JP2004245735A - Disposable sensor card for measuring blood component - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a disposable sensor card for measuring blood components capable of measuring at least two kinds of arbitrary components with one sensor without being limited by a difference in preprocessing. <P>SOLUTION: This disposable sensor card for measuring the blood components comprises a substrate having a measuring part with a reaction reagent to measured components to be measured in the blood and at least two sets of electrode systems with a terminal connectable to a separate measuring device. The sensor card also comprises two or more independent flow passages passing at least over the measured portions of the electrode systems and a blood lead-in holding part joined to the upstream ends of all flow passages. Suction openings are formed at the downstream ends of the flow passages. <P>COPYRIGHT: (C)2004,JPO&NCIPI

Description

[0001]
TECHNICAL FIELD OF THE INVENTION
The present invention relates to an improvement in a disposable sensor card used for measuring a specific component in blood.
[0002]
[Prior art]
Conventionally, various sensors have been proposed for quickly and simply quantifying a specific component in a biological sample solution such as blood.
Specifically, one space including a reaction layer reacting with a specific component to be measured is provided on a substrate, and an inlet for a sample liquid and an outlet for discharging gas in the space are provided in this space. A biosensor has been proposed (see Patent Document 1).
[0003]
[Patent Document 1] Japanese Patent Publication No. 06-58338
[Problems to be solved by the invention]
In the above-described conventional biosensor, when the sample liquid is brought into contact with the sample liquid inlet, the sample liquid is guided into the interior of the space by capillary action, and the sample liquid is discharged onto the electrode while discharging the air in the space from the outlet. Therefore, there is an effect that the electrode surface can be uniformly wetted with the sample solution without bubbles remaining on the electrode.
By the way, there are many types of components to be measured in blood, and pretreatment required before measurement differs for each component. Specifically, for example, when glucose is measured as in Patent Document 1, blood collected from a patient can be directly used for measurement, but when cholesterol and neutral fat are measured, blood It is necessary to remove blood cells from blood in advance in order for catalase contained in red blood cells to inhibit the measurement, and when measuring HDL, further remove non-HDL components in addition to blood cells. There is a need. Further, depending on the measurement component, there is also a component that requires use of serum obtained by further removing fibrinogen from plasma from which blood cells have been removed.
However, as described above, the conventional biosensor has only one sample liquid inlet and one space in which an electrode to be measured is arranged, and therefore cannot simultaneously measure components subjected to different pretreatments. For this reason, there is a problem that the measurement target items are significantly limited.
The present invention solves the above-mentioned conventional problems, and is not limited to a difference in pretreatment and the like, and is capable of measuring at least two types of arbitrary components with one sensor, and is a disposable component for measuring blood components. It is intended to provide a sensor card.
[0005]
[Means for Solving the Problems]
In order to achieve the above-mentioned object, the disposable sensor card for measuring blood components according to the present invention can be connected to a measurement unit provided with a reaction reagent for a measurement component to be measured in blood and a separate measurement device. A substrate having at least two sets of electrode systems having a plurality of terminals, at least two independent flow paths passing over at least a measurement site of each electrode system, and one of the flow paths connected to the upstream ends of all the flow paths. A blood introduction holding section, and a suction opening is provided at a downstream end of each of the flow paths.
A substance that inhibits blood aggregation, such as heparin, citric acid, oxalic acid, EDTA, or antithrombin III, may be preferably applied to the blood introduction holding unit. The blood coagulation inhibitor such as heparin can be applied by, for example, applying the blood coagulation inhibitor to the wall surface of the blood introduction holding unit before manufacturing the sensor.
Preferably, a sealing member having both properties of gas permeability and liquid impermeability may be provided at a position between the suction opening and the measurement site of the electrode in each flow path.
Further, if necessary, a blood cell separation filter can be provided between the measurement unit and the blood holding unit in at least one flow path. In this case, preferably, at least a portion of the flow path where the filter is disposed is configured to be perpendicular to the sensor plane, and the blood cell separation filter can be configured by sequentially stacking a glass fiber filter and a porous filter. . In this case, the glass fiber nonwoven fabric may previously hold a blood cell separation accelerator such as lectin.
Further, if necessary, a blood cell and non-HDL component removal filter may be provided between the measurement unit and the blood holding unit in at least one flow path. In this case, it is preferable that at least a portion of the flow path where the filter is disposed is configured to be perpendicular to the sensor plane, and the blood cell and non-HDL component removal filter are made of a glass fiber nonwoven fabric holding a non-HDL precipitant and a porous material. It can be configured by sequentially laminating filters.
