JPH0989888A - Analyzing element conforming to whole blood - Google Patents

Abstract

PROBLEM TO BE SOLVED: To accurately determine the amount of an analyte in the whole blood without being influenced by a value of hematocrit, by layering a separation layer, a polymer layer, a reagent layer and a supporting body in this order, thereby constituting an analysis element. SOLUTION: A polymer layer of water-absorptive polymer absorbing blood plasma or its diluted solution and swelling, and reagent layer of a reagent reacting with an analyte in blood and optically changing are layered sequentially on a separation layer, which is press-fitted onto a supporting body. The whole blood spotted on the separation layer is separated to blood corpuscles and blood plasma, while the unnecessary corpuscles remain on the separation layer and in the separation layer. The blood plasma reaches the polymer layer. The polymer layer absorbs the blood plasma and consequently swells, so that the blood plasma is forcibly absorbed from the whole blood at a constant speed. In other words, the sample solution is filtered at the separation layer forcibly, and then held temporarily at the polymer layer to be supplied into the reagent layer at the constant speed. Therefore, the amount of the blood plasma reaching the reagent layer is not influenced by a value of hematocrit.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a whole blood-compatible analytical element used in the field of clinical examination, and more specifically, it relates to a dry whole blood-compatible analytical element that is less susceptible to the hematocrit value in whole blood. It is provided.

[0002]

2. Description of the Related Art In the field of clinical examination, reagents are used in a method for quantitatively analyzing biochemically active components (hereinafter, also referred to as "analyte") such as glucose and bilirubin in body fluids such as blood. A system using a so-called "dry analytical element" using a test piece / test paper provided in a dry state is already known.

The advantage of the dry analytical element is that it does not use a reagent solution, so that it can be measured at any place and the measurement can be carried out quickly. However, many of these dry analytical elements have drawbacks such as error in the measurement result when whole blood is used for measurement. The cause of the error is that the blood cell components present in whole blood have various effects. Therefore, after removing blood cell components from whole blood in advance by a method such as centrifugation to obtain plasma, measurement and quantitative analysis of the analyte are performed by a dry analytical element using the plasma.

However, these methods such as centrifugation require a great deal of labor and time. Therefore, when whole blood is applied to an analytical element, the blood cell component is removed from the whole blood at the same time as spotting on the analytical element and plasma is applied. There have been invented a large number of dry blood analytical elements capable of separating whole blood (hereinafter, these may be referred to as "whole blood compatible dry test pieces").

As a method for separating plasma from whole blood in a dry test strip for whole blood, a glass filter, filter paper, membrane filter, gel or the like is installed as a filter layer for filtering blood cells and filtration is performed. Method, method for removing blood cell component using blood coagulant, blood cell adsorbent (for example, JP-A-60-36961)
No.), a method of using an optical wavelength that is not affected by blood cells for measurement, and so on.

[0006]

However, in the dry test strip for whole blood using the above-mentioned separation method, the influence of the blood cell component itself (for example, the substance inside the blood cell is eluted and the value of the analyte increases or decreases). However, it is affected by the concentration of blood cell components, so-called hematocrit value, and as a result, an error occurs in the measured value of the analyte.

When the hematocrit value is high, a large amount of blood cell components are present. Due to the decrease in the fluidity due to this, the capillary action in the filter layer for filtration is delayed, or the blood cell components are used for filtration. This is because the layers are clogged. The greater the excess of whole blood sample, the greater the tendency.

As a prior art aiming at a whole blood analysis element that is not affected by the hematocrit value, Japanese Patent Application Laid-Open No. 1-2394
Analytical elements described in Japanese Patent Publication No. 56 are mentioned. This analytical element has a reagent layer that is water-permeable and a porous developability, and when a liquid sample is spotted on the porous developable layer, the liquid sample shows a constant amount per unit area due to the metering action of the developable layer. It spreads at a rate and reacts with the reagents in the reagent layer below it. In this analytical element, a water absorbing layer made of a hydrophilic polymer or the like is provided below the reagent layer, so that the dye produced as a result of the above reaction does not substantially diffuse.

The present invention provides a whole blood analysis element having a novel structure which utilizes a principle completely different from those of the conventional separation methods, is less susceptible to the hematocrit value in whole blood, and has a high measurement accuracy. Is.

[0010]

In the present invention, in order to make it less susceptible to the hematocrit value, the whole blood correspondence analysis element has the following structure.

