JP2006068384A - Body fluid transfer implement, and body fluid inspecting system using the same - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To stably measure the concentration of a blood component by effectively and easily sampling a small amount of blood from a living body, facilitating mounting on a blood inspecting apparatus, and eliminating a measurement error caused by unavoidable nonuniformity which is generated in mass-production. <P>SOLUTION: A body fluid transfer implement comprises an impregnation part for being impregnated with a body fluid by contact, which seeps onto a skin surface; and a support part for supporting the impregnation part. The impregnation part has a shape to be stored in a body fluid inspecting part. A blood bioinstrumentation for optically performing measurement, while rotating a disk, includes a standard tub for storing standard substance on a measurement circumference, so as to measure the nonuniformity of the light path length by measuring the absorbance of the previously inserted standard substance, and to correct optical information such as a dimension error. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to a body fluid transfer device and a body fluid inspection system using the body fluid transfer device.

The concentration measurement of body fluid components represented by blood has been performed for a long time, and the accuracy has also been improved by increasing the functionality of analyzers.
Such a blood test apparatus is a so-called business use, and a system in which a qualified person such as a doctor or a nurse collects about several tens of milliliters of necessary and sufficient blood using a blood collection tube is generally used.
On the other hand, patients who are worried about changes in blood glucose levels over time, such as diabetes, have their blood exposed to the skin surface using a blood collection device that they can use at home, and then impregnate them with a test piece. Techniques have been used.
It is desirable that the amount of blood collected be smaller in order to reduce the burden on the patient and use at home.

Japanese Patent Application Laid-Open No. 11-318871 shows a configuration for holding the expressed blood fraction while quantifying it.
Japanese Patent Application Laid-Open No. 11-318887 is suitable for a measuring device that does not have a quantification unit. However, since it is configured to be held by capillary force, only a small amount can be used, and in order to maintain by capillary force, erroneous contact is not possible. If there is, the capillary force may collapse and disperse.
By the way, the test paper type, such as dry chemistry, seems to be able to impregnate the porous material by assigning the blood expression part to the supply part made of the porous material. Therefore, it is necessary to supply a fixed amount of blood using a pipette for dispensing.
On the other hand, there has been proposed a small and portable device that performs multi-component blood component concentration measurement by quantifying, moving, and manipulating body fluid on the flow path using capillary force and centrifugal force. This is a disk-shaped device that injects blood into the center, then separates and distributes blood cells by centrifugal force, supplies quantitative blood to the reagent reaction tank, optically measures the color reaction, and displays the component concentration However, the transfer of blood from the specimen must use a pipette.

Japanese Patent Laid-Open No. 11-174048 JP-A-11-318871 JP 2004-101381 A JP-A-5-72210 JP 9-504732 A Japanese National Patent Publication No. 3-510484 JP-A-5-508709 Japanese Patent Publication No. 50-23624 Japanese translation of PCT publication No. 2003-520582

  There is no device to transfer to the blood test device while holding a sufficient amount of body fluid necessary for measurement even though it is a small amount, and even to transfer tens to hundreds of micro fluids so that they can be tested with the blood test device There is no suitable configuration yet.

Optical body fluid component measurement in a blood test apparatus usually uses an absorbance measurement method, and supplies body fluid components such as serum to a columnar reaction tank having a liquid or solid reagent therein, and a reagent. And reacting for a predetermined time, irradiate a light beam such as laser light from the side or up and down direction, measure the amount of light attenuation from the reflected light or transmitted light, and separately measure the material showing a known absorbance Calibration and measurement are performed by comparison with the obtained calibration curve.
Therefore, it is necessary to cope with a darker reaction color, depending on the nature of the reagent or sample, when reducing the blood volume and making the whole thinner and smaller, and at least shorten the optical path length of the reaction tank. In order to detect more light obtained from the sample and improve the accuracy with respect to high concentration value detection using a calibration curve, it is necessary to make the substrate including the reaction vessel thinner and smaller.
In such a case, if the reaction vessel is made thinner and smaller, errors such as invisible burrs and material modification that have not been a problem until now in the production of the base material will affect the measurement light.
For example, assuming that the optical path length is 2 mm, an error of 100 microns generated in a member forming the optical path length alone reduces the accuracy by 5%.
Furthermore, if the optical path length is 1 mm, the structural error alone becomes 10%, and accurate component analysis becomes difficult.

As described above, with regard to an invasive device that collects and analyzes blood by damaging the living body, it is preferable to minimize the amount of blood used so as not to burden the human body as much as possible. Even in a blood analysis rotor using force, it is preferable to analyze blood using a smaller space.
Making the rotor smaller also means reducing the volume of the reagent reaction tank that mixes body fluids and reagents to cause a color reaction. At that time, the area of the part irradiated with measurement light and irradiated to the outside is reduced. Smaller may be a better adjustment than other reductions.
Reducing the upper and lower areas of the reagent reaction tank, on the other hand, narrows the irradiation range of measurement light such as lasers. Therefore, even if the irradiation area is reduced by narrowing the laser light with a lens, uneven rotation of the rotor, etc. In some cases, the deviation between the reaction tank and the optical path that comes from is greatly reflected as a measurement error.

By the way, among the multi-component component inspection items of blood components, there are items that must be measured spectrophotometrically as a result of reacting with at least two types of reagents such as DHLC, unlike other reagent reaction steps. .
Such a configuration in which a microfluid is moved and a reagent reaction is performed a plurality of times and a configuration for enabling measurement of a smaller amount of blood components has not yet been disclosed.

When mass-producing inspection units that form flow paths, reaction tanks, separation tanks, etc. on a substrate, it is possible to provide a unit that guarantees stable reaction operation by creating a precisely adjusted mold. However, depending on the situation, there is often a need to minimize the volume of blood handled by the unit.
This situation is consistent with the need to keep blood with minimal blood draw so as not to cause more pain for the patient.
For example, for the blood analysis unit provided to allow 15 kinds of test reactions when the required blood volume is 45 μl, there are cases where 5 test items are necessary depending on the test situation, but even in that case, the blood volume needs to be 45 μl. End up.
One of the reasons why the required amount of blood does not change is, for example, a blood cell separation tank (for example, 302 in FIG. 11) and a blood flow path of serum after centrifugation (for example, 302 in the centrifugal separation structure at the time of blood cell separation as shown in FIG. 305) must be fixed including the margin of the hematocrit value.
However, it is impossible to change the fixed relationship between the blood cell separation part and the flow path after mass production using a precise mold.
The above matters are a configuration for collecting more limited blood and measuring multi-item components of blood, and those that can be applied to home medical care become a greater problem.