[0006]
BEST MODE FOR CARRYING OUT THE INVENTION
Hereinafter, an embodiment of a disposable sensor card for measuring blood components (hereinafter, simply referred to as a sensor card) according to the present invention will be described with reference to an embodiment shown in the accompanying drawings.
[0007]
FIG. 1 is an exploded perspective view of one embodiment of a sensor card according to the present invention.
This sensor card is configured to measure cholesterol, neutral fat and HDL in blood.
As shown in the drawing, this sensor card
Eight films 1 to 8 forming a flow path of the sample liquid;
Three filters 9-11,
It comprises a single substrate 12 on which electrodes and terminals are formed.
[0008]
The uppermost film 1 is a polyethylene terephthalate film (hereinafter, PET film) having a thickness of 0.125 mm.
The second film 2 is made of a single-sided pressure-sensitive adhesive tape having a thickness of 0.15 mm and having an adhesive surface on an upper surface, and a notch 2a for forming a blood introduction holding portion A at one end thereof, and a film 3 described later. And two independent openings 2b and 2c communicating with the notches 3a.
The third film 3 is made of a double-sided pressure-sensitive adhesive tape having a thickness of 0.3 mm having an adhesive surface on both sides, and a notch for forming a blood introduction holding portion together with the notch 2a of the film 2 at one end thereof. 3a are formed. The notch 3a is notched widely inside the notch 2a of the film 2 so as to communicate with openings 2b and 2c of the film 2 and openings 4a and 4b of the film 4 described later.
The fourth film 4 is made of a PET film having a thickness of 0.125 mm, and has an opening 4a forming the first flow path and an opening 4b forming the second flow path.
The fifth film 5 is made of a double-sided adhesive tape having a thickness of 0.725 mm and having adhesive surfaces on both sides, and has an opening 5a communicating with the opening 4a of the film 4 at one end thereof. An opening 5b communicating with the opening 4b is formed.
[0009]
A glass fiber nonwoven fabric 9 is fitted into the opening 5a. The glass fiber non-woven fabric 9 has the same thickness as the film 5, has a pore diameter of 1 to 10 μm, and has a cross-sectional shape formed to have the same shape and the same size as the opening 5a. Functions as a progress delay filter. In addition, the glass fiber nonwoven fabric 9 previously holds a lectin as a blood cell separation promoting agent in a dry state, and the reaction with the lectin increases the effect of delaying the progress speed of blood cells.
Similarly, the glass fiber nonwoven fabric 10 is fitted into the opening 5b. This glass fiber nonwoven fabric 10 has the same thickness as the film 5, has a hole diameter of 1 to 10 μm, and is formed to have the same cross-sectional shape as the opening 5b. In addition, the glass fiber nonwoven fabric 10 has a non-HDL precipitant dried and held in advance, so that the glass fiber nonwoven fabric 10 can delay the progression of blood cells, and can also be used to delay non-HDL components. Functions as an HDL component removal filter.
A porous polyester membrane 11 is provided between the film 5 (that is, the two independent filters 9 and 10 described above) and a film 6 described below. The porous polyester membrane 11 is provided with a large number of pores extending in the vertical direction (that is, the flow direction of the flow path) and having a pore diameter in the range of 0.5 to 4 μm. And functions as a blood cell removal filter that traps blood cells that pass through the plasma.
[0010]
The sixth film 6 is made of a double-sided pressure-sensitive adhesive tape having a thickness of 0.06 mm and having adhesive surfaces on both sides, and has, at one end thereof, the glass fiber nonwoven fabrics 9 and 10 fitted in the openings 5a and 5b. Independent openings 6a and 6b communicating with the openings 4a and 4b of the film 4, respectively, are formed via the and the porous polystyrene membrane 11.
The seventh film 7 is made of a PET film having a thickness of 0.125 mm, and has independent openings 7a and 7b communicating with the openings 6a and 6b of the film 6, respectively.
The eighth film 8 is made of a 0.1 mm thick double-sided pressure-sensitive adhesive tape having adhesive surfaces on both sides.
In this film 8,
One end communicates with the opening 7a, passes through the upper surface of a first measuring section B of the substrate 12 described later, and extends along the longitudinal direction of the film to a suction opening D formed in the substrate 12; ,
One end communicates with the opening 7b, passes through the upper surface of a second measuring section C of the substrate 12 described later, and extends along the longitudinal direction of the film to a suction opening E formed in the substrate 12; Are respectively formed.
