WO2006025608A1 - Body fluid feeder and body fluid inspection system - Google Patents

Abstract

A body fluid feeder and a body fluid inspection system for feeding and inspecting a body fluid. The body fluid feeder, particularly a blood feeder, is characterized by comprising a body fluid impregnating part capable of impregnating the body fluid therein by the contact thereof with the body fluid and a support part supporting the body fluid impregnating part and in that the body fluid impregnating part has such a shape and a size that can be stored in the body fluid inspection part of a body fluid inspection apparatus. The body fluid inspection system is characterized by comprising a blood organism measuring device optically measuring by operating a fluid while rotating a rotor, a standard tank installed on the measuring circumference of the blood organism measuring device and storing a standard substance, and a correction means measuring the dispersion of the optical path length of the standard tank by measuring the absorbancy of the standard substance stored in the standard tank beforehand and correcting optical information such as dimensional error.

Description

Body fluid transfer device and body fluid inspection system

Technical field

 The present invention relates to a bodily fluid transfer tool for transferring bodily fluids such as blood and a bodily fluid inspection system using such bodily fluid transfer tools.

 Background art

 Concentration meter measurements of body fluid components typified by blood have been carried out for a long time using blood test equipment, and the measurement accuracy has been improved by improving the functionality of analyzers. Such a blood test apparatus is a so-called business use, and a method in which a qualified person such as a doctor or nurse collects necessary and sufficient blood (usually about several tens of ml) using a blood collection tube is generally used. Is.

 On the other hand, patients who are concerned about changes in blood glucose levels over time, such as diabetic patients, use blood collection devices that they can use at home. In this blood collection device, a technique is used in which blood is exposed to the surface of the skin, and a test piece is applied to the blood to impregnate it. It is desirable that the amount of blood collected be smaller in order to reduce the burden on patients and use at home.

 For example, Japanese Patent Application Laid-Open No. 1_3 1 8 8 71 describes a quantitative blood collecting device having a configuration for holding the expressed blood fraction while quantifying it. This quantitative blood sampling device is suitable for a measuring device that does not have a quantitative portion, but because it is configured to hold blood by capillary force, it has the disadvantage that only a small amount of blood can be used, and it is maintained by capillary force. Therefore, if there is an incorrect contact, the capillary force may be lost and blood may be dispersed.

By the way, like a dry chemistry tree, a 'test paper type blood test The investigative element is that the blood expression part is applied to the supply part made of a porous material, and there is no force quantification that makes it possible to impregnate the porous material with blood. It is necessary to supply a certain amount of blood using sucrose.

 On the other hand, small, portable blood test devices that measure blood component concentrations in multiple items by measuring, moving and manipulating body fluids on the flow path using capillary and centrifugal forces. Has been proposed. In this blood test apparatus, for example, a disc-shaped blood is injected into the center, and then blood is separated and distributed by force, and quantitative blood is supplied to the 6-type drug reaction tank, and the 3¾ color reaction is optically performed. Although there is a device that measures and displays the concentration of the component, the transfer of blood from the specimen must use a pipette.

 Other conventional techniques described for blood tests include, for example, Japanese Patent Laid-Open No. 1 1 1 1 7 4 0 4 8, Japanese Patent Laid-Open No. 2 0 0 4 — 1 0 1 3 8 1, and Japanese Patent Laid-Open No. 5 7-2. No. 2 1 0, No. 9 Heisei 5 0 4 7 3 No. 2, No. 3 No. 5-5 1 0 4 8 No. 4, No. 5 No. 5-5 0 8 7 0 No. 9 The official gazettes of No. 5 0 — 2 3 6 2 4 and the special table 2 0 0 3 — 5 2 0 5 8 2 can be cited. Disclosure of the invention

 Although there is no small amount of blood that holds enough blood for measurement and there is no instrument to transfer the blood to a blood test device, more than tens to hundreds of microliters (1) of body fluid can be used for blood tests. There is still no suitable configuration for transporting the equipment for inspection.

Optical body fluid component measurement in a blood test apparatus usually uses an absorbance measurement technique, and blood components such as serum are supplied to a columnar reaction tank having a liquid or solid reagent inside. After reacting with the reagent for a predetermined time, a light beam such as a laser beam is applied from the side or the vertical direction. Irradiate, measure the amount of light attenuation from reflected or transmitted light, and calibrate and measure by comparing with a calibration curve obtained from measurement of a material that has a known absorbance.

 Therefore, it is necessary to cope with a darker reaction color when reducing the blood volume and making the entire device thinner and smaller, or depending on the nature of the reagent or sample, and at least increase the optical path length of the reaction tank. In short, in order to detect more light obtained from the reaction sample and improve the accuracy for detecting high concentration values using the 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 invisibility and material transformation that have not been a problem until now and material modification will be affected by the measurement light. It comes to give. For example, when the optical path length is 2 mm, the error of 100 S cron (m) generated in the member forming the optical path length is minus 5% accuracy by itself. Furthermore, assuming that the optical path length is 1 mm, it becomes 10% minus only with the above configuration, and accurate component analysis becomes difficult.

 As described above, regarding 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. In a low-pressure blood analyzer using capillary force, it is preferable to analyze blood using a smaller space.

 Reducing the volume also means reducing the volume of the reagent reaction tank that mixes blood and reagents to cause a color reaction. At this time, the area of the part irradiated with measurement light and irradiated to the outside Reducing the value may be a better adjustment than other reductions.

Reducing the area above and below the reagent reaction tank, on the other hand, narrows the irradiation range of measurement light such as lasers, so that the laser light is focused with a lens. Even if the irradiation area is reduced, the deviation between the reaction tank and the optical path, which is caused by uneven rotation in the evening, may be largely reflected as a measurement error.

 On the other hand, some of the component test items that cover multiple blood components must be measured spectrophotometrically with the results of reaction with at least two reagents, such as DHLC, unlike other reaction processes. Some items are not

. However, a configuration in which a microfluid is moved and a reagent reaction is performed a plurality of times and a configuration that enables measurement of a smaller amount of a dish liquid component has not yet been disclosed.