In view of the above, the present invention comprises, in a blood transfer configuration, an impregnation portion that contacts and impregnates body fluid exposed on the skin surface and a support portion that supports the impregnation portion, and the impregnation portion is accommodated in the body fluid inspection portion. It is possible to easily transfer a small amount of blood collected from a patient by using a blood transfer device having a possible shape.
The impregnation part in the present invention may be, for example, a non-woven fabric, sponge, porous ceramic or the like that is porous so that at least serum can be easily separated and extracted during centrifugation while impregnating and holding a liquid. Moreover, the impregnation part should just be folded in the shape which can be mounted | worn in a test | inspection machine, and it is preferable to shape | mold in the shape in a test | inspection machine.
The support part is formed of a dense plastic or the like that is bonded or mechanically bonded to the impregnation part, and the shape thereof is easy to support and the impregnation part has a shape according to the specifications when being inserted into the inspection device. Well, at least when the blood impregnated in the impregnation part is transported, it is not particularly limited as long as it is in a state where it does not adhere to the person or device that transports the blood.
The present invention is an inspection device for processing a liquid through a flow path or the like, such as a configuration in which a body fluid such as blood is quantified and mixed with a reagent or the like to develop a color, and a device that is sufficient for a minute amount of blood. Realizes the effective transfer of a small amount of blood from a living body.

Furthermore, in the present invention, in the optical measurement, by placing one or more reference reaction tanks containing optical reference materials instead of reagents in the measurement trajectory, the concentration is obtained from the absorbance measurement of the reference material at the time of measurement. By detecting the optical path length fluctuation from the calibration curve deviation and compensating the concentration, it was possible to eliminate variations in specifications that occur during mass production of products.
In the present invention, when measuring a blood reaction item with a high concentration, it is necessary to shorten the optical path for the purpose of lowering the absorbance OD value or facilitating oxygen reaction by reducing the total blood volume. The calibration curve can be corrected by measuring the reaction tank.
In the present invention, one or more reference reaction tanks may be provided on one optical measurement trajectory. For example, the reference reaction tanks are on the trajectory adjacent to the reagent reaction tank at intervals of 90 degrees.
The optical reference material is, for example, a dye, a dye liquid, or a solid composite material, and preferably has a known concentration, and a substance used for preparing a calibration curve is preferably used.
When the calibration curve is corrected by the one-point method, an optical reference material having a known concentration component may be arranged on the optical path orbit at one location of the rotor. In the case of multiple points, the calibration curve is corrected at several locations on the rotor. An optical reference material (for example, concentration values indicated by c1 to c4 in FIG. 10 (d)) having different concentration values is arranged, and an error in the absorbance value obtained individually is obtained. Although calibration curve inclination correction is exemplified, the correction value may be determined in a predictive and linear function even when there are multiple points and the error is small.
The measurement of the reference reaction tank is an individual unit, and may be performed before measurement, sequentially during measurement, at the time of final measurement, or may be performed during production and converted into lot management data.

  Furthermore, the present invention is a unit for measuring blood components due to reagent reactions of a large number of items, and has a rotating body structure in which a large number of measurement reaction chambers are concentrically arranged, and is transmissive and optical while rotating the unit. In a blood test system equipped with optical measuring means for sequentially measuring, a dummy window is formed on the same circumference as the measurement reaction chamber and at a position perpendicular to the circumferential direction of the rotating body, and passes through the dummy window. The deviation of the light emission path of the illuminant is detected from the transmitted light amount to realize accurate speculative analysis.

The present invention further includes an input port for containing a reagent and inputting a sample therein and an output port for outputting a mixed sample solution of the reagent to the outside for component measurement requiring a plurality of reagent reactions from a minute amount of blood. A combination of the first reagent reaction tank, an input port for containing the reagent therein and inputting the mixed sample solution supplied from the first reagent reaction tank, and a second reagent reaction tank having a configuration that can be measured from the outside According to the configuration, it is possible to mix with a plurality of reagents only by adjusting the centrifugal force and the capillary force.
According to the said structure, combined use with another one time reagent reaction structure is also attained.

Furthermore, the present invention relates to a configuration that makes it possible to adjust the amount of body fluid to be used, a body fluid test in which a blood cell separation unit performs blood cell separation on a rotating body, reacts serum with a reagent, and measures a color reaction value. In the system, by providing a prosthesis that performs prosthesis to adjust the volume in the blood cell separation unit, the volume is adjusted, and the quantitative value is adjusted, the fluid operation timing is adjusted, and the like.

  In the present invention, by using a blood transfer device comprising a combination of an impregnation portion and a support portion, a small amount of blood is transferred to a testing device that can perform multi-component measurement by performing an operation process such as quantitative distribution and mixing. At this time, it is possible to provide a transfer device and a blood test system which are simple and less likely to scatter blood to the outside and which are inexpensive.

  When performing multi-component analysis using a small amount of blood, the present invention can sufficiently cope with the inevitable structural fluctuations and optical path length changes that occur during optical measurement and mass production in order to make the test unit thinner and smaller. The range is greatly expanded.

  The present invention makes it possible to obtain sufficient optical information for analysis even with a small amount of sample, and it is possible to measure an accurate value of the component concentration even in a reagent reaction region having a diameter of several hundreds of microns.

  In the present invention, the test item for reacting a plurality of types of reagents is easily performed by adjusting the centrifugal force and the capillary force, and the test item for reacting with one reagent can be easily used together. Enables many types of multi-item inspection.

The present invention provides a prosthesis for a blood cell separation chamber, a mixture dilution chamber, a blood storage chamber, etc. having a fixed volume on a unit by performing a prosthesis at a site where the volume can be adjusted while maintaining functionality. While having shape and size, it is possible to expand the field of application such as different component measurement.

Blood transfer configuration

As an example of the best mode for carrying out the present invention, a combination of an impregnation portion and a support portion for supporting the impregnation portion is shown, and the shape of the impregnation portion is at least a shape that can be accommodated in the inspection apparatus.
The impregnation part of the present invention has a shape and a structure that is accommodated in a part that injects blood from the outside of a unit that separates, quantifies, mixes, and moves blood cells by rotational force. It is preferable to have a porosity and shape that can be extracted. The impregnation of the impregnation part may be a liquid holding structure by capillary force generated in the gap, and is not limited to a porous material such as a brush.

Optical measurement

In the present invention, one or a plurality of reference reaction tanks may be provided on the optical measurement trajectory, and it may be preferably placed in a ratio of 1: 1 on a portion adjacent to the reagent reaction tank.
In this case, the possibility that the reference reaction tank has the thickness fluctuation of the adjacent reagent tank is sufficiently high.
For example, the absorbance of the reference reaction vessel is measured to obtain the absorbance ODS, and the concentration C1 is obtained based on the calibration curve drawn at the time of initial setting.
Since the concentration value Cs of the reference substance in the reference reaction tank is set in advance, the difference Cdef between Cs and C1 corresponds to the thickness of the lid and the thickness under the reaction tank.
Therefore, an accurate concentration can be obtained by correcting the concentration value obtained in the reagent reaction vessel around the reference reaction vessel by the concentration fluctuation Cdef.
In this way, if there are a large number of standard reaction tanks, accurate concentration can be obtained, but conversely, since a large area is required or the amount of calculation increases dramatically, every other or every other standard The reaction tank may be set, and the parameter for shake correction may be obtained 1 to repeatedly before and after the actual measurement.
In the present invention, the analysis unit may automatically move while drawing an optical measurement trajectory, or a shape that moves manually, or an optical element that automatically moves and measures, Further, a plurality of measurement probes may be provided to measure the reagent part and the reference part at the same time.