The elongated openings 8a and 8b are formed such that portions corresponding to the measurement portions B and C of the substrate 12 described later are formed wide, and after narrowing from the wide portion to the downstream, a suction opening D of the substrate 12 described later. And E are formed so as to be wider again.
A narrow flow path portion between the wide portion corresponding to the measuring portion B and the wide portion corresponding to the suction opening C in the elongated opening 8a has a seal having both gas-permeable and liquid-impermeable properties. A member 13a is provided.
Similarly, the narrow flow path portion between the wide portion corresponding to the measurement portion C and the wide portion corresponding to the suction opening E in the elongated opening 8b has both properties of gas permeability and liquid impermeability. A sealing member 13b is provided.
As the sealing members 13a and 13b, for example, those formed using fibers made of a water-absorbing polymer or fibers made of a hydrophobic polymer are used. Specifically, the sealing members 13a and 13b can be formed by, for example, coating an appropriate core material with the fibers. When the water-absorbing polymer is used, when the blood comes into contact, the water-absorbing polymer absorbs the blood and swells, and does not pass through the blood any more. When the hydrophobic polymer is used, the blood does not pass through due to surface tension.
As the water-absorbing polymer, for example, a polysaccharide and / or a derivative thereof, an acrylic polymer, polyvinyl alcohol, gelatin, a block copolymer containing collagen or maleic anhydride, or the like can be used.
As the hydrophobic polymer, for example, polyester, silicone, fluororesin, polyethylene, or the like can be used.
[0011]
Lastly, the substrate 12 will be described with reference to FIGS.
FIG. 2 is an enlarged view of the substrate 12 in FIG.
The substrate 12 is made of a polyester film, and has a first measuring section B and a second measuring section C formed thereon.
The first measurement unit B includes a pair of electrodes B1 and B2 for measuring cholesterol, a pair of electrodes B3 and B4 for measuring neutral fat, and a counter electrode B5.
The second measuring section C includes a pair of electrodes C1 and C2 for HDL measurement and a counter electrode C3.
A cholesterol measuring reagent, cholesterol esterase, cholesterol oxidase, and an electron acceptor are held on the measurement site of one electrode B1 of the pair of electrodes B1 and B2 for measuring cholesterol by drop drying, and the other electrode Cholesterol esterase and an electron acceptor are held on the measurement site of B2.
A lipase, a glycerol kinase, a glycerophosphate oxidase, and an electron acceptor are held as a neutral fat measurement reagent on a measurement site of one electrode B3 of the pair of electrodes B3 and B4 for the neutral fat measurement. On the measurement site of the other electrode B4, glycerol kinase, glycerophosphate oxidase, and an electron acceptor are held.
On the measurement site of one electrode C1 of the pair of electrodes C1 and C2 for HDL measurement, cholesterol esterase, cholesterol oxidase, and an electron acceptor are held by drop drying for HDL measurement, and the other is held. Cholesterol esterase and an electron acceptor are held on the measurement site of the electrode C2.
As described above, a pair of electrodes is provided for each measurement item, one reagent holds all reagents necessary for measurement, and the other electrode removes one reagent from all reagents required for measurement. By holding the sample, the cholesterol, neutral fat, and HDL components can be measured from the difference between the reaction values obtained at both electrodes by the measuring device.
As for the HDL component, the non-HDL component is removed by the glass fiber nonwoven fabric 10 in advance, and the blood cells are removed in advance by the combination of the glass fiber nonwoven fabric 10 and the porous polyester membrane 111. It is possible to measure components.
Each of the above-mentioned electrodes is formed by bonding a copper foil on a substrate and then forming a desired pattern by a photolithography method.
Gold or platinum plating is applied to the surface of the measurement site of the measurement electrodes B1, B2, B3, B4, C1, and C2. On the counter electrodes B5 and C3, a conductive layer made of a conductive paste containing silver powder and silver chloride powder is further formed on the pattern by screen printing.
Also, an insulating resist made of a UV-curable polyester resin was formed on the electrode by photolithography so that only the measurement site and the terminal site were exposed. In the present example, the diameter of the exposed portion of each measurement site could be reduced to 0.6φ by using the photolithography method for forming the insulating resist. As described above, by reducing the exposed portion of the measurement site, the amount of blood required for measurement can be greatly reduced, and the effect of reducing the burden on the patient can be achieved.
[0012]
The films 1 to 8 and the three filters 9 to 11 are all laminated on the substrate 12.