 In addition, when a flow path, reaction tank, separation tank, etc. are formed on a substrate to measure the test unit, an inspection unit that ensures stable reaction operation by creating a precisely adjusted mold. Depending on the strength of the situation, it is often necessary to minimize the amount of blood handled by the laboratory.

 This situation is also consistent with the need to keep blood with minimal blood draw so as not to cause more pain to the skewer. For example, if the required blood volume is 4 5 1 and the blood analysis tool provided to allow 15 types of test reactions, 5 test items may be sufficient depending on the test status. But blood volume is required 4 5 1.

 As one of the reasons why the required amount of blood does not change, for example, in the configuration using centrifugation for blood cell separation as shown in FIGS. 13A and 13B, a blood cell separation tank (for example, In this figure, the connection position of 30 2) and the serum flow path after centrifugation (30 5) must be fixed, including the margin of the matrix value. However, it is impossible to change the connection relationship between the blood cell separation part and the flow path after mass production using a precise mold.

The above items are collected from a limited number of blood samples. This is a bigger problem for a configuration that can be applied to home medical care.

 The present invention has been made in view of the above problems, and realizes a novel configuration for transferring bodily fluids represented by blood. That is, according to the present invention, a body fluid impregnated portion that is brought into contact with and impregnated with a body fluid exposed on the skin surface and a support portion that supports the body fluid impregnated portion are provided, and the body fluid impregnated portion is a body fluid of the body fluid inspection device. By using a body fluid transfer device having a shape and size that can be accommodated in the examination section, a small amount of body fluid collected from a patient, typically blood, can be easily transferred.

 In the bodily fluid transfer device of the present invention, the bodily fluid impregnation part is easily separated and extracted with at least a bodily fluid component, such as serum, at the time of centrifuge separation while impregnating and holding liquid such as nonwoven fabric, sponge, porous ceramics, etc. What is necessary is just to be formed from the porous material used. In addition, the body fluid impregnated part only needs to have a shape and a dimension that can be mounted in a predetermined part of the inspection device. Preferably it is.

The support part is preferably integrated with the body fluid-impregnated part. For example, the support part can be integrated by adhesion, mechanical bonding, or the like. The support portion is formed of, for example, a dense plastic, and the shape thereof may be any shape as long as it is easy to support and satisfies the use when the body fluid-impregnated portion is inserted into the inspection device. It is not limited. In addition, the support part, when transferring body fluid such as blood impregnated in the body fluid impregnated part, ensures that the body fluid does not adhere to the person involved in the transfer (such as a laboratory technician) or the inspection equipment. As long as the present invention is not particularly limited, the present invention relates to a testing device that processes 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 to develop a color. At Therefore, it is possible to effectively transfer a small amount of bodily fluid from the living body to equipment that can be sufficiently inspected with a small amount of bodily fluid. .

 Furthermore, in the present invention, in the optical measurement, one or a plurality of reference reaction tanks in which an optical reference material is put in place of a reagent are placed on the measurement trajectory, so that the absorbance measurement value of the reference substance can be measured. By obtaining the concentration from the calibration curve, and detecting the optical path length fluctuation from the deviation of the calibration curve, and compensating the concentration, it is possible to eliminate the variations in specifications that occur during mass production of products.

 In the present invention, it is necessary to shorten the optical path length for the purpose of lowering the absorbance OD value for measuring a blood reaction item having a high concentration or reducing the total blood volume to facilitate an oxygen reaction, etc. Calibration of the calibration curve is possible by measuring the reference reaction tank.

 One or a plurality of reference reaction tanks may be arranged on one optical measurement trajectory in the present invention. For example, an arrangement in which reagent reaction tanks are adjacent to each other at intervals of 90 degrees on the trajectory is exemplified.

 The optical reference substance 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.

 The calibration curve can be corrected by a single-point method, where an optical reference material having a known concentration component is placed on the optical path orbit at one location in the low-rise area. Place optical reference materials of known components with different concentration values (for example, concentration values indicated by cl to c4 in Fig. 8D) at several locations, and obtain errors in the absorbance values obtained individually. This □ overnight calibration curve slope correction etc. is exemplified, but even if there are multiple points, if the error is small, etc., the correction value is determined in a predictive and linear function. May be.

The measurement of the reference reaction tank can be performed by individual units before measurement, when performing measurement sequentially, when performing final measurement, or during production. In some cases, the data may be converted into lot management data.

 Furthermore, the present invention is a unit for measuring blood components by a large number of reagent reactions, and has a rotating body structure in which a large number of measurement reaction chambers are concentrically arranged, while transmitting the unit while rotating the unit. In a blood test system comprising optical measuring means for optically measuring sequentially with a mold, an adjacent 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. By detecting the deviation of the light emission path of the light emitter from the amount of light transmitted through the dummy window, accurate sample analysis is realized.

 Furthermore, the present invention relates to a component measurement that requires a plurality of reagent reactions from a very small amount of blood, and has an input port for storing a reagent therein and inputting a sample, and an output port for outputting a mixed sample solution of the reagent to the outside. A first reagent reaction tank, a reagent container inside, an input port for 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. The combination configuration enables mixing with multiple reagents only by adjusting the centrifugal force and capillary force. According to this configuration, it can be used in combination with another one-time reagent reaction configuration.

 Furthermore, the present invention relates to a configuration that makes it possible to adjust the amount of bodily fluid to be used. On a rotating body, blood cell separation is performed by a blood cell separation unit, and a reaction between serum and a reagent is performed, and a color reaction value is measured. In the system, by providing a prosthetic body that performs prosthesis to adjust the volume in the blood cell separation unit, the volume is adjusted, the quantitative value is adjusted, and the fluid operation timing is adjusted.

According to the present invention, as will be understood in more detail from the following description, the use of a bodily fluid transfer device comprising a combination of a bodily fluid impregnated portion and a support portion enables a small amount of bodily fluid to be quantified, distributed, mixed, etc. When transferring to a testing device that can perform multi-component component measurement through operation processing, it is simple and less likely to cause bodily fluids to scatter to the outside. And a body fluid testing system, typically a blood transfer device and a blood testing system.

 In addition, according to the present invention, when multi-component analysis is performed using a small amount of blood, in order to make the test unit thinner and thinner, it is unavoidable at the time of optical measurement and mass production. It is possible to cope with changes in the measurement range and the measurement range is greatly expanded.