In the present invention, a plurality of reagent reaction vessels are mainly arranged on a common circular orbit on a rotating body, and a dummy window serving as a reference is arranged on the circular orbit. On the other hand, dummy windows are formed in the vertical direction, that is, in the diameter direction, and the light receiving elements on the measuring device side are respectively arranged at positions corresponding to the positions of these dummy windows, and an optical device composed of a combination of these light receiving element arrays and light emitting elements. The measuring body only needs to be slidable in the radial direction, and the light emission of the light emitting element is always caused by the reagent reaction by sliding the optical light emitting body with the balance of the intensity of light received by this optical measuring body. It suffices if it can be adjusted to irradiate the center of the part. Further, the irradiation area may be adjusted by moving the rotor driving unit and the rotor.
Any dummy window may be used as long as it has the same color and light attenuation rate as long as the optical intensity of the light emitter can be recognized as a dummy in optical measurement.

Measurement of components that require multiple reagent reactions from micro blood

The present invention is preferably used for a so-called rotor-type body fluid component testing apparatus, and it is preferable that a flow is controlled by a centrifugal force and a capillary force by forming a concave flow path on a rotor type, that is, a disk. On the rotor, a supply tank that supplies blood that is also formed in a concave shape, a blood cell separation unit that separates and removes blood cells from the blood, and a serum that is separated and extracted by the blood cell separation unit is quantified, and a quantitative serum A first reagent reaction tank that mixes the first reagent with each other and performs an intermediate reaction; and a solution reacted in the first reagent reaction tank is further reacted with a reagent to develop a color, and a component is measured by external measurement light It is preferable to be comprised with a 2 reagent reaction tank.
The sample supplied to the first reagent reaction tank may be preferably quantified, but may be configured to perform quantification at the time of centrifugation described in FIG. 12, for example.
The movement of the liquid between the first reagent reaction tank and the second reagent reaction tank uses, for example, centrifugal force due to rotation and capillary force, and coexists with another one reagent reaction configuration. A configuration is preferred.
For example, in the case of one reagent reaction configuration, a configuration in which a mixing step with a diluent is incorporated and a reaction with the first reagent is performed in the mixing step is exemplified.
In this case, in the case of a plurality of reagent reaction configurations, the dilution step is omitted. However, a configuration may be added in which a diluent is supplied into the reaction tank during the reaction with the first reagent.
Note that the reagent may be solidified and sealed in advance, or supplied from outside during the reaction.

Configuration that makes it possible to adjust the amount of body fluid used

The present invention at least includes a portion that stores blood and temporarily stores blood cells in a unit that uses power to move the substrate, such as a rotor, or a unit that uses capillary action, air pressure, etc. without moving the substrate. Using a prosthesis for changing the volume of the part to be separated, the part to be mixed with other substances such as diluent, etc., the amount of sample to be handled, the timing of sample movement, etc. may be adjusted. It is selected appropriately.
For example, in the case of a blood cell separation unit in which the timing of taking out the serum is determined by the degree of blood cell separation in the blood cell separation unit, there is a case where the blood cell storage unit is prosthetic and the amount of blood cells separated and accumulated is adjusted. is there.
Examples of the prosthesis include a prosthesis using a solid block made of the same material as the base material and having a size and shape for target adjustment, and encapsulating a curable resin.

FIG. 1 is a diagram showing an embodiment of the present invention.
01 is an impregnated member, which is formed of a nonwoven fabric, sponge, sponge, porous ceramics, porous plastic, paper, wood, etc., and its porosity is preferably 50% or more. It is adjusted as appropriate by the force to extract body fluid from the impregnated member.
The impregnation member 01 may be a single porous material or an aggregate of porous materials divided into a plurality of portions. In that case, it is sufficient that the impregnated blood is retained to the outside by centrifugal force, and various shapes can be taken within that range.
02 is a support member, which is formed of water-repellent plastic, glass, or other members.
The impregnation member 01 and the support member 02 are connected by an adhesive in addition to mechanical coupling.
Reference numeral 03 denotes a gripping part that is formed integrally with or separately from the support member 02 in order to facilitate phase shifting, such as when pinching with a finger to perform phase shifting. In some cases, the support member may not be used.

The handling operation of this embodiment will be described below with reference to FIGS.
In FIG. 2, the skin is injured using a skin injury device including a puncture device. Examples of the skin injury device provided with the puncture device include those described in JP-A-5-63506, but other configurations in which the lancet protrudes instantaneously are exemplified.
When damage S is formed on the skin H, blood B exudes from the inside. The impregnated member 01 is applied to the exuded blood B with the gripping part 03.
The impregnated member 01 stores the blood B in the blood storing unit 06 of the blood analysis rotor RO as shown in FIG.
When the impregnated member 01 is accommodated in the blood analysis rotor RO, the support member 02 is handled substantially integrally with the lid portion of the rotor RO.
The blood impregnated in the impregnation member 01 accommodated in the blood accommodating part 06 flows out to the outside by the rotation of the rotor RO.
The blood that has flowed to the outside travels through the flow path 07 and reaches the blood cell separation unit 08.
In the blood cell separation unit 08, blood and blood cells are separated by moving the blood cells having a high specific gravity in the outer circumferential direction by centrifugal force. After the separation is sufficiently performed, the serum is siphon tube 09 by reducing the rotation speed. To the distribution flow path 10. The serum that has moved to the distribution channel moves to the individual reagent reaction tanks and fills the quantitative flow paths of the individual reagent reaction tanks 11.
After filling, the rotation is strengthened and quantitative serum is supplied to the reagent reaction tank 11.
Reference numeral 12 denotes an example of a connection port with a device for rotationally driving the rotor RO.
As described above, while the structure is simple, it is possible to reliably perform the treatment of the exposed blood and to measure a number of blood components from a very small amount of blood.