As described above, the films 2, 3, 5, 6, and 8 sandwiched between the films or between the film and the substrate are simply made of single-sided tape or double-sided tape, so that they are simply aligned and stacked. Each film is liquid-tightly and air-tightly adhered to the substrate only by stacking, so that the sensor card can be easily manufactured.
When all the films 1 to 8 and the filters 9 to 11 are laminated on the substrate 12, the blood introduction holding portion A is formed by the notch 2a of the film 1, the notch 2, the notch 3a of the film 3, and the film 4. A substance that inhibits blood coagulation, such as heparin, is previously applied to a portion of the film 1 and the film 4 corresponding to the blood introduction holding section A, so that the blood introduction holding section A has a certain amount of time. It is possible to keep blood.
When all the films 1 to 8 and the filters 9 to 11 are laminated on the substrate 12, the openings 4a, the glass fiber nonwoven fabric 9 fitted in the openings 5a, the porous polyester membrane 11, the openings 6a, the openings 7a, All of the elongated opening 8a and the suction opening D communicate with each other to form the first flow path F. The upstream end of the first flow path F communicates with the blood introduction holding section A, passes through the upper surface of the first measurement section B formed on the substrate 12, and reaches the suction opening D.
At the same time, the opening 4b, the glass fiber nonwoven fabric 10, the porous polyester membrane 11, the opening 6b, the opening 7b, the elongated opening 8b, and the suction opening E which are fitted in the opening 5b all communicate with each other, and the second flow path G Is formed. The upstream end of the second flow path G communicates with the blood introduction holding section A, passes through the upper surface of the second measurement section C formed on the substrate 12, and reaches the suction opening E.
The first flow path F and the second flow path G are, as shown in FIG. 1, the substrate 12 from the blood introduction holding section A to the first measurement section B and the second measurement section C on the same plane. Perpendicular to the substrate 12, from which it is horizontal with respect to the substrate 12, and further opened vertically to the substrate 12 via suction openings D and E. Then, the glass fiber nonwoven fabrics 9 and 10 and the porous polyester membrane 11 functioning as filters are all arranged in the portions of the flow paths F and G perpendicular to the substrate.
[0013]
Hereinafter, a usage example of the sensor card configured as described above will be briefly described.
This sensor card is set in a measuring device having an input section to which a terminal can be connected, and a pump configured to be able to independently suction the test liquid in the two flow paths via the two suction openings. Used as
After setting the sensor card in the measuring device, the user introduces blood into the blood introduction holding part A, one of which is open to the outside.
The blood immediately after the introduction is held by the blood introduction holding unit A without flowing to the first flow path F and the second flow path G due to surface tension.
Here, first, the blood in the blood introduction holding section A flows through the second flow path G against the surface tension, and flows through the suction opening E on the second flow path G side until it contacts the filter 10. Through the pump. When blood comes into contact, the filter 10 absorbs the blood itself until it fills its capacity.
Next, the blood in the blood introduction holding section A flows into the first flow path F against the surface tension, and is sucked by the pump through the suction opening D on the first flow path F side until it contacts the filter 9. . When the blood comes in contact, the filter 9 absorbs the blood by itself until it fills the capacity.
In this state, the apparatus waits until the blood cell separation promoting agent and the blood in the filter 9 sufficiently react with each other, and after a sufficient reaction time has elapsed, the blood in the filter 9 again passes through the filters 6 through the openings 6a, 7a, and 8a. It flows in order and is sucked by the pump through the suction opening D on the first flow path F side until it reaches the sealing member 13a of the opening 8a through the first measuring portion B of the substrate 12.
Thereby, only the plasma from which the blood cells have been removed by the action of the filter 11 is filled in the first flow path F from the downstream of the filter 11 to the sealing member 13a. At this time, in addition to the blood cell progression delaying action of the filter 9 and the reaction with the blood cell separation promoting agent, the blood cell progression in the filter 9 is sufficiently delayed with respect to the plasma. The filter 11 does not get clogged with blood cells before reaching the sealing member 13a above the first measuring section B.
Next, after a sufficient reaction time between the non-HDL precipitant and the blood has passed, the blood in the filter 10 flows again through the filter 11 in the order of the openings 6b, 7b, and 8b, and flows on the second measuring section C of the substrate 12 again. The liquid is sucked by the pump of the measuring device through the suction opening E on the second flow path G side until the gas reaches the sealing member 13b of the opening 8b.