 Furthermore, according to the present invention, optical information sufficient for analysis can be obtained even with a small amount of sample, and an accurate value of the component concentration can be obtained as a reagent reaction region having a diameter of several hundred m. But it becomes possible to measure.

 Furthermore, according to the present invention, a test item for reacting a plurality of types of reagents can be easily realized by adjusting centrifugal force and capillary force, and combined with a test item for reacting with one reagent. This makes it possible to perform many types of multi-item inspections by moving fluids.

 In addition, according to the present invention, a prosthesis can be placed on a portion of a blood cell separation chamber, a mixing / dilution chamber, a blood storage chamber, and the like that are fixed on the unit and that can adjust the volume while maintaining functionality. By doing this, it is possible to expand the field of use such as measuring different components while having the same shape and size. Brief Description of Drawings

 FIG. 1 is a perspective view showing a first embodiment of the present invention.

 2A to 2C are schematic diagrams sequentially showing the operation of the embodiment shown in FIG.

 FIG. 3 is a perspective view showing the operation of the embodiment shown in FIG. 1, and FIG. 4 is a perspective view showing the second embodiment of the present invention.

 FIG. 5 is a perspective view showing a third embodiment of the present invention.

6A to 6D are cross-sectional views sequentially showing the operation of the third embodiment of the present invention. It is a surface view,

 7A and 7B are a sectional view and a perspective view showing a fourth embodiment of the present invention,

 8A to 8D are a perspective view, a cross-sectional view and a calibration curve graph showing a fifth embodiment of the present invention,

 9A and 9B are a perspective view and a sectional view of a sixth embodiment of the present invention,

 FIGS. 1 O A to 10 C are graphs of received light intensity showing the operation of the embodiment shown in FIGS. 9A and 9B.

 FIG. 11 is a plan view showing a seventh embodiment of the present invention, and FIGS. 12A to 12C are schematic views showing the operation of the embodiment shown in FIG. And

 13A and 13B are schematic views showing an eighth embodiment of the present invention. BEST MODE FOR CARRYING OUT THE INVENTION

 Subsequently, the present invention will be described with reference to its preferred embodiments. It should be understood that the present invention is not limited to the specific embodiments described below.

Body fluid transfer configuration, especially blood transfer configuration:

 As an example of the best mode for carrying out the present invention, a combination of a body fluid impregnated portion and a support portion that supports the body fluid impregnated portion is shown. The shape of the body fluid impregnated part is at least a shape that can be accommodated in the body fluid testing device. The body fluid is typically blood.

The body fluid-impregnated portion of the present invention has, for example, a shape and structure accommodated in a portion that injects blood from a unit that separates, quantifies, mixes, and moves blood cells by rotating force when it is a blood-impregnated portion. Have a low evening It is preferable to have such a porosity and shape that blood can be extracted to the outside by rotation. The impregnation of blood in the body fluid impregnated part is not particularly limited, and may be a liquid holding structure by capillary force generated in the gap, or may be a brush-like porous material.

Optical measurement:

 In the present invention, one or a plurality of reference reaction tanks may be provided on the optical measurement trajectory, and preferably, the reference reaction tanks are arranged at a ratio of 1: 1 in a portion adjacent to the reagent reaction tank. . This is because the possibility that the reference reaction tank has the thickness fluctuation of the adjacent reagent reaction tank is sufficiently high.

 For example, the absorbance O D S is obtained by measuring the absorbance in the standard reaction tank, and the concentration C 1 is obtained based on the calibration curve drawn at the initial setting. Since the concentration C s of the reference substance in the reference reaction tank is set in advance, the difference C def between C s and C 1 corresponds to the thickness of the lid and the thickness under the reaction tank. Therefore, if the concentration value obtained in the reagent reaction vessel around the reference reaction vessel is corrected by the concentration fluctuation C de, the correct concentration can be obtained.

 In this way, if there are a large number of reference reaction tanks, the correct concentration can be obtained, but conversely, a large area is required and the amount of calculations increases dramatically, so every other or every other number A reference reaction tank may be set, and the parameters for blur correction may be repeated one or more times before and after the actual measurement.

 In the present invention, the analysis unit may automatically move by drawing an optical measurement trajectory, or may be a shape that moves manually, or an optical element that automatically moves and measures. A plurality of measurement probes may be provided, and the reagent part and the reference part may be measured simultaneously.

The present invention mainly arranges a plurality of reagent reaction tanks on a common circular orbit on a rotating body, and arranges a dummy window as a reference on the circumferential orbit, Dummy windows are formed on both sides in a direction perpendicular to the circumference, that is, in the diameter direction, and the light receiving elements on the measurement device side are also arranged at positions corresponding to the positions of these dummy windows. It is only necessary that the optical measuring body composed of the combination of the row and the light emitting element is formed so as to be slidable in the radial direction. The optical light emitting body is slid by the balance of the intensity of light received by the optical measuring body. Therefore, it is sufficient that the light emission of the light emitting element can always be adjusted so as to irradiate the center of the reagent reaction part. Further, the irradiation area may be adjusted by moving the low evening drive unit and low evening.

 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.

Component measurement that requires multiple reagent reactions from a small amount of blood: The present invention is suitably used for a so-called low-humidity body fluid component testing device, typically a blood component testing device. It is preferable that the flow is controlled by centrifugal force and capillary force. In the evening, 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 quantification of serum separated and extracted by the blood cell separation unit The first reagent reaction tank that mixes the quantitative serum and the first reagent and performs an intermediate reaction, and the solution reacted in the first reagent reaction tank is further reacted with the reagent to develop color, and the components are measured by external photometry. It is preferable to be composed of a second reagent reaction tank to be measured.

 Although it may be preferable to quantify the sample supplied to the first reagent reaction tank, it should be quantified during centrifuge separation, for example, as shown in Figs. 12A to 12C. It may be a configuration.

The movement of the liquid between the first reagent reaction tank and the second reagent reaction tank is, for example, using centrifugal force due to rotation and capillary force. A configuration coexisting with one reagent reaction configuration is preferred. For example, in the case of a single reagent reaction configuration, a configuration in which a mixing step with a diluent is incorporated, and a reaction with the first reagent is performed during this mixing step is exemplified.