That is, according to the present invention, a separation layer for separating a blood cell component and a plasma component contained in whole blood, a polymer layer containing a water-absorbing polymer as a main constituent, and a reaction target component in blood are obtained. A whole blood-compatible analytical element for analyzing the above-mentioned components to be measured, in which a reagent layer containing a reagent that causes an optical change and a support are laminated in this order.

As one aspect of the whole blood-compatible analysis element, there is provided a whole blood-compatible analysis element in which the reagent layer and the polymer layer are integrated. The present invention also provides
Provided is a whole blood-compatible analytical element in which a spreading layer is further laminated on the separation layer.

Examples of the hydrophilic polymer include nonionic swelling agents. Examples of the nonionic swelling agent include polymers having a structure represented by the following general formula (1).

[0014]

Embedded image R ₁ -[(-O-CH ₂ -CH _2- ) _n -R ₂ -(-CH ₂ -CH ₂ -O-) _m ] _l -R ₃ (1) (wherein , R ₁ and R ₃ have ₁ to 22 carbon atoms, preferably 6 to 1
8 represents a group selected from an alkyl group, an alkylphenyl group and hydrogen, R ₁ and R ₃ may be the same or different, and R ₂ is a phenyl group, an oxyphenoxy group or a carbon atom. Number 3 to 22, preferably 10 to 1
8 represents a group selected from an oxyphenoxy group, an oxyalkylphenoxy group and an oxyalkoxy group, and the sum of m and n is 100 to 200, preferably 120.
Is about 185, and l is 10 to 50, preferably about 20 to
40. )

As the polymer having the structure represented by the general formula (1), specifically, R ₁ and R ₃ are hydrogen, and R is
Examples thereof include polymers in which ₂ is an oxyphenoxy group.
Furthermore, the present invention provides an analytical element in which the support is made of a light transmissive material or has a through hole for optical detection.

The whole blood corresponding analysis element of the present invention is a dry test piece which can correspond to whole blood containing blood cell components, and according to the present invention, the amount of the analyte in whole blood even when whole blood is used as a sample. Can be accurately quantified without being affected by the hematocrit value in whole blood.

[0017]

BEST MODE FOR CARRYING OUT THE INVENTION The whole blood-compatible analytical element of the present invention (hereinafter, also simply referred to as "analytical element") has a structure in which a separation layer, a polymer layer, a reagent layer and a support are laminated in this order.

When the whole blood or its diluted solution is spotted on the surface of the separation layer, the blood cell component and the plasma component contained in the whole blood are separated, and the plasma component is allowed to pass through to be guided to the polymer layer. It is for. The material of the separation layer is not particularly limited as long as the blood cell component remains inside and the plasma component can pass through, but, for example, a membrane filter, a glass filter, a filter paper, or the like used in the conventional separation layer. Is mentioned.

The polymer layer contains a water-absorbing polymer as a main constituent. The water-absorbent polymer is not particularly limited as long as it absorbs blood plasma or a diluted solution thereof and swells, but "a liquid sample is forcibly and at a constant rate absorbed to a reagent layer in contact with the polymer layer". It is preferable that the liquid sample can be supplied at a constant rate. The present inventors have found that by using such a polymer, the polymer layer swells by absorbing the plasma component, and then even if an excess sample is applied in order to absorb the plasma component at a constant absorption rate, It was found that the amount of the sample supplied to the reagent layer was constant.

Specific examples of the water-absorbing polymer include polyacrylic acid type polymers, starch-acrylate graft polymer type, vinyl acetate copolymer type, maleic anhydride copolymer type, polyvinyl alcohol type and ethylene oxide type polymers. Can be mentioned. Although any of these can be used in the present invention, more preferred are nonionic water-absorbing polymers, and more specifically, polymers containing an ethylene oxide chain (referred to as "ethylene oxide polymer"). Some of these are commercially available as water-absorbing agents and are easily available. As such a commercially available water-absorbing agent, for example, a thermoplastic nonionic hydrophilic resin “Aqua Coke” (trademark of Sumitomo Seika Chemicals Co., Ltd.) produced by crosslinking thermoplastic polyethylene oxide can be mentioned. When such a nonionic water-absorbing polymer is used, the electrostatic attraction between the groups in the polymer is less likely to change due to pH, the degree of swelling of the polymer becomes constant, and the plasma absorption rate does not change.