Further, another embodiment of the present invention will be described in detail with reference to FIG.
In the embodiment shown in FIG. 4, a configuration in which the impregnation member 01 and the diluent storage unit 21 are provided on one support 22 is shown. The diluent storage unit 21 is configured by filling a thin plastic bag with physiological saline or the like, and is torn when pierced by a sharp needle or blade from the outside.
The plastic bag constituting the diluent storage unit 21 may be any material that can be torn when a sharp protrusion collides, and may be a material such as an aluminum pouch that keeps the quality of the diluent constant.
In FIG. 4, the gripping portion shown in FIG. 1 is not provided, but the support 22 is relatively larger than that in FIG.
FIG. 5 is a diagram for explaining a state where the present embodiment is actually placed on a rotor type blood test unit.
When a smaller amount of blood is used, it is diluted and used, but the portion where the skin has been pierced and the portion where blood has exuded is impregnated with the diluted solution storage portion 21 provided on the support 22. After placing the member 01 and impregnating with blood, the impregnation tool is set on the rotor RO as shown in FIG. At that time, the diluent storage unit 21 is also press-fitted and stored in the diluent storage unit 23.
At the time of press-fitting, the puncture tool 24 protruding from the bottom surface of the diluent storage part punctures and breaks the diluent storage part 21 and causes the diluent inside to flow out of the diluent storage part 21.
With such a configuration, it is possible to simplify the handling of the diluted solution, facilitate the storage of the diluted solution, and facilitate the work when discharging the diluted solution from the diluted solution storage unit 21.

An embodiment of the present invention will be described with reference to FIG.
FIG. 6 shows a configuration in which the impregnation member incorporates a puncture means that slides up and down.
Reference numeral 61 denotes an impregnating member, which is porous and is formed to hold blood in a detachable manner during centrifugation.
62 is a support member that opens upward and when the blood test apparatus is mounted and accommodates the impregnation member 61. The puncture member 63 is slidable up and down within a certain range at the lower center. For this purpose, a puncture member accommodating portion 621 having a protrusion on the inner periphery is formed integrally or detachably with another support member.
A plurality of stimulation pins 623 are planted in the support member 62, and the tip is preferably somewhat acute.
Reference numeral 63 denotes a puncture member, which has a blade-like shape and a needle-like shape on the outer peripheral side surface, each having a projection portion that can be engaged with a projection portion on the inner peripheral surface of the puncture member accommodating portion 621.
The puncture member 63 has a driving means that slides up and down and assists the sliding.
The driving means has a configuration in which the puncture member is pushed upward upward and moved downward.
Although not shown in the figure, the drive means is such as to transmit the deformation force of an elastic member such as a spring to the transmission member, and a combination in which the puncture means and the transmission member are in contact is exemplified.
Reference numeral 64 denotes vibration means for transmitting vibration generated by rotation of the vibration motor to the outside.
Reference numeral 65 denotes a placement portion for placing a puncture site. The open edge of the support member 62 accommodates the support member 62 so as to form a protruding portion 622 in a slightly protruding state. .

Next, the operation will be described.
As shown in FIG. 6A, a finger is placed so as to cover the protruding portion 622 that forms the contour of the placement portion 65. The puncture member 63 is hidden inside the impregnation member 61.
The vibration means 64 is vibrated to transmit the vibration to the support member 62, and the vibration generated in the upper protruding portion 622 and the plurality of stimulation pins 623 of the support member 62 is transmitted to the finger as a stimulus.
The driving means pushes the puncture member 63 upward vigorously (6S), and the puncture member 63 breaks through the impregnating member and collides with the fingertip YH, causing damage S (FIG. 6) (a)).
Thereafter, the driving means is driven to push down the puncture member 63 (6F) (FIG. 6B).
The blood exposed from the damage S is impregnated and held in the impregnation member 61 (GB) (FIG. 6C).
After the blood is sufficiently impregnated and held, the support member 62 is removed from the placement portion 65 (FIG. 6D) and attached to the blood test apparatus.

In the present embodiment, the configuration in which the impregnation member and the movable puncture means are combined is shown. However, the puncture means is fixed without sliding up and down, and the skin is raised and punctured using suction force. Such a configuration may be adopted.
Further, a combination of the puncture means and the impregnation member may be further combined with a blood test rotor unit. An example is shown in FIG.

FIG. 7A is a cross-sectional view of a rotary blood test unit having a puncture portion, and FIG. 7B is a perspective view thereof.
Reference numeral 71 denotes a rotor body, which is made of PP, polyacrylic material, or the like, and is formed of a member having a light-transmitting property as a whole.
Reference numeral 72 denotes a lid, which is made of PET, polyacryl, PP, or the like, and is joined to the rotor body 71 with an adhesive, a double-sided tape, or the like.
Reference numeral 73 denotes a connection opening surface, which is a portion for bringing the fingertip into contact with the impregnation member 74.
Reference numeral 74 denotes an impregnating member, which is formed of the above-described porous material such as a nonwoven fabric or a sponge. Reference numeral 75 denotes a puncturing means, which is formed in a needle shape or a blade shape, and has a configuration that can slide up and down.
The periphery of the puncture means has the configuration shown in FIG. 6 and has a configuration in which the puncture means is slid up and down in communication with the vertical drive of the external drive means.
Reference numeral 76 denotes a flow path, which is a passage through which blood impregnated in the impregnation member 74 flows out by the rotation of the rotor body 71 and moves the blood that has moved outward to the blood cell separation unit 77.
Reference numeral 77 denotes a blood cell separation unit, in which a housing part 771 for accommodating the separated blood cells in the circumferential direction is formed, and a continuous projection 772 is formed so that the separated blood cells do not return to the serum part 773 again.
Reference numeral 78 denotes a distribution flow path for connecting a plurality of reagent reaction vessels.
79 is a fixed flow channel, and the amount of reagent to be supplied to the reagent reaction tank 80 is determined by the length and the diameter of the flow channel.

Reference numeral 80 denotes a reagent reaction tank in which a freeze-dried reagent is accommodated. The reagent develops color due to different components.
Reference numerals 81 and 82 denote light guides, which are formed of a light-transmitting member so that measurement light from the outside can pass therethrough. If the entire rotor body and rotor lid are transparent, they may be unnecessary if they have translucency.
Reference numeral 83 denotes a shaft portion, which forms a connection portion with an external drive portion.
Reference numeral 84 denotes a bearing recess, which is configured on the measurement storage side and has a configuration in which a locked state is formed on the inner insertion surface when the shaft 83 is inserted.
Reference numeral 85 denotes a housing case that houses the rotor 70 and has a sliding open / close shutter 86 at the center. When the shutter 86 is opened, the rotor connection opening surface 73 appears, and the impregnation member 74 is exposed. The shutter 86 is always closed by an elastic member or the like, and when necessary, a shutter 86 is opened and fixed, and a separate instrument is provided to close after blood collection so that the impregnation member is not inadvertently touched. This is a preferable configuration.
In one part corresponding to the circumference of the reagent reaction tank provided on the rotor main body 71, holes 87 and 88 for optical connection with the outside are formed.