 In the case of a plurality of reagent reaction configurations, the dilution step may be omitted, but a configuration may be added in which a diluent is supplied into the reaction tank at the time of reaction with the first reagent. The reagent may be a solid-stated pre-encapsulated one or supplied from the outside during the reaction. Configuration that allows adjustment of the amount of body fluid to be used:

 The present invention inputs a body fluid, typically blood, at least in a unit that uses the power to move the substrate, such as low evening, or in a unit that uses capillary action, air pressure, etc. without moving the substrate. Using a prosthesis to change the volume of the part that temporarily stores blood, the part that separates blood cells, the part that mixes with other substances such as diluents, etc. What is necessary is just to adjust timing etc. The site | part of a prosthesis, etc. are selected suitably.

 For example, in the blood cell separation unit, in the case of a blood cell separation unit where the timing of taking out the serum is determined by the degree of blood cell separation, the blood cell storage unit is prosthetic and the amount of blood cells separated and accumulated is adjusted. There are cases.

 Examples of the prosthesis include a prosthesis using a solid block having the same material and size and shape as the base material, and encapsulating a curable resin. It is selected appropriately.

Example

 The following examples are intended to further illustrate the present invention. Example 1

FIG. 1 is a perspective view showing a bodily fluid transfer device according to a first embodiment of the present invention. is there. In the figure, 1 is a body fluid impregnated member (hereinafter also referred to as “impregnated member”) for impregnating body fluid, which is typically blood. Nonwoven fabric, sponge, sponge, porous ceramics, porous plastic It is made of paper, wood. The porosity of the impregnated member 1 is preferably 50% or more, but is appropriately adjusted in accordance with the force with which the body fluid is extracted from the impregnated member in the body fluid testing device to which the impregnated member 1 is attached.

 The impregnated member 1 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 body fluid (blood, etc.) force is retained by the centrifugal force so that it flows to the outside, and various shapes can be taken within that range.

 Reference numeral 2 denotes a support member for supporting the impregnated member 1, which is formed of water-repellent plastic, glass, or other members. The impregnation member 1 and the support member 2 can be connected by an adhesive or the like in addition to mechanical coupling.

 Reference numeral 3 denotes a gripping part for the body fluid transfer tool, which is formed integrally with or separately from the support member 2 so as to be easily transported when picking up with a finger and transporting. The gripping part 3 may be omitted depending on the transfer speed and the support material.

 The handling operation of the bodily fluid transfer device of this embodiment will be described below with reference to FIGS. 2A to 2C and FIG.

In Fig. 2A, skin H is injured using a skin injury device (not shown) equipped with a puncture device. Examples of the skin damage device provided with the puncture device include those described in Japanese Patent Application Laid-Open No. 5-635506, but other examples include a configuration in which the lancet protrudes instantaneously. . When damage S is formed on skin H, blood B exudes from the inside of skin H. Next, as shown in FIG. 2B, the impregnated member 1 is applied to the exuded blood B with the grip portion 3. As shown in Fig. 2B and Fig. 2C, Blood B is impregnated and absorbed (absorbed blood: GH).

 Next, as shown in FIG. 3, the impregnated member 1 is accommodated in the blood accommodating portion 6 of the blood analysis row RO. When the impregnated member 1 is accommodated in the blood analysis row RO, the support member 2 is practically handled integrally with the lid portion of the mouth pot RO.

 The blood impregnated in the impregnating member 1 accommodated in the blood accommodating part 6 flows out to the outside by the rotation of the RO. The blood that flows out travels along the flow path 7 and reaches the blood cell separation unit 8.

 In the blood cell separation unit 8, serum and blood cells are separated by moving blood cells with a high specific gravity toward the outer circumference by centrifugal force. After the separation is sufficiently performed, the serum moves to the distribution channel 10 via the siphon tube 9 by lowering the rotation speed of the low-rotation RO. The serum that has moved to the distribution channel 10 moves to the individual reagent reaction tank 1 1 and is filled in the quantitative flow channel.

 After filling the serum, the rotation speed of the rotor RO is increased and the fixed amount serum is supplied to the reagent reaction tank 11. Here, the opening 1 2 on the low evening RO is an example of an opening for coupling with the device for rotationally driving the mouth overnight RO. As described above, in this embodiment, the configuration is simple, The treatment of the exposed blood can be performed reliably, and measurement of many blood components can be realized from a very small amount of blood.

Example 2

 A bodily fluid transfer device according to a second embodiment of the present invention will be described in detail with reference to FIGS. 4 and 5. FIG.

The embodiment shown in FIG. 4 shows a configuration in which a body fluid impregnated member 1 and a diluent storage part 2 1 are provided on one support body 2 2. The diluent storage unit 21 is configured by filling a thin plastic bag with physiological saline or the like, and can be torn when pierced by a sharp needle or blade from the outside. Dilution The plastic bag constituting the liquid storage part 21 may be any bag that can be broken if a sharp projection collides with it. The diluent storage unit 21 may be made of a material that keeps the quality of the diluent constant, such as an aluminum bouch.

 In FIG. 4, the gripping portion shown in FIG. 1 is not provided, but the support 22 is relatively larger than the support portion shown in FIG. 1, and can be gripped as it is. A gripping part may be added if necessary.

 FIG. 5 is a perspective view showing a state in which the bodily fluid transfer device (blood transfer device) of this embodiment is actually installed on a rotor type blood test unit. In this blood transfer device, a smaller amount of blood is used. In this case, the blood is diluted and used, but the impregnation member 1 is applied to the site where the skin has been pierced and the blood has exuded in a state where the diluent storage unit 2 1 is provided on the support 2 2. After the blood is impregnated, the blood transfer device is set in the RO RO as shown in FIG. The impregnating member 1 is press-fitted and stored in the blood storage section 6 of the low temperature RO, and the diluent storage section 2 1 is also press-fitted and stored in the diluent storage section 2 3. Here, when the diluent reservoir 21 is press-fitted, the puncture tool 24 protruding from the bottom surface of the diluent reservoir 2 3 punctures and breaks the diluent reservoir 21 to dilute the internal diluent. A configuration is adopted in which the liquid is stored outside the liquid reservoir 2 1.