The general structural formula of the ethylene oxide polymer is as shown in the above general formula (1). As with this formula, the polymer can take various forms. For example, in the formula, R ₁ is an alkylphenyl group such as an octylphenyl group or a nonylphenyl group, R ₂ is an oxy group, R ₃ is hydrogen, the sum of m and n is 2 to 70, and 1 is 1
Are referred to as polyoxyethylene alkylphenyl ethers. This is commercially available as a surfactant, and in the analysis element described in JP-A-1-239456 mentioned above, a liquid product in which the sum of m and n is 25 or less, m
A solid product whose sum of n and n is 40 is used.

R ₁ is an alkyl group such as dodecyl group, hexadecyl group, octadecyl group, 2-ethylhexyl group, R ₂ is an oxy group, R ₃ is hydrogen,
The one in which the sum of m and n is 2 to 70 and l is 1 is called polyoxyethylene alkyl ether and is commercially available as a surfactant.

Further, those in which R ₁ and R ₃ are hydrogen, R ₂ is an oxy group, the sum of m and n is 2 to 70, and l is 1 or more are called polyethylene glycols. It is commercially available as a surfactant.

The present invention is represented by the above general formula (1).
Of the various forms of polymer, the surfactants above
Is an ethylene oxide that is crosslinked between molecules to form a polymer.
Side polymers are preferred. More specifically, the same formula smell
And R₁And R_ThreeIs hydrogen and R ₂Is a phenyl group, oxy
Phenoxy group having 3 to 22 carbon atoms, preferably 10 to 18 carbon atoms
A group selected from any of the oxyphenoxy groups of
The sum of m and n is 100 to 200, preferably 120 to
185, 1 is 10 to 50, preferably about 20 to 40
Polymers are particularly suitable. In addition, the hydrophobic balun
Considering the space, R₂Is preferably a phenyl group, oxy
A phenoxy group or an oxyalkylphenoxy group,
More preferably, in consideration of easiness of manufacturing at the time of manufacturing, oxyphene
A nonoxy group. Where R₂Is an oxyalkoxy group
In some cases, it is preferred that the carbon number is 1 or 3 or more.
Yes. This is because when the carbon number is 2,
It has the same structure as polyethylene glycol, which is a sex agent,
Hydrophobicity is weakened, and gel is less likely to occur,
Often deviates from the intention of the present invention. Also, R₂But
When it is a xyalkoxy group, the raw material is easily available industrially.
Therefore, the carbon number is preferably 22 or less.

The polymer preferably used in the present invention has the ethylene oxide chain cross-linked through the hydrophobic R ₂ as shown above. Further, a plurality of polymers are crosslinked by the intermolecular force between the R ₂ groups or between the ethylene oxide chains. Therefore, since such a polymer has a hydrophilic ethylene oxide chain, it is highly water-absorbing but insoluble in water, and exhibits a gel state in the presence of water. The swelling ratio of the water-absorbent polymer used in the present invention (the volume in the dry state and the volume ratio when absorbing the liquid) is 1.1 times or more and 300 times or less, preferably 2 times or more and 100 times or less, It is preferably 2 times or more and 50 times or less.

The thickness of the polymer layer varies depending on the type of polymer used and the swelling ratio, but it is usually preferably 1 to 200 μm in order to effectively exhibit its function. A powder of titanium oxide or the like may be added to the polymer layer in order to enhance the reflection efficiency of the polymer layer when the reflected light is measured from the support side. In addition, in order to increase the permeability of plasma,
A surfactant may be added.

The reagent layer is a reagent for measuring an analyte and contains a reagent which causes an optical change by reacting with an analyte in blood, and the analyte is detected by the optical change of this reagent. It will be possible. Examples of the reagent used include glucose oxidase, peroxidase, 4-aminoantipyrine, and N-methyl-N- (2-hydroxy-3-sulfopropyl) -3 when the analyte is glucose. When the analyte of 5,5-dimethylaniline is cholesterol, cholesterol oxidase, peroxidase, 4-aminoantipyrine, N-methyl-N- (2-hydroxy-3-sulfopropyl) -3, 5-dimethylaniline, when the analyte is lactic acid, lactate dehydrogenase, NAD ⁺ , diaphorase, tetrazolium violet, and when the analyte is alkaline phosphatase, p-
Nitrophenyl phosphate is used respectively.

The reagent layer may be prepared into a layer by a known method. For example, a water-soluble binder such as polyvinyl alcohol, polyacrylic acid, sodium alginate, or polyacrylamide, or a natural or synthetic polymer such as pullulan, a cellulose derivative, metrose, or gelatin is used to react with the analyte. After mixing the reagent and water to increase the viscosity, casting is performed in layers on the support and dried to form a reagent layer.