The operation of this embodiment will be described below.
The accommodation case 85 containing the rotor 70 is placed on the blood test apparatus in advance, and the puncture means 75 is in such a state that the driving force of the drive means on the apparatus side is transmitted.
The shutter 86 of the housing case 85 is open, and is stopped with the impregnating member 74 visible at that portion.
The finger YH is placed on the impregnation member 74 as shown in FIG. The drive unit on the device side is driven to push up the puncture means 75 upward. These states are the same as in the operation description shown in FIG.
After the blood is sufficiently impregnated in the impregnation member 74, the fingertip is released and the shutter 86 is closed.
The opening / closing operation of the shutter 86 may be automatically closed when the housing case is driven.
In addition, it may be unclear whether the blood exposed from the skin damaged part is sufficiently impregnated, but in that case, it is judged electrically by measuring whether the blood is sufficiently impregnated, its weight, content area, etc. May be.
Thereafter, the rotor 70 is rotated, the blood in the impregnating member 74 is pushed out in the circumferential direction, moved through the flow path 76, serum is separated and extracted by the blood cell separation section 77, and the distribution flow path 78 is used. The quantitative flow path 79 connected to each reagent reaction tank is filled.
After filling, the number of rotations is further increased, and the serum in the quantitative flow path is caused to flow into the reagent reaction tank 80 in an extruded form. The reagent reacts with the infused serum. In a colored state, laser light is transmitted from the outside (HH) through the hole 87 of the housing case, and color measurement is performed to obtain a component concentration.
The operation of the rotor 70 is an example, and various configurations are exemplified.
Such a combination of the blood analysis unit and the puncture means makes it possible to easily perform blood analysis even without taking charge of blood collection.

FIG. 8 (a) is an embodiment for measuring the multi-component component concentration value by separating and quantifying the central blood while rotating, distributing the quantified serum to each reagent tank and measuring the color development value. .
FIG. 8B is a schematic cross-sectional view taken along line X2-X2 ′ of FIG.
Reference numeral 80 denotes a rotor, which is formed by joining a transparent or translucent rotor main body 81 made of polyacryl, PP, PET, or the like and a lid portion 82.
FIG. 8A shows the rotor main body 81 to which the lid portion 82 is not attached.
In the rotor body 81, a blood reservoir R1, a blood cell separation tank R2, a distribution channel R3, and a quantitative channel R4 are formed as recesses, and reagent reaction vessels 84 and 86, reference reaction vessels 85, 87, 88, 89, 90 is also formed as a recess, and the lid 82 is adhesively bonded from above with a double-sided tape, an adhesive or the like. Reference numeral 83 denotes an optical measurement unit, which vertically holds a part of the rotor 80 in a non-contact manner.
The optical measuring unit 83 includes a light emitter 92 such as a laser and a light receiving unit 93. The optical measuring unit 83 irradiates light on the measurement light trajectory 91, and the light receiving unit 93 receives the light that has passed through the reaction vessel.
Reference numeral 94 denotes a reaction tank, and the inside is filled with a reagent and a sample or a reference substance and is in a full tank state. The reference substance in the reaction tank 94 does not necessarily need to be filled to the extent that there is no void, and it is sufficient that it is at least a reference for optical measurement.
Reference numeral 98 denotes a translucent part A, which is a part of the rotor body 81 and has translucency.
99 is a translucent part B, which is formed integrally with the lid part 82 and has translucency.
95 indicates the optical path length, 96 indicates the thickness of the light transmitting part B, and 97 indicates the thickness of the light transmitting part A.

The operation of this embodiment will be described.
In this embodiment, the rotor 80 rotates around the center point O, and blood (which may be impregnated blood) supplied to the central blood reservoir R1 is separated into blood cells via the flow path R6 by centrifugal force. Blood cell separation is performed by adjusting the rotational force that moves to the tank R2, and serum is extracted. The siphon flow path R5 supplies the serum to the distribution flow path R3 due to a decrease in the number of rotations of the rotor 80 and a change in the increase, and the serum supplied to the distribution flow path R3 is applied to each quantitative flow path R4 by capillary force. Filled.
Next, the rotation of the rotor 80 is increased, the centrifugal force is increased, and the serum is pushed into the reagent reaction tanks 84 and 86.
The serum develops a color reaction with the reagent in the reagent reaction tank, and the optical measuring unit 83 starts a measurement operation.
At that time, the optical measurement unit 83 measures the absorbance of the reference reaction tank 85 in advance or afterwards.
With the rotor 80 rotating at a predetermined speed or stopped, the light emission of the light emitter 92 reaches the light receiving portion 93 via the light transmitting portion A98, the reaction tank 94, and the light transmitting portion B99. Measure the absorbance at that time.
At this point, the calibration curve shown in FIGS. 8C and 8D has already been formed. FIG. 8C shows a calibration curve for a reagent to which the one-check calibration curve method can be applied, and FIG. 8D shows a calibration curve for a reagent to which the multi-check calibration curve method can be applied.

In FIG. 8C, since the concentration of the reference substance is known 8c, the absorbance Oda at that time is also known from the calibration curve 8a, and this is used as the reference value.
However, in the measurement of the individual reference materials on the actual rotor, the absorbance value ODad may deviate from the reference value Oda.
This deviation 8b is caused by uneven production of the thickness 96, 97 of the translucent part of the reaction tank. Therefore, the reagent reaction tank 84 in the vicinity of the deviation 8b can be accurately corrected by correcting with the same concentration deviation value. A concentration value is obtained.

The same applies to FIG. 8 (d), and the multi-inspection curve is a correction value based on the difference (8f) in the concentration value based on the absorbance difference ODbd−ODb for each unit in the reference reaction tank with respect to the calibration curve 8e. Optical measurement of the reagent reaction tank for each unit is performed.

As described above, it is possible to correct measurement values due to uneven production that is difficult to correct. It is also possible to obtain an accurate concentration value using the calibration curve data of the previous optical path length.