 With such a configuration, the handling of the diluent can be simplified, the diluent can be easily stored, and the work for releasing the diluent from the diluent reservoir 21 can be facilitated.

Example 3

 A bodily fluid transfer device (blood transfer device) according to a third embodiment of the present invention will be described in detail with reference to FIGS. 6A to 6D.

FIG. 6A shows a configuration in which a puncture means that slides up and down is incorporated in an impregnated member. 6 1 is an impregnated member, which is porous and centrifuges blood It is formed with what is detachably held at the time of separation. Reference numeral 6 2 denotes a support member that accommodates the impregnating member 6 1, and an upper portion thereof and an extraction direction when the blood test apparatus is mounted are opened. Further, a puncture member 6 3 is formed at the center lower portion of the support member 6 2, and the puncture member 6 3 has an inner circumference in order to make a certain range slidable up and down. A puncture member accommodating portion 6 2 1 having a protrusion formed on the other is formed integrally or detachably with another support member. Furthermore, it is preferable that a plurality of stimulation pins 6 2 3 are planted in the support member 6 2, and that the tips of the stimulation pins 6 2 3 have a slightly acute angle.

 The puncture member 63 has a blade-like shape, a needle-like shape or the like, and has a protruding portion 6 3 a that engages with a protruding portion on the inner peripheral surface of the puncture member accommodating portion 6 21 on the outer peripheral side surface. It is. The puncture member 6 3 is slidable up and down and has drive means 6 4 for assisting this sliding.

 The driving means 64 has a configuration that pushes the puncture member 6 3 upward and also moves it downward. The drive means 64 is not shown in the figure, but is a mechanism that transmits the deformation force of an elastic member such as a panel to the transmission member, and a combination in which the puncture member and the transmission member are in contact is illustrated. The vibration means 64 is for transmitting the vibration generated by the rotation of the vibration mode to the outside.

 Reference numeral 65 denotes a placement portion for a specimen, which is a portion for placing a puncture site such as a fingertip. The mounting portion 65 accommodates the support member 62, and the open edge portion of the support member 62 forms a protruding portion 62 2 in a slightly protruding state as shown in the figure.

 Next, the operation of the illustrated blood transfer tool will be described.

As shown in FIG. 6A, the fingertip is placed so as to cover the protruding portion 6 2 2 that forms the outline of the placing portion 65. The puncture member 63 is hidden inside the impregnation member 61. Next, the vibration means 64 is vibrated to transmit the vibration to the support member 6 2. As a result, the vibration generated in the upward projecting portion 6 2 2 of the support member 6 2 and the plurality of stimulation pins 6 2 3 is transmitted to the finger as a stimulus.

 Next, as shown in FIG. 6B, the puncture member 63 is vigorously pushed upward by the driving means (not shown) (arrow 6 S). The puncture member 63 breaks through the impregnating member 61 and collides with the fingertip YH, causing damage S.

 Thereafter, as shown in FIG. 6C, the driving means is driven to push down the puncture member 63 (arrow 6 F). The blood (GB) exposed from the damage S is impregnated in the impregnating member 61 and held.

 After the blood (GB) is sufficiently impregnated and held in the impregnated member 61, the support member 62 is removed from the mounting portion 65 and attached to the blood test apparatus (not shown) as shown in FIG. 6D. .

 In the present embodiment, the structure in which the impregnating member 61 and the puncture member 63 that can slide up and down are combined is shown. However, the puncture member is not slid up and down, and the suction force is used while keeping it fixed. The structure may be such that the skin is raised and puncture is performed.

 In addition, a combination of a puncture member and an impregnation member may be further combined with a low temperature unit for blood testing. FIG. 7A and FIG. 7B show an example of this.

Example 4

 FIG. 7A is a cross-sectional view of a rotary blood test apparatus (also called a blood test unit) having a puncture portion, and FIG. 7B is a perspective view thereof.

 In the illustrated rotary blood test apparatus, 70 is a low evening, and 7 1 is a mouth and evening main body. Mouth overnight 7 1 is made of PP, polyacrylic material, etc., and is made of a translucent material as a whole.

7 2 is the lid of Low evening 70, PET, Polyacrylic, PP It is joined to the main body 7 1 with adhesive, double-sided tape, etc.

 Reference numeral 7 3 denotes a connection open surface, which is a part for bringing the fingertip into contact with the impregnated member 74. The impregnated member 74 is made of the porous material described above, such as a nonwoven fabric or a sponge. Puncture means 75 is formed in the shape of a needle or a blade, and has a structure that can slide up and down.

 The periphery of puncturing means 75 has a configuration similar to that of the blood transfer device described above with reference to FIG. 6A. In other words, the puncture means slides up and down in communication with the vertical drive of the external drive means.

 7 6 is a flow path, and the blood impregnated in the impregnating member 74 flows out by the rotation of the main body 7 1, and the passage for moving the blood that has moved outward to the blood cell separation unit 7 It is. In the blood cell separation part 7 7, an accommodation part 7 7 1 is formed to accommodate the separated blood cells in the circumferential direction, and the continuous protrusion 7 7 3 so that the separated blood cells do not return to the serum part 7 7 3 again. 2 is formed.

 78 is a distribution channel for connecting multiple reagent reaction vessels.

 7 9 is a quantitative flow path, and the amount of reagent to be supplied to the reagent reaction tank 80 is determined by the length and diameter of the flow path.

 8 ◦ is a reagent reaction tank that contains lyophilized reagent 80 1 inside. The reagent develops color due to different components.

 8 1 and 8 2 are light guides, and are formed of a translucent member so that measurement light from the outside can pass therethrough. It may be unnecessary if the entire rotor body and low lid cover are transparent or translucent.

 8 3 is a shaft part, which forms a connection part with the external drive part.

8 4 is a bearing recess, which is configured on the measurement storage side. When 3 is inserted, it has a configuration in which a locked state is formed on the inner insertion surface.