In one embodiment of the analytical element of the present invention, the reagent layer is provided as a layer different from the polymer layer,
In another embodiment, the polymer layer and the reagent layer may be integrated, that is, a polymer layer containing a water-absorbing polymer and a reagent. Since the polymer used in the present invention is colorless and light transmissive, the color change can be easily read from the support side. Further, there is an advantage that the labor for providing the reagent layer separately can be avoided. Even in this case, the liquid sample is supplied to the reagent at a constant rate, and accurate measurement is possible.

The support is for supporting the analytical element, but can be omitted as long as it has the required physical strength only in the separation layer, the polymer layer and the reagent layer.
As the material for the support, synthetic resin film such as glass, polyester, cellulose ester, polymethylmethacrylate, etc. is used. However, since there are cases where changes in reagents cannot be read due to the accumulation of blood cells in the upper part of the polymer layer, measurement is generally performed from the support side. Therefore, it is desirable that the support is made of a light-transmissive material or has through holes for photometry. Further, when oxygen is required for the reaction of the reagent, it is desirable to cover the through holes of the support with a porous film and provide the reagent layer / polymer layer on the porous film.

The analytical element of the present invention is produced by laminating the above-mentioned separation layer, polymer layer, reagent layer and support in this order. A spreading layer may be further provided on the separation layer, that is, on the uppermost layer of the laminate. This spreads the spotted liquid in the left-right direction and is not directly related to the reaction. This is because it is prevented from being locally spotted on the whole blood separation layer and eventually causing some time lag in water absorption of the polymer layer.

The method for producing the analytical element of the present invention is not particularly limited, but, for example, a polymer solution, a reagent solution,
Alternatively, a method of coating a polymer liquid containing a reagent and press-bonding the polymer liquid onto a support so that the coated surface is in contact therewith is exemplified. At this time, in order to support the reagent layer or the polymer layer containing the reagent, a porous film or the like may be used to hold the reagent layer or the polymer layer. However, this porous film is not essential to the present invention.

Next, the usage of the analytical element of the present invention will be described. When spotted on the separation layer of the analytical element, first, the separation layer separates whole blood into blood cell components and plasma components. Excess blood cells accumulate on and in the whole blood separation layer, and plasma components reach the polymer layer.

By absorbing the liquid sample (here, the plasma component), the polymer layer swells to a greater extent than before the sample is spotted. At this time, the polymer layer absorbs the plasma component at a constant absorption rate. In order to do so, there is no problem if an excess of sample is applied. At this time, instead of relying solely on gravity and capillary action for the operation of blood cell separation in the separation layer, the polymer layer below the separation layer forces plasma components from whole blood due to its water absorption capacity. The amount of the plasma component reaching the reagent layer is not affected by the hematocrit value because it is absorbed at a constant rate. That is, by providing the polymer layer, the sample liquid is forcibly filtered by the separation layer, and the filtered sample liquid is once held in the polymer layer and supplied into the reagent layer at a constant rate.

Next, the reagent in the reagent layer below the polymer layer is dissolved by the water content of the plasma component, and the reagent for measuring the target substance and the analyte in the sample are mixed and reacted. At this time, since the liquid sample in the polymer layer is gradually supplied to the reagent layer by a constant amount due to the ability of the polymer layer, the reagent does not flow out to the excess sample or the excess sample, and reliable measurement is possible. it can.

Then, the amount of the analyte in the sample is measured by detecting the optical change of the reagent after the reaction from the side of the support.

[0037]

EXAMPLES The present invention will be described more specifically with reference to the following examples.

[0038]

Example 1 First, in order to show that the analytical element of the present invention is not affected by the hematocrit value, an analytical element having no reagent layer was prepared, and the hematocrit value and the absorption amount of the sample in the polymer layer were prepared. I investigated the relationship with. <1> Preparation of Analytical Element The following polymer layer liquid was applied onto a whole blood separation layer (membrane filter (pore size 0.45 μm), manufactured by Millipore) at a film thickness of 50 μm (wet state). Then 1 at 50 ℃
It was blow-dried for 5 minutes, and after drying, cut into a tape having a width of 7 mm. 35 x 50 mm coated with hot melt
Light-transmitting polyethylene terephthalate (thickness 0.5m
The tape piece was placed on one end of a support made of m) so that the polymer side faced the support, and thermocompression bonded. Finally, the support was cut in a width of 7 mm perpendicular to the longitudinal direction of the tape to obtain 5 analytical elements.