FIG. 9 is a diagram showing an embodiment of the present invention.
FIG. 9A is a perspective view of the present embodiment, and FIG. 9B is a cross-sectional view taken along x3-x3 ′.
A rotor 900 includes a lid 901 and a rotor main body 902. The rotor main body 902 is made of polypropylene, polyacryl, PET, or the like, and has a concave portion formed on the surface thereof. A blood reservoir R1, a blood cell separator R2, a distribution channel R3, a reagent reaction tank R4, a siphon channel R5, and the like are formed. ing. FIG. 9A shows a state in which the lid portion 901 is not attached, while FIG. 9B shows a schematic cross-sectional view in a state in which the lid portion 901 is attached.
Reference numeral 903 denotes an optical measurement unit, and FIG. 9B shows a cross-sectional view thereof.
Reference numeral 904 denotes a central dummy portion, which is a standard color substance, which can transmit light and give a predetermined absorbance to the received light.
Reference numeral 905 denotes an outer dummy portion, which has the same shape as the central dummy portion 904, is filled with the same substance, and is provided in the outer peripheral direction.
Reference numeral 906 denotes an inner dummy, which has the same shape as the central dummy 904, is filled with the same substance, and is provided in the inner circumferential direction. The respective dummies are adjacent to each other, but the dummy interval is appropriately adjusted in a range corresponding to the shake of the rotor at the time of optical measurement.
All of these dummy portions have the same cylindrical shape, but even if they have other shapes such as a rectangular shape, their positions may be on the measurement trajectory and pass through the center of the reagent reaction tank. .
The arrangement of the dummy windows is not necessarily limited to the arrangement 9A perpendicular to the circumferential direction, and may be arranged in a shifted state, such as 9B and 9C.
In the arrangement of 9B, the dummy windows 905 ′ and 906 ′ on both sides of the central dummy window 904 ′ are shifted by a predetermined angle. On the other hand, in the arrangement of 9C, the dummy windows 905 '' and 906 '' on both sides of the central dummy window 904 '' are shifted by a predetermined angle in the opposite direction to 9B.
Such a shifted arrangement makes it difficult to form a dead area between the dummy windows (for example, between FIGS. 10A and 9B) compared to the arrangement of 9A, and a more accurate light irradiation position of the light transmitting unit 916. Can be recognized.
In this embodiment, the three dummy window arrangement patterns 9A to 9C are shown. However, only various patterns are illustrated, and only one arrangement pattern among them is displayed at predetermined intervals. In some cases, it may be arranged in the same manner.
Reference numeral 907 denotes an inner light receiving unit that receives light transmitted through the inner dummy unit 906, performs photoelectric conversion, and sends the light to the processing unit 917.
Reference numeral 908 denotes a central light receiving unit that receives light transmitted through the central dummy unit 904 and the reagent reaction tank R7, photoelectrically converts it, and sends it to the processing unit 917.
Reference numeral 909 denotes an outer light receiving unit that receives light transmitted through the outer dummy unit 905, photoelectrically converts it, and sends it to the processing unit.

Reference numeral 910 denotes a lid inner translucent portion, which is disposed in the center direction of the rotor 900 and is formed of a translucent member. Reference numeral 911 denotes a lid central translucent part, which is formed of a translucent member, and 912 is a lid outer side translucent part, which is formed of a translucent member.
In any case, it is preferable to use a material that does not attenuate as much as possible with respect to the transmitted measurement light. If the lid 901 is formed of a translucent member, that material is sufficient.
Reference numeral 913 denotes a main body inner translucent portion, which is made of a material that does not attenuate the measurement light passing therethrough. Reference numeral 914 denotes a main body central light transmitting portion, and 915 denotes a main body outer light transmitting portion, which has the same material shape as the main body inner light transmitting portion 913. Any main body translucent portion is not particularly required as long as the rotor main body 902 has translucency.
Reference numeral 916 denotes a light transmission unit, which includes a laser light source and a condenser lens group. The light transmission unit 916 may include a plurality of laser light sources.
Reference numeral 917 denotes a processing unit having a central processing unit and a memory, obtaining an absorbance, an OD value, etc. with respect to input transmitted light, comparing and discriminating distributions of the three values, and a driving unit 918. To output a drive control signal.
A driving unit 918 includes a motor, a power transmission unit, an actuator, and the like, and has a servo mechanism for sliding the optical measurement unit 903.
Reference numeral 919 denotes an electrical lead wire for transmitting an electrical output for causing the light transmitting unit 916 to emit laser light.
920 is an electric lead wire for transmitting an electric signal from the light receiving unit to the processing unit.
Reference numeral 921 denotes an electric lead for electrically connecting the processing unit 917 and the driving unit 918.

Next, the operation of this embodiment will be described in detail with reference to FIG.
The driving in this embodiment is performed at the timing of actual sample measurement, and is controlled so that the received light amount OD at the center is the strongest as shown in FIG.
That is, in a stable state, when the rotor 900 rotates and optically measures the reagent reaction tank on the locus 922, the laser light output from the light transmitting unit 916 causes some scattering and attenuation. The central dummy 904 is irradiated with laser light through the main body central light transmitting portion 914.
The light that has passed through the central dummy 904 is received by the central light receiving unit 908 via the lid central translucent unit 911. The received light is photoelectrically converted and transmitted as an electrical signal to the processing unit 917 via the electrical lead 920.

The light transmitting unit 916 is located immediately below the central dummy 904, but a part of the light transmitting unit 916 passes through the main body inner light transmitting portion 913 and the main body outer light transmitting portion 915 due to light scattering or the like. The laser light passes through the outer dummy portion 905 and is received by the inner light receiving portion 907 via the lid inner light transmitting portion 910 and the outer light receiving portion 909 via the lid inner light transmitting portion 910, respectively.
As a result, as shown in FIG. 10A, when the horizontal axis is the position of the light receiving unit and the vertical axis is the intensity OD value of the received light, the peak 9b of the central dummy 904 is in the strongest state. appear.
The state shown in FIG. 10A is a reference state, 9a indicates the intensity of light that has passed through the inner dummy portion 906, 9b passes through the central dummy portion 904, and 9c passes through the outer dummy portion 905, respectively. This is the light intensity of the laser beam.

However, when the rotation of the rotor 900 is uneven and the center is deviated, the output laser of the light transmitting unit 916 is output to the outer dummy unit 905 in a tilted state, and to the outer dummy unit 905. As shown in FIG. 10B, the received light amount 9f of the outer light receiving unit 909 becomes larger than the received light amount 9c at the central light receiving unit 908 and the received light amount at the inner light receiving unit 907.
At this time, the processing unit 917 instructs the driving unit 918 to slide a predetermined amount outside the optical measuring unit 903, and the driving unit 918 slides the optical measuring unit 903 by a predetermined amount, and the next dummy area In the measurement, driving is performed so that the central peak as shown in FIG.

When the light receiving intensity 9g of the inner light receiving unit 907 becomes significantly larger than the light receiving amount 9h and the outer light receiving amount 9i of the central light receiving unit 908 due to uneven rotation of the rotor 900, as shown in FIG. The unit 917 gives a command to the drive unit 918 to cause the optical measurement unit 903 to be trained in the center direction, and controls the position of the optical measurement unit 903 so that the state shown in FIG. To do.
This adjustment enables optical measurement at the center of the reagent reaction tank. Stable color reaction can be measured.
An example of the amount of light received when the dummy windows are arranged 9B or 9C is indicated by broken lines 9J and 9K in FIG. Since there is no gap between the light receiving parts, the area where the light receiving parts 907 to 909 cannot receive light is reduced, and a more accurate light irradiation range can be obtained.