 8 5 is a housing case that houses the mouth all night 70 and has a sliding shutter 8 6 at the center. When the shutter 8 6 opens, the connection open surface 7 3 of the mouth 70 0 appears, and the impregnated member 7 4 appears. Shutter evening 8 6 is always closed by a resilient member, etc., and when necessary, the shutter evening 8 6 is opened and fixed, and a separate device is provided to close after blood collection. This is a preferable configuration to prevent the member 7 4 from being inadvertently touched.

 One part corresponding to the circumference of the reagent reaction tank 80 provided on the mouth / outside body 7 1 has holes 8 7 and 8 8 for optical connection with the outside. .

 Next, the operation of the illustrated rotary blood test apparatus will be described. A storage case 8 5 that stores the container 70 in advance is placed on the blood test apparatus. At this time, the puncturing means 75 is in a state where the driving force of the driving means on the apparatus side is transmitted. The shutter 8 6 of the storage case 85 is open, and the impregnated member 74 is stopped in a visible state at the opening.

 Next, as shown in FIG. 7B, the fingertip YH is placed on the impregnated member 74. Thereafter, the drive unit on the blood test apparatus side is driven to push up the puncture means 75. These operations are the same as those described above with reference to FIGS. 6A to 6C.

 After the blood is sufficiently impregnated in the impregnated member 7 4, release the fingertip and close the shutter 8 6. The opening / closing operation of the shutter 86 may be automatically closed when the housing case 85 is driven.

It may be unclear whether or not the blood exposed from the skin damaged part is sufficiently impregnated. It may be judged electrically by measuring the amount, area, etc.

 Thereafter, the low angle 70 is rotated, the blood in the impregnated member 74 is pushed in the circumferential direction, and moved through the flow path 76. Next, serum is separated and extracted by the blood cell separation unit 7 7, and filled into the quantitative flow path 79 connected to each reagent reaction tank 80 through the distribution flow path 7 8.

 After the serum is filled, the rotational speed of the low pressure 70 is increased, and the serum in the quantitative flow path 79 is pushed into the reagent reaction tank 80 in the form of being pushed out. In the state where the color of the infused serum reacts with the reagent, laser light is transmitted from the outside (HH) through the hole 8 7 of the housing case 85, and the color is measured to obtain the component concentration.

 It should be noted that the above-described operation of Low Level 70 is an example, and it is recommended to adopt various configurations in the implementation of the present invention.

 Such a combination of blood analysis unit and puncture means makes it possible to easily perform blood analysis even without blood collection.

Example 5

 Fig. 8A shows blood for measuring the concentration of multi-component components by separating and quantifying the blood at the center while rotating the row, distributing the quantified serum to each reagent tank and measuring the color value. It is an Example of an inspection system. FIG. 8B is a schematic cross-sectional view taken along line X 2 —X 2 ′ of the blood test system shown in FIG. 8A.

 80 is a mouth / outlet, which is formed by joining a transparent or semi-transparent mouth / outside body 8 1 made of polyacryl, PP, PET, or the like and a lid portion 8 2. In FIG. 8A, the low evening body 8 1 without the lid 8 2 is shown.

In the rotor body 8 1, a blood storage tank R 1, a blood cell separation tank R 2, a distribution flow path R 3, and a quantitative flow path R 4 are formed as recesses, a reagent reaction tank 8 4 and 8 6, a reference reaction tank 8 5, 8 7, 8 8, 8 9 and 9 0 are also recessed. The lid 8 2 is bonded from the top with double-sided tape or adhesive. 8 3 is an optical measuring unit, and a part of the low angle 80 is sandwiched up and down in a non-contact manner. The optical measuring unit 8 3 has a light emitter 9 2 such as a laser and a light receiving unit 9 3. The optical measuring unit 8 3 irradiates light on the measuring light path 9 1, and the light passing through the reaction vessel is received by the light receiving unit 93. ing.

 9 4 is a reaction tank, and the inside is filled with reagents and sample or reference material. The reference substance in the reaction vessel 94 does not necessarily need to be filled to the extent that there is no space, and at least it should be a standard for optical measurement.

 9 8 is a translucent part A, which is a part of the lower body 8 1, and has translucency. Reference numeral 9 9 denotes a translucent part B, which is formed integrally with the lid part 8 2 and has translucency. 9 5 indicates the optical path length, 96 indicates the thickness of the translucent part B, and 9 7 indicates the thickness of the translucent part A.

 Next, the operation of the illustrated blood test system will be described.

 In the present embodiment, the mouth / portion 80 rotates around the center point O, and blood (which may be impregnated blood) supplied to the central blood reservoir R 1 is caused to flow through the flow path R by centrifugal force. 6 Move to the blood cell separation tank R 2 through the blood cell separation by adjusting the rotational force, extract the serum. The siphon flow path R 5 supplies serum to the distribution flow path R 3 due to a decrease in the rotational speed and increase of the low speed 80, and the serum supplied to the distribution flow path R 3 R 4 is filled by capillary force.

Next, the rotation of the rotor 80 is strengthened, the centrifugal force is increased, and the serum is pushed out into the reagent reaction vessels 84 and 86. Serum develops a color reaction with the reagent in the reagent reaction tank, and the optical measuring unit 83 starts the measurement operation. At that time, the absorbance in the reference reaction tank 85 is measured by the optical measuring section 83 in advance or after the fact. When the mouth is rotating at a predetermined speed or stopped, light emission of the light emitter 92 is performed by the light transmitting part A 9 8, the reaction tank 94, and the light transmitting part B 9 The light reaches the light receiver 9 3 via 9 and the absorbance at that time is measured.

 At this point, calibration curves shown in FIGS. 8C and 8D have already been formed. Fig. 8C shows a calibration curve for a reagent to which the single inspection standard method can be applied, and Fig. 8D shows a calibration curve for a reagent to which the multi-inspection standard method can be applied.

 In Fig. 8C, since the concentration of the reference substance is known 8 c, the absorbance O D a at that time is also known from the calibration curve 8 a, and this is the reference value. However, the absorbance value O D ad may be different from the reference value O D a in the measurement of individual reference materials on the actual law. Since this deviation 8 b is caused by uneven production of the translucent parts 96 and 9 7 of the reaction tank, the neighboring reagent reaction tank 8 4 is also corrected by the same concentration deviation value. As a result, an accurate density value can be obtained.