As a result, the filter 10 removes the non-HDL component, the filter 11 removes the blood cells, and only the blood plasma from which the blood cells and the non-HDL component have been removed is sealed from the downstream of the filter 11 in the second flow path G by the sealing member 13b. Will be charged until
As described above, in this sensor card, the plasma to be measured (or the plasma from which non-HDL components have been removed) is filled over the first measuring unit B and the second measuring unit C to the sealing members 13a and 13b. The configuration is such that a constant amount of plasma can be guided onto the electrodes without worrying about overshoot, regardless of the wetting of the electrode surface of each electrode, so that the measurement is very stable.
[0014]
As described above, the sensor card according to the present embodiment exemplifies application of heparin as a blood coagulation inhibitor to the blood introduction holding unit in advance, but the blood coagulation inhibitor is not limited to this embodiment. Any substance can be used as long as it can inhibit blood aggregation, such as citric acid, oxalic acid, EDTA, and antithrombin II.
In the above-described embodiment, the sensor card having two flow paths F and G connected to one blood introduction holding unit is described as an example. However, the number of flow paths is not limited to this embodiment. Any number may be used as long as the number is two or more.
Further, in the above-described embodiment, the blood cell removal filters 9 and 11 are provided in one of the flow paths, and the blood cell and non-HDL component removal filters 10 and 11 are provided in the other flow path. The present invention is not limited to this example, and can be arbitrarily determined according to the component to be measured. Specifically, for example, a filter for removing non-LDL components or a filter for removing LDL is provided when measuring LDL cholesterol, and a filter for removing a specific isozyme when measuring enzyme isozymes. Alternatively, a filter for removing enzymes other than a specific isozyme may be provided.
Further, in the above-described embodiment, the configuration is such that HDL is measured by removing non-HDL components. However, this is not limited to the present embodiment. , A channel having a filter capable of removing the HDL component may be provided, cholesterol may be measured in both channels, and the HDL component may be measured based on the difference between the two.
Further, for the LDL component, similarly, for example, a flow path without a filter and a flow path with a filter capable of removing the LDL component are provided, and the LDL component is determined based on the difference between the measured values in both flow paths. It may be configured to measure.
Further, the filter is not limited to these examples, and can be widely used when a specific substance can be measured by removing a certain component in a sample.
[0015]
【The invention's effect】
As described above, the disposable sensor card for measuring a blood component according to the present invention includes a measurement unit provided with a reaction reagent for a measurement component to be measured in blood, and a terminal connectable to a separate measurement device. A substrate having at least two sets of electrode systems each having at least two independent flow paths passing at least over the measurement site of each electrode system, and one blood introduction holding device connected to the upstream ends of all flow paths And a suction opening is provided at the downstream end of each of the flow paths, so that, if necessary, simply providing a filter required for pretreatment in a necessary flow path, simply, A plurality of types of components having different pretreatments can be measured from blood.
According to the second aspect of the present invention, since a substance that inhibits aggregation of blood is provided to the blood introduction holding section, blood introduction is performed for adjustment of a pretreatment time that differs depending on the component to be measured. Even if blood is held in the holding unit for a certain period of time, blood does not aggregate.
According to the invention of claim 3, in the above-mentioned disposable sensor card for measuring blood components, gas permeability and liquid impermeability are provided at a position between the suction opening in each channel and the measurement site of the electrode. Since a sealing member having both of the above properties is provided, a necessary amount of blood can be supplied onto the measurement site of the electrode without fine adjustment of the suction amount.
Further, according to the invention of claim 4, in the above-mentioned disposable sensor card for measuring blood components, since the blood cell separation filter is provided between the measurement unit and the blood holding unit in at least one flow path, the blood cells are separated. , Such as cholesterol and neutral fat, and other components can be measured simultaneously.
According to the invention of claim 5, at least a portion of the flow path where the filter is disposed is perpendicular to a sensor plane, and the blood cell separation filter is configured by sequentially laminating a glass fiber nonwoven fabric and a porous filter. Therefore, the distance occupied by the blood cell separation filter portion in the flow path can be shortened, and since the blood passes through the porous filter after sufficiently delaying the progress of blood cells with a glass fiber nonwoven fabric, a necessary amount of blood is reduced. The porous filter does not become clogged with blood cells before plasma is obtained.
Further, according to the invention of claim 6, since the blood cell separation promoting agent is held in the glass fiber nonwoven fabric, the action of delaying blood cell progress in the glass fiber filter can be further amplified.
According to the invention of claim 7, since the blood cell and non-HDL component removal filter is provided between the measurement unit and the blood holding unit in at least one flow path, the HDL component and the other components are removed. Can be measured simultaneously.