Next, an embodiment of the present invention will be described in detail with reference to FIG.
The embodiment shown in FIG. 11 is formed as a recess on a disk-shaped unit (rotor) RO, and rotates around a center point O with a sheet-like lid that covers the surface of the recess. It is preferable that the drive device for the rotation can change the rotation direction of the rotor or change the rotation speed.
Reference numeral 201 denotes an input flow path, which is formed from a preceding blood storage part or a centrifuge part that separates blood cells and serum.
Reference numeral 202 denotes a first reagent reaction tank in which a reagent S1 is enclosed. The reagent S1 is preferably a freeze-dried solid, but it may be a liquid reagent to be injected at the time of use.
203 is a 2nd flow path, Comprising: While forming the bending part bent in the center direction in the middle, it has a diameter which can exhibit capillary force.
Reference numeral 204 denotes a second reagent reaction tank, which has the same optical measurement trajectory as the reagent reaction tank OT that performs a color reaction with one other reagent, and the second reagent S2 is enclosed and fixed therein. ing. The second reagent S2 is exemplified by a solid or liquid form as in S1.
The volumes of the first reagent reaction tank 202 and the second reagent reaction tank 204 are set so as to have the same volume in this embodiment, but may be different. In this case, the first reagent reaction tank 202 When the volume of 202 is larger than the volume of the second reagent reaction tank 204, an overflow chamber for accommodating the overflow is provided at the connection boundary between the second reagent reaction tank 204 and the second flow path 203. Also good. The overflow chamber is, for example, 306 shown in FIG.

The operation of the embodiment shown in FIG. 11 will be described in detail with reference to FIG.
Serum, preferably quantitative serum, is supplied to the first reagent reaction tank 202 from the input channel 201 of FIG. Since the reagent S1 exists in the first reagent reaction tank 202, the quantitative serum is mixed with the reagent. At that time, by changing the rotation speed or changing the rotation direction, sufficient mixing is performed to form a mixed serum SM (FIG. 12A).
Next, when the rotation is stopped or weakened, the capillary force of the second channel 203 becomes stronger than the centrifugal force generated by the rotation, so that the mixed serum SM moves so as to be filled in the second channel 203. (FIG. 12B).
When the mixed serum SM exceeds the bent portion, when the rotational speed is increased again, the mixed serum SM flows into the second reagent reaction tank 204 and is filled by the siphon phenomenon.
After the mixed serum SM is filled in the second reagent reaction tank 204, the mixing speed is increased or the rotation direction is changed or the rotation direction is changed to promote mixing to form the final mixed serum SMM.
The color value of the final mixed serum SMM is read by optical measurement from the outside.
As described above, by adjusting the balance of the capillary force and the centrifugal force and adjusting the flow of the liquid in the two reagent reaction tanks, the reagent and the sample are easily mixed multiple times. By further connecting these, operations such as a reagent reaction, a fluorescent substance, and a magnetic substance binding three times or more can be performed.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.
In FIG. 13, a concave portion is formed in a disk-shaped base material such as polypropylene, PET, PP, etc., and these are used as a blood inlet, a flow path, a blood cell separator, and the like.
FIG. 13 omits the entire configuration, but for example, the entire configuration shown in FIGS. 7 and 12 is referred to.
The base material surface on which the recesses are formed is covered with a sheet made of the same material to form a unit.
In FIG. 13A, reference numeral 301 denotes an input flow path, which is connected to a blood injection part formed in the vicinity of the central part O.
Reference numeral 302 denotes a separated serum section, and the volume between the overflow chamber 306 and the connection port of the output flow path 305 determines the amount of serum that moves to the next processing section.
Reference numeral 303 denotes a blood cell storage part, which is formed by a recess deeper than the separated serum part.
Depending on the height of the separation wall 304, there may be a case where the separation wall 304 is not deep.
Reference numeral 304 denotes a separation wall, which is set at such a height that the separated blood cells do not return to the separated serum part.
In this embodiment, blood cells having a large specific gravity are performed by utilizing the property of moving in the outer circumferential direction when rotating the rotor, so that blood cells are separated even without a separation wall. At this time, the blood cell container 303 may be deeper or zigzag shaped so that the blood cells do not return.
Reference numeral 305 denotes an output flow path, which forms a bent portion in the direction of the center point O at any flow diameter utilizing the capillary phenomenon, so that the fluid generated by the centrifugal force generated by the rotational force and the capillary force of the flow path Adjust the movement.
Reference numeral 306 denotes an overflow chamber, which is a storage section when excess blood overflows from the separated serum section.
The overflow chamber 306 is connected in the direction of the center point O of the separated serum part 302.
Reference numeral 307 denotes a distribution flow path, one of which is connected to the output flow path 305 and a side surface of the distribution flow path 307, to which the fixed flow paths 308a to 308d are connected at predetermined intervals in the outer circumferential direction. To do. The fixed flow channels 308a to 308d are connected to the reagent reaction vessels 309a to 309d, respectively, and a fixed flow channel is added to connect the distribution flow channel 307 and the reagent reaction vessels according to the number of reagent reaction vessels. The
Reference numeral 310 denotes a prosthetic part, which is formed of the same material as the base material and may be only a hollow and strong frame, and may be any shape that can be attached when necessary. The connection is exemplified by the use of an adhesive, but depending on the shape, it may be simply fitted. Since the rotor in the present embodiment is generally used once, it does not need to be detached. However, in some cases, the rotor may be configured to be removable by adjusting the fitting configuration.

Reference numeral 311 denotes a stopper, which is a water-insoluble substance for blocking the flow path.
The stopper 311 uses an ink jet type discharge tool in which the discharge site is accurately positioned, and discharges a water-insoluble and curable solution onto the target flow path surface by the ink jet method. A method of blocking the flow path is preferably used.
The ink jet method is a method that suffices if the ink of a commercially available ink jet printer is changed to a curing material, and is a preferable method when the embodiment of the present invention is formed.

Next, the operation of this embodiment will be described.
First, the rotor rotates around the center point O, and blood collected through the input flow path 301 is supplied to the separated serum part 302 and the blood cell storage part 303.
A large amount of blood is supplied from the input flow path 301, and the blood fills up to the opening surface of the overflow chamber 306. If the blood continues to increase, the blood flows into the overflow chamber 306 as much as possible.
The number of rotations is increased / decreased so that blood cells are accommodated in the blood cell accommodating portion 303 beyond the separation wall 304. After almost all blood cells are stored in the blood cell storage unit 303, the rotation speed is decreased. By the capillary force of the output flow path 305, the serum exceeds the bent portion, and then the rotation speed is increased. Is output in the direction of the distribution flow path 307.
The serum of the separated serum part 302 reaches the opening of the output flow path 305, and when the serum runs out, the fluid movement stops.
The serum that reaches the distribution channel 307 is sequentially filled from the immediately preceding quantitative channel 308a by capillary force.
After the quantification flow paths 308a to 308d and all the other quantification flow paths are filled with serum, the number of rotations is increased, and the reagent reaction tanks 309a to 309d and other reagent flow paths connected to the other measurement flow paths are quantified by centrifugal force. Push in body fluids.