[Polymer Layer Liquid] The above components are mixed in methanol and stirred.・ Aqua Coke (Sumitomo Seika Co., Ltd.) ^*) 5% (weight ratio) ・ Triton X-100 (Wako Pure Chemical Industries, Ltd.) 0.1% (weight ratio) ・ TiO ₂ (Wako Pure Chemical ( 10% (weight ratio) *): In the general formula (1), R ₁ and R ₃ are hydrogen, R ₂ is an oxyphenoxy group, m + n = about 180, and l = about 27.5.

<2> Evaluation of Analytical Elements (1) Preparation of Whole Blood Sample Blue blood dye No. 1 (manufactured by Tokyo Chemical Industry Co., Ltd.) was applied to whole blood of healthy individuals.
Was added at a concentration of 1 mg / ml. After the addition, whole blood was centrifuged and separated into a blood cell component and a plasma component, and the hematocrit value was adjusted to about 30 to 60%. The hematocrit value was assayed by the centrifugation method.

(2) Measurement of Water Absorption Rate The water absorption of the polymer layer was measured by using a colorimeter (Σ90, manufactured by Nippon Denshoku Industries Co., Ltd.) to detect and measure a blue dye. An excess amount of 20 μl of whole blood was spotted on the upper part of the analytical element, and the reflectance at 640 nm was measured from the lower portion (support side). From the obtained reflectance, a simple Kubelka-Munk type The K / S value was determined according to the formula.
FIG. 1 is a graph in which the horizontal axis represents time and the vertical axis represents K / S value.

[0042]

## EQU1 ## K / S value = (1-R) ² / 2R R: reflectance (%)

Next, the difference between the 55th second and the 185th second of the K / S value obtained previously is set as the ΔK / S value.
The absorption rate of the polymer layer was observed. FIG. 2 is a graph in which the horizontal axis represents the hematocrit value and the vertical axis represents the ΔK / S value.

As shown in FIG. 1, the higher the hematocrit value in the range of 35% to 54%, the longer the measurement, but this is because there is some time difference in the whole blood separation layer. However, as is clear from FIG. 2, it can be seen that the hematocrit value did not affect the absorption rate per unit time of the polymer layer.

From this result, it is understood that the polymer layer absorbs the liquid sample at a constant rate and can supply a preferable amount of plasma from the whole blood to react with the reagent in the reagent layer.

[0046]

Example 2 Next, the influence of the hematocrit value on the measured value was investigated using an analytical element that actually contained a reagent. <1> Preparation of analysis element The following reagent-containing polymer layer liquid was used as a whole blood separation layer (membrane filter (pore size 0.65 μm), manufactured by Millipore).
It was coated on top with a film thickness of 50 μm. On the coated surface of this membrane filter, a light-transmitting porous film (thickness 1
50 μm, manufactured by Millipore) was placed thereon, dried by blowing at 50 ° C. for 15 minutes, and then cut into a tape having a width of 7 mm.

A support made of light-transmissive polyethylene terephthalate (thickness: 0.5 mm) of 35 × 50 mm, having through holes each having a diameter of 4 mm and having 5 rows at 3 mm intervals at one end and being coated with hot melt. The tape pieces were stacked on top of each other so that the porous film side faced the support and covered the row of through holes, and thermocompression bonded.

Finally, the support was cut in a width of 7 mm perpendicularly to the row of through holes for each through hole to obtain five analytical elements. The porous film is a support for holding the reagent-containing polymer layer in a state of straddling the through holes, and is not essential to the present invention. The total amount of the reagent solution in 8 g of the polymer solution (reagent-containing polymer layer solution) was mixed and stirred to obtain a reagent-containing polymer layer solution.

Polymer Liquid-Aqua Coke (Sumitomo Seika Co., Ltd.) 6.25% (weight ratio) -Triton X-100 (Wako Pure Chemical Industries, Ltd.) 0.25% (weight ratio) -TiO ₂ (Wako Pure Chemical Industries, Ltd.) 12.5% (weight ratio) The above components are mixed in methanol and stirred.

