18A and 18B interposed therebetween. A pair of the light emitting element 15C and the light receiving element 16C and a pair of the light emitting element 15D and the light receiving element 16D are arranged and formed to be aligned. In addition, the other structure of the measuring apparatus 12 is the same as that of the measuring apparatus 12 of above-described Embodiment 1.
[0038]
The measurement procedure of the biosensor 11 having such a configuration will be described below. First, holding the grip portion 13 </ b> B of the measurement cell 13, the measurement cell 13 is inserted into the insertion gap 14 of the measurement device 12. In this state, light of a predetermined wavelength range is irradiated from each pair of light emitting elements 15C and 15D, and the amounts of light transmitted through the sample reaction layers 18A and 18B are measured by the respective light receiving elements 16C and 16D. . Next, the sample solution is dropped or attached from one sample solution introducing portion 13A of the measurement cell 13 to reach the respective sample reaction layers 18A and 18B by capillary action, and again emits light after a predetermined time has elapsed. Light is irradiated from the elements 15C and 15D, and the amounts of light transmitted through the sample reaction layers 18A and 18B are measured by the light receiving elements 16C and 16D. The absorbance is obtained from the light amount ratio before and after the introduction of the sample solution in the sample reaction layer 18A, and the glucose concentration is calculated. Further, the cholesterol concentration is calculated by obtaining the absorbance from the light amount ratio before and after introducing the sample solution in the sample reaction layer 18B.
[0039]
As described above, in this embodiment, since the two concave portions 17B and 17C are provided in the lower substrate 17 and the sample reaction layer is formed in the concave portions, even if the sample liquid penetrates into the measurement cell 13 due to capillary action. The reagent in the recess can be prevented from flowing into the sample flow of the sample liquid. Therefore, the reagents in the sample reaction layers 18A and 18B provided in the different recesses 17B and 17C do not mix with each other, and each measurement can be performed independently. In this embodiment, there is an advantage that a plurality of substrate concentrations can be measured simultaneously.
In the present embodiment, a light shielding film may be provided between the sample reaction layers 18A and 18B so that light colored by coloring does not interfere with each other.
In each of the above embodiments, the measurement cell 13 includes the lower substrate 17 and the upper substrate 18, but only the lower substrate may be used.
In each of the above embodiments, the sample liquid is introduced into the sample liquid introduction gap 21 after the measurement cell 13 is inserted into the insertion gap 14 of the measurement apparatus 12. However, after the sample liquid is introduced into the sample liquid introduction gap 21, the measurement is performed. The measurement cell 13 may be inserted into the insertion gap 14 of the device 12.
[0040]
【The invention's effect】
As is clear from the above description, according to the present invention, a transmissive biosensor can be obtained, so that the sample reaction layer is made of the emitted light radiated in a plurality of traveling directions of the light emitting portion. It can be arranged so that the amount of light traveling substantially perpendicular to the surface direction of the sample reaction layer is maximized, minimizing irregular reflection of light on the sample reaction layer and the substrate, and improving the light receiving efficiency. Can be improved. And since it can suppress that a light emission part and a light-receiving part are polluted with a sample liquid, there exists an effect that a highly accurate substrate concentration can be measured. In addition, since the light-emitting part and the light-receiving part can be placed as close as possible to the sample reaction layer, the optical path length can be shortened, and diffused light from the sample reaction layer can be received efficiently and high-performance concentration measurement. There is an effect that can be performed reliably. Furthermore, according to the present invention, it is possible to measure a plurality of types of substrate concentrations by a single measurement, and it is possible to realize a biosensor capable of performing an efficient measurement.
[Brief description of the drawings]
FIG. 1 is an explanatory cross-sectional view showing a biosensor according to a first embodiment of the present invention.
FIG. 2 is an explanatory plan view of the first embodiment.
3A is a plan view showing the measurement sensor of Embodiment 1, and FIG. 3B is a sectional view taken along line XX in FIG. 3A.
4 is a cross-sectional view showing a state where a measurement cell is inserted in the biosensor of Embodiment 1. FIG.
FIG. 5 is a sectional view showing Embodiment 2 of the biosensor according to the present invention.
FIG. 6 is a sectional view showing Embodiment 3 of the biosensor according to the present invention.
7A is a partially exploded perspective view of a measurement cell according to Embodiment 3, and FIG. 7B is a cross-sectional view of main parts of the measurement cell.
8A is a plan view of a measurement cell according to a fourth embodiment of the biosensor according to the present invention, FIG. 8B is a YY sectional view of FIG. 8A, and FIG. 8C is a diagram of the biosensor according to the fourth embodiment. Sectional drawing.
FIG. 9 is a side view of a conventional biosensor.
[Explanation of symbols]
DESCRIPTION OF SYMBOLS 11 Biosensor 12 Measuring apparatus 13 Measurement cell 13A Sample liquid introduction part 14 Insertion gap 15 Light emitting element 16 Light receiving element 17 Lower substrate 18 Sample reaction layer 19 Spacer 20 Upper substrate 21 Sample liquid introduction gap

Claims (5)

A measuring device in which a light emitting unit and a light receiving unit are arranged to face each other through a measurement space;
A measurement cell in which a sample reaction layer is disposed on a light-transmitting substrate and a sample liquid introduction part that can be inserted into the measurement space is formed;
Equipped with a,
The sample solution introduction part is provided with a sample solution introduction port in a width direction perpendicular to the insertion direction of the measurement cell, and the width of the sample solution introduction part is wider than the width of the measurement space of the measurement device. Features biosensor. Claims wherein the measuring cell includes a substrate above the sample reaction layer, between the substrate spacer is interposed, characterized in that the sample liquid along the sample liquid introduction port which the spacer is formed is introduced Item 10. The biosensor according to Item 1. The biosensor according to claim 2, wherein the sample solution inlet of the measurement cell is exposed from the measurement device in a state where the measurement cell is inserted into the measurement device.   In the measurement device, a plurality of pairs of the light emitting unit and the light receiving unit facing each other through the measurement space are arranged, and the measurement cell corresponds to the pair of the light emitting unit and the light receiving unit. The biosensor according to any one of claims 1 to 3, wherein a plurality of sample reaction layers are arranged at positions.   The circumference surrounding the measurement space of the measuring device has a property of reflecting light from a light emitting portion and light colored by color reaction caused by contact of a sample liquid with the sample reaction layer. The biosensor according to any one of claims 1 to 4.

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