By the way, when the necessary amount of blood can be reduced by reducing the number of reagent items, the volume of the separated serum part 302 is reduced by inserting the prosthesis 310. (Fig. 13 (b))
Furthermore, an unnecessary reagent reaction tank is cut off by discharging a curing material to a predetermined position of the distribution flow path 307 by using an ink jet method or the like and curing it to form a plug portion 311.
The formation of the plug portion 311 is a preferable method because the ink jet method makes it possible to form a plug portion of an arbitrary size in a free place like a commercially available printer.
By forming the state as shown in Fig. 13 (b), the number of test items can be increased or decreased, and even a blood test unit that is mass-produced and fixedly formed should only test the necessary items. Is possible.

  Since it is possible to simplify the transfer of trace blood, it is possible to make full use of a testing device that can measure multiple blood components even with trace blood, especially in a rotor type analysis unit. Can be simplified.

The present invention can realize blood component measurement without any special training, overcomes the problems in mass production of units handled by individual patients in a disposable manner, enables stable measurement, and enables blood measurement. Expand the field.
Even small amounts can be used for accurate blood measurement without waste, simplifying blood tests and making it easier to check the health of healthy people.
The present invention expands the range of use of a micro blood analysis unit having a flow path configuration that is difficult to adjust, reduces the cost of manufacturing the analysis unit, and makes it possible to provide a simpler blood test unit.

The figure which shows one Example of this invention. The figure for demonstrating operation | movement of one Example of this invention. The figure for demonstrating operation | movement of one Example of this invention. The figure which shows the other Example of this invention. The figure explaining operation | movement of the other Example of this invention. The figure which shows the other Example of this invention. The figure which shows the other Example of this invention. The figure which shows the other Example of this invention. The figure which shows the other Example of this invention. The figure explaining operation | movement of the other Example of this invention. The figure which shows the other Example of this invention. The figure explaining operation | movement of the other Example of this invention. The figure which shows the other Example of this invention.

Explanation of symbols

01 Impregnating member 02 Support member 03 Grasping part

Claims (25)

A blood transfer device comprising an impregnation portion that contacts and impregnates body fluid exposed on the skin surface and a support portion that supports the impregnation portion, and the impregnation portion has a shape that can be accommodated in the body fluid inspection portion. From a puncture device for puncturing the skin surface to expose blood to the skin surface, a blood transfer device for impregnating the blood exposed to the skin surface by the puncture device and placing it on the setting part of the blood test unit Blood test system. The blood transfer tool according to claim 1 or 2, wherein the impregnated part contains a blood coagulation inhibitor. A placement unit for placing a blood transfer device, an extraction means for extracting a test element from an impregnation part of the blood transfer device placed in the placement unit, a quantification unit for quantifying the extracted test element, and quantification by the quantification unit The blood test system according to claim 2, further comprising a blood test device including a detection unit that reacts the test element with the reagent component to obtain specific component information.   A blood reagent reaction measurement unit having a supply means capable of supplying and controlling a necessary blood volume in accordance with a required test item in a blood reagent reaction measurement unit having a reagent reaction system that causes color reaction of serum after blood cell separation with a number of reagents. A stimulating means for applying a physical stimulus to a blood collection site, a puncturing means for puncturing a site stimulated by the stimulation means, an absorptive member that is in contact with the site punctured by the puncturing means and absorbs and absorbs blood; A blood test system comprising measuring means for extracting blood, separating it, and measuring biological information. The gastric blood test system according to claim 6, wherein the physical stimulation is formed by vibration means and suction means. The blood test system according to claim 6, wherein a puncture member is disposed in the absorption member.
    In a blood biological measuring instrument that measures optically by operating a fluid while rotating a rotor, a standard tank containing a standard substance is provided on the circumference of the measurement. A bodily fluid inspection system having a correcting means for measuring optical absorbance of a standard substance that has been inserted and correcting optical information such as dimensional errors.   The body fluid test system according to claim 9, wherein the correction of the optical information is correction of a calibration curve.   The body fluid test system according to claim 9, wherein a plurality of the standard tanks are arranged at equal angular intervals on the circumference. The body fluid test system according to claim 9, wherein the standard substance has a known concentration value. A unit that optically measures reagent reactions caused by blood components, and has a rotating body structure in which many measurement reaction chambers are arranged concentrically, and sequentially measures optically in a transmission type while rotating the unit. In a blood test system equipped with optical measurement means, a plurality of adjacent dummy windows are provided on the optical path trajectory for measurement, the beam irradiation position of the light source is controlled based on the amount of light passing therethrough, and measurement light is always applied to the reagent reaction tank. Blood test system to irradiate.
The blood test system according to claim 13, wherein the dummy window is disposed on the same circumference as the measurement reaction chamber and at a position perpendicular to the circumferential direction of the rotating body. The blood test system according to claim 13, wherein individual dummy windows of the plurality of adjacent dummy windows are shifted in the circumferential direction. The blood test system according to claim 13, wherein the dummy windows are 3 or more. The blood test system according to claim 13, wherein a light receiving portion corresponding to the dummy window is formed.   The blood test system according to claim 13, further comprising an adjustment unit that adjusts a position of the measurement reaction chamber and the optical measurement unit based on optical information obtained based on the dummy window.   The blood test system according to claim 13, wherein one or a plurality of the dummy windows are arranged in one rotating body. In the body fluid testing system, which separates the body fluid on the rotor by capillary force and centrifugal force, performs quantitative mixing with the reagent, and then obtains information such as component concentration from the color reaction of the body fluid component and the reagent,
A first reagent reaction chamber having a first reagent contained therein, an input port for inputting a sample, and an output port for outputting a mixed sample solution of the first reagent to the outside; A body fluid test system comprising an input port for receiving a reagent and inputting a mixed sample solution supplied from the first reagent reaction tank, and a second reagent reaction tank having a configuration capable of being measured from the outside. The body fluid test system according to claim 20, wherein the measurement is an optical measurement. 21. The body fluid testing system according to claim 20, wherein the flow path connecting the first reagent reaction tank and the second reagent reaction tank is a flow path in which movement of an internal fluid is adjusted by a rotational force. 21. The body fluid testing system according to claim 20, wherein the flow path, the first reagent reaction tank, and the second reagent reaction tank are formed on one rotor. In the body fluid test system that performs blood cell separation etc. on the rotating body, reacts serum and reagents, and measures the color reaction value,
A blood test system comprising a prosthesis for performing prosthesis to adjust the volume in the blood operation section. The blood test system according to claim 24, wherein the prosthesis is for adjusting a serum amount obtained in a blood cell separation region.

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