Further, according to the invention of claim 8, at least a portion of the flow path where the filter is arranged is perpendicular to a sensor plane, and the blood cell and non-HDL component removing filter is a glass fiber nonwoven fabric holding a non-HDL precipitant. And the porous filter are sequentially laminated, so that non-HDL components can be trapped in the glass fiber non-woven fabric, and blood cells are clogged in the porous filter due to the blood cell progression delay action in the glass fiber non-woven fabric. Nothing.
[Brief description of the drawings]
FIG. 1 is a developed perspective view of one embodiment of a sensor card according to the present invention.
FIG. 2 is an enlarged view of a substrate in FIG.
[Description of References]
A blood introduction holding section B first measurement section B1 cholesterol measurement electrode B2 cholesterol measurement electrode B3 triglyceride measurement electrode B4 triglyceride measurement electrode B5 counter electrode C second measurement section C1 HDL measurement electrode C2 HDL measurement Electrode C3 Counter electrode D Suction opening E Suction opening F First channel G Second channel 1 Film (PET film)
2 Film (single-sided tape)
2a notch 2b opening 2c opening 3 film (double-sided tape)
3a Notch 4 film (PET film)
4a Opening 4b Opening 5 Film (double-sided tape)
5a Opening 5b Opening 6 Film (double-sided tape)
6a Opening 6b Opening 7 Film (PET film)
7a opening 7b opening 8 film (double-sided tape)
8a Elongated opening 8b Elongated opening 9 Glass fiber nonwoven fabric (holds blood cell separation promoter lectin)
10 Glass fiber nonwoven fabric (holds non-HDL precipitant)
DESCRIPTION OF SYMBOLS 11 Porous polyester membrane 12 Substrate 13a Sealing member 13b Sealing member

Claims (12)

A measurement unit provided with a reaction reagent for a measurement component to be measured in blood, and a substrate provided with at least two sets of electrode systems each having a terminal connectable to a separate measurement device,
At least two or more independent flow paths passing over the measurement site of each electrode system,
Having one blood introduction holding unit connected to the upstream ends of all the flow paths,
A disposable sensor card for measuring blood components, wherein a suction opening is provided at a downstream end of each of the flow paths. The disposable sensor card for measuring blood components according to claim 1, wherein a substance that inhibits aggregation of blood is provided to the blood introduction holding unit. 3. A sealing member having both gas permeability and liquid impermeability is provided at a position between a suction opening and a measurement site of an electrode in each flow path. The disposable sensor card for measuring blood components according to 1. The disposable sensor card for measuring blood components according to any one of claims 1 to 3, wherein a blood cell separation filter is provided between the measurement unit and the blood holding unit in at least one flow path. At least a portion of the flow path where the filter is arranged is perpendicular to the sensor plane,
The disposable sensor card for measuring blood components according to claim 4, wherein the blood cell separation filter is formed by sequentially laminating a glass fiber nonwoven fabric and a porous filter. The disposable sensor card for measuring blood components according to claim 5, wherein a blood cell separation promoting agent is held in the glass fiber nonwoven fabric. The blood component measurement use according to any one of claims 1 to 6, wherein a blood cell and non-HDL component removal filter is provided between the measurement unit and the blood holding unit in at least one flow path. Discard sensor card. At least a portion of the flow path where the filter is arranged is perpendicular to the sensor plane,
The disposable sensor card for blood component measurement according to claim 7, wherein the blood cell and non-HDL component removal filter is formed by sequentially laminating a glass fiber nonwoven fabric holding a non-HDL precipitant and a porous filter. . The blood component measurement use according to any one of claims 1 to 6, wherein a blood cell and non-LDL component removal filter is provided between the measurement unit and the blood holding unit in at least one flow path. Discard sensor card. At least a portion of the flow path where the filter is arranged is perpendicular to the sensor plane,
8. The disposable sensor card for measuring blood components according to claim 7, wherein the blood cell and non-LDL component removing filter is formed by sequentially laminating a glass fiber nonwoven fabric holding a non-LDL precipitant and a porous filter. . A flow path without a filter,
The disposable sensor card for blood component measurement according to any one of claims 1 to 10, further comprising a flow path provided with an HDL component removal filter between the measurement unit and the blood holding unit. A flow path without a filter,
The disposable sensor card for blood component measurement according to any one of claims 1 to 10, further comprising a flow path provided with an LDL component removal filter between the measurement unit and the blood holding unit.

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