 The same applies to Fig. 8D. The difference between the absorbance values for each unit in the standard reaction tank O Dbd — concentration difference based on O Db (8 As a correction value, optical measurement of the reagent reaction tank for each unit is performed.

 By configuring as described above, it is possible to correct measurement values due to uneven production, which is difficult to correct, and to take the difference between other factors and changes in the optical path length when the reaction is too dark. This makes it possible to obtain an accurate concentration value using the calibration curve data of the optical path length before the change. Example 6

9A and 9B show a blood test system that is a sixth embodiment of the present invention. FIG. 9A is a perspective view of the blood test system of the present example, and FIG. 9B is a schematic cross-sectional view along the line X 2 —X 2 ′ of the blood test system shown in FIG. 9A. 9 0 0 is a rotor, which is composed of a lid portion 9 0 1 and a low evening body 9 0 2. The main body 90 2 is made of polypropylene, polyacrylic acid, PET, etc., and has a recess formed on the surface, blood reservoir R 1, blood cell separator R 2, distribution channel R 3, reagent reaction tank R 4, Siphon flow path R5 etc. are formed. FIG. 9A shows a state in which the lid portion 9 0 1 is not attached, while FIG. 9B shows a state in which the lid portion 9 0 1 is attached.

 Reference numeral 9 0 3 denotes an optical measurement unit.

 9 0 4 is a central dummy portion. The central dummy portion 04 is filled with a reference color-changing substance and transmits light to give a predetermined absorbance to the received light. 9 0 5 is an outer dummy portion. The outer dummy part 90 5 has the same shape as the central dummy part 90 4 and is filled with the same substance, and is provided in the outer peripheral direction. 9 0 6 is an inner dummy portion. The inner dummy portion 90 6 has the same shape as the central dummy portion 90 4 and is filled with the same substance, and is provided in the inner circumferential direction.

 Each dummy part is adjacent to each other, but the interval between the dummy parts is adjusted as appropriate within the range according to the blur of the evening at the time of optical measurement. The dummy parts shown in the figure have the same cylindrical shape, but may have other shapes such as a rectangular shape, and the position thereof is on the measurement trajectory and passes through the center of the reagent reaction tank. Any position can be used.

 The arrangement of the dummy windows is not necessarily an arrangement (9A) perpendicular to the circumferential direction, and may be an arrangement in a shifted state as in the arrangements 9B and 9C.

In the array 9 B, the dummy windows 9 0 5 ′ and 9 0 6 ′ on both sides are shifted from each other by a predetermined angle with respect to the central dummy window 9 0 4 ′. On the other hand, the array 9 C has a predetermined angle in the opposite direction to the array 9 B and the dummy windows 9 0 5 '' and 9 0 6 '' on both sides of the center dummy window 9 0 4 ''. It is shifted in degrees.

 Such a shifted arrangement is less likely to form a gap between the dummy windows (so-called “dead area”) (for example, between array 9A and array 9B in FIG. 9A) than array 9A. Therefore, the more accurate light irradiation position of the light transmitting unit 9 16 can be recognized.

 In the present embodiment, the arrangement patterns of the three dummy windows indicated by the arrangements 9A to 9C are shown. However, only various patterns are illustrated, and only one of these arrangement patterns is shown. In some cases, it may be arranged at predetermined intervals.

 Reference numeral 9 0 7 denotes an inner light receiving portion that receives light transmitted through the inner dummy portion 90 6, photoelectrically converts it, and sends it to the processing portion 9 1 7.

 Reference numeral 90 8 denotes a central light-receiving unit that receives light transmitted through the central dummy unit 90 4 and the reagent reaction vessel R 7, photoelectrically converts it, and sends it to the processing unit 9 17.

 Reference numeral 9 09 denotes an outer light-receiving unit that receives light transmitted through the outer dummy portion 9 0 5, photoelectrically converts it, and sends it to the processing unit.

 Reference numeral 9 10 denotes a lid inner translucent portion, which is disposed in the center direction of the low angle 90 0 and is formed of a translucent member. 9 1 1 is a lid center translucent part, which is formed of a translucent member, and 9 1 2 is a lid outer side translucent part, which is formed of a translucent member.

 Any of these light-transmitting portions is preferably formed of a material that does not attenuate as much as possible with respect to the transmitted measurement light, and if the lid portion 9 0 1 is formed of a light-transmitting member. The material is sufficient.

9 1 3 is a light transmitting part inside the body, which is made of a material that does not attenuate the passing measurement light. In addition, 9 1 4 is a main body central light transmitting portion, and 9 15 is a main body outer light transmitting portion, both of which are the same as the main body inner light transmitting portion 9 1 3 It has a material shape. Note that any of the main body translucent portions is not particularly required as long as the main body 9 0 2 has translucency.

9 1 6 is a light transmission unit, which is composed of a laser light source and a condenser lens group. The light transmitter 9 1 6 may include a plurality of laser light sources.

 9 1 7 is a processing unit, which includes a central processing unit and a memory. The processing unit 9 1 7 obtains the absorbance, 〇 D value, etc. for the transmitted light that has been input, compares and discriminates the distribution of the three values, and sends the drive control signal to the drive unit 9 1 8 Output.

 Reference numeral 9 1 8 denotes a drive unit, which includes a motor, a power transmission unit, an actuate and the like, and has a servo mechanism for sliding the optical measurement unit 90 3.

 9 1 9 is an electrical lead wire for transmitting an electrical output for emitting the laser beam of the light transmitting unit 9 1 6.

 9 20 is an electrical lead wire for transmitting an electrical signal from the light receiving unit to the processing unit.

 9 2 1 is an electrical lead wire for electrically connecting the processing unit 9 1 7 and the driving unit 9 1 8.

 Next, the operation of the illustrated blood test system will be described in detail with reference to FIGS. 10A to 10C.

 The driving of this embodiment is performed at the timing of actual sample measurement, and is controlled so that the center received light intensity (also called received light amount) OD is the strongest as shown in Fig. 10A. Is done.