Reagent liquid: glucose oxidase (manufactured by Toyobo Co., Ltd.) 10 KU, peroxidase (manufactured by Toyobo Co., Ltd.) 20 KU, 4-aminoantipyrine (manufactured by Kishida Chemical Co., Ltd.) 150 mg, N-methyl-N- (2-Hydroxy-3-sulfopropyl) -3,5-dimethylaniline (manufactured by Wako Pure Chemical Industries, Ltd.) 200 mg 0.15M phosphate buffer (pH 7.0) (manufactured by Nacalai Tesque, Inc.) 2 ml Mix and dissolve the ingredients.

<2> Evaluation of analytical elements (1) Preparation of whole blood sample Sodium fluoride (manufactured by Nacalai Tesque, Inc.) was added to whole blood of a healthy person at 1 mg / ml for the purpose of inhibiting glycolysis. Was added. Then, the whole blood was centrifuged to separate it into a blood cell component and a plasma component, and then adjusted to each hematocrit value. The hematocrit value was assayed by the centrifugation method. Each blood glucose level test uses plasma as a blood glucose measuring device GA-112.
It was confirmed that the blood glucose levels were almost the same by performing a test with 0 (manufactured by Kyoto Daiichi Kagaku Co., Ltd.).

(2) Measurement of blood glucose level Whole blood was spotted on the upper part of the analytical element in an excess amount of 20 μl, and a colorimeter (Σ90, manufactured by Nippon Denshoku Industries Co., Ltd.) was applied from the lower part (support side). The reflectance at 640 nm was measured by using it, and the K / S value was obtained from the obtained reflectance. The difference between the calculated K / S value at 115 seconds and the value at 125 seconds was taken as the ΔK / S value.

The hematocrit value is plotted on the horizontal axis and Δ is plotted on the vertical axis.
A graph of K / S values is shown in FIG. As shown in FIG. 3, there was no difference in the amount of color development per unit time regardless of the hematocrit value in the range of 28 to 62%. From this result, it can be seen that the hematocrit value was not affected.

[0054]

EFFECTS OF THE INVENTION By using the analysis element of the present invention, an analyte can be accurately measured without being affected by the hematocrit value even when whole blood is used as a sample. Further, even if an excessive amount of whole blood sample is spotted on the analytical element, the analyte can be accurately measured.

[Brief description of drawings]

FIG. 1 is a graph showing the relationship between time and K / S value when whole blood was spotted on an analysis element according to the present invention.

FIG. 2 shows the K / S value obtained in FIG.
It is a graph at the time of comparing with the hematocrit value, where the difference between the values at the 5th second is ΔK / S value.

FIG. 3 shows a K / S value of 115 which is actually obtained by using a reagent.
It is a graph at the time of comparing with a hematocrit value by making the difference between the value at the second second and the value at the 125th second the ΔK / S value.

Claims (7)

[Claims] 1. A separation layer for separating a blood cell component and a plasma component contained in whole blood, a polymer layer containing a water-absorbing polymer as a main constituent component, and an optical change by reacting with a measurement target component in blood. A whole blood-compatible analytical element for analyzing the component to be measured, comprising a support and a reagent layer containing a reagent that causes the above-mentioned reaction, which are laminated in this order. 2. The whole blood-compatible analytical element according to claim 1, wherein the reagent layer and the polymer layer are integrated. 3. The whole blood correspondence analysis element according to claim 1, wherein a development layer is further laminated on the separation layer. 4. The whole blood-compatible analytical element according to claim 1, wherein the hydrophilic polymer is a nonionic swelling agent. 5. The nonionic swelling agent is represented by the following general formula (1):
The whole blood corresponding analytical element according to claim 4, which is a polymer having a structure represented by: Embedded image R ₁ -[(-O-CH ₂ -CH _2- ) _n -R ₂ -(-CH ₂ -CH ₂ -O-) _m ] _l -R ₃ (1) (wherein , R ₁ and R ₃ represent a group selected from an alkyl group having 1 to 22 carbon atoms, an alkylphenyl group, and hydrogen, and R ₁ and R ₃ may be the same or different, R ₂ represents a group selected from a phenyl group, an oxyphenoxy group, an oxyalkylphenoxy group having 3 to 22 carbon atoms, and an oxyalkoxy group, the sum of m and n is 100 to 200, and l is 10 ~ 50.) 6. R ₁ and R ₃ are hydrogen and R ₂ has 1 carbon atom.
Or the analytical element for whole blood according to claim 5, which is an oxyalkoxy group of 3 to 22. 7. The support according to claim 1, wherein the support is made of a light transmissive material, or has a through hole for optical detection.
The whole blood corresponding analysis element according to any one of 1.