That is, in a stable state, the mouthpiece 90 0 0 rotates, and when the reagent reaction tank on the locus 9 2 2 is optically measured, the laser beam output from the light transmitter 9 16 is somewhat The central dummy portion 9 0 4 is irradiated through the main body central light transmitting portion 9 1 4 while causing scattering and attenuation. The light that has passed through the central dummy portion 9 0 4 is received by the central light receiving portion 9 0 8 through the lid central light transmitting portion 9 1 1. The received light is further photoelectrically converted and transmitted as an electrical signal to the processing unit 9 17 through the electrical lead wire 9 20.

 The light transmitting unit 9 1 6 is located immediately below the central dummy unit 90 4, but a part of the light transmitting unit 9 1 3 and the outside light transmitting unit 9 1 5 are scattered due to light scattering. Through the inner dummy portion 9 0 6 and the outer dummy portion 9 0 5, respectively. Further, the passed laser light is received by the inner light receiving unit 9 0 7 through the lid inner light transmitting unit 9 10 and received by the outer light receiving unit 9 0 9 through the cover inner light transmitting unit 9 10. .

 As a result, as shown in Fig. 1 OA, when the horizontal axis is the position of the light receiving part and the vertical axis is the received light intensity OD value, the peak 9 b force 9 b of the central dummy part 9 0 4 is the strongest. Appears as a state.

 The state indicated by O A in FIG. 1 is the reference state, and 9 a indicates the intensity of light that has passed through the inner part 9 0 6. In addition, 9b indicates the intensity of the laser beam that has passed through the central part 904, and 9c indicates the outer dummy portion 905.

 However, if the center of rotation is shifted due to low rotation rotation of 90,000, for example, the output laser of the light transmission unit 9 16 is tilted to the outer dummy unit 90 5 If the light is output, the amount of light output to the outer dummy portion 9 0 5 will increase, and the received light amount 9 ί of the outer light receiving portion 9 0 9 will be The amount of light received is 9c, and the amount of light received by the inner light receiving unit 9 07 is larger.

At this time, the processing unit 9 17 instructs the driving unit 9 1 8 to slide a predetermined amount to the outside of the optical measuring unit 90 3, and the driving unit 9 18 receives the optical measuring unit 9 0 3. Slide it a predetermined amount and drive it so that the peak at the center as shown in Figure 1 OA becomes the highest in the next dummy area measurement. Then, due to uneven rotation of the rotor 90 0, as shown in FIG. 10 C, the light receiving intensity 9 g of the inner light receiving portion 9 07 is obtained from the light receiving amount 9 h and the outer light receiving amount 9 i of the central light receiving portion 90 8. When it becomes much larger, the processing unit 9 1 7 gives a command to the drive unit 9 1 8 to make the optical measurement unit 90 3 tune in the center direction, and the state as shown in FIG. Thus, the position of the optical measurement unit 90 3 is controlled.

 By making such adjustments in the blood test system, light measurement at the center of the reagent reaction tank becomes possible, and stable color reaction can be measured.

 An example of the amount of light received when the dummy windows are arranged as 9B or 9C is shown by broken lines 9J and 9K in FIG. 10A. Since there are no gaps (dead areas) between the light receiving parts, the areas where the light receiving parts 9 07 to 90 9 cannot receive light are reduced, and a more accurate light irradiation range can be obtained. Example 7

 The seventh embodiment of the present invention will be described in detail with reference to FIG.

 The embodiment shown in Fig. 11 is a disk-shaped unit (mouth / mouth) formed as a concave part on the RO, and after the sheet-like lid is put on the concave surface, the center point O is set. Rotates as the center. It is preferable that the drive device for the rotation can change the rotation direction of the row or change the rotation speed.

 Reference numeral 20 1 denotes an input flow path, which is formed from a blood storage part in the previous stage or a centrifuge part that separates blood cells and blood.

 Reference numeral 20 2 denotes a first reagent reaction tank in which reagent S 1 is enclosed. The reagent S 1 is preferably a lyophilized solid, but may be a liquid reagent to be injected at the time of use.

2 0 3 is the second flow path, which is a bent portion bent in the center direction in the middle And having a caliber capable of exerting capillary force.

 20 4 is the second reagent reaction tank, which has the same optical measurement trajectory as the reagent reaction tank that performs the color reaction with one other reagent ○ T, and has the second reagent S inside. 2 is enclosed and fixed. The second reagent S 2 may be solid or liquid like S 1.

 The volumes of the first reagent reaction tank 20 2 and the second reagent reaction tank 20 4 may be different from each other in the present embodiment, and the force set to have the same volume may be different. When the volume of the first reagent reaction tank 20 2 is larger than the volume of the second reagent reaction tank 20 4, the connection boundary between the second reagent reaction tank 20 4 and the second flow path 20 3 In addition, an overflow chamber may be provided to accommodate the overflow. The overflow chamber is, for example, 3 06 shown in FIG. 13 and FIG.

 Next, the operation of the embodiment shown in FIG. 11 will be described in detail with reference to FIGS. 12A to 12C.

 Serum, preferably quantitative serum, is supplied to the first reagent reaction tank 20 2 from the input channel 2 0 1 in FIG. Since the reagent S1 exists in the first reagent reaction tank 202, the quantitative serum is mixed with the reagent. At that time, change the rotation speed of the low evening or change the direction of rotation to mix thoroughly to form mixed serum SM (see Fig. 12 A).

 Next, stop or weaken the low evening rotation. Then, since the capillary force of the second channel 20 3 becomes stronger than the centrifugal force generated by the low-speed rotation, the mixed serum SM moves as if it is filled in the second channel 20 3. (See Figure 12 B).

When the mixed serum SM exceeds the bent portion, the rotational speed of the low evening is increased again. Due to the siphon phenomenon, the mixed serum SM flows into the second reagent reaction tank 204 and is filled. After the mixed serum SM is filled in the second reagent reaction tank 204, the mixing speed is increased or changed by changing the rotation speed to form the final mixed serum SM M (See Figure 12 C). The color value of this final mixed serum SMM is read by optical measurement from outside. As described above, the flow of liquid in the two reagent reaction tanks is adjusted by adjusting the balance between capillary force and centrifugal force. This makes it easy to mix reagents and specimens multiple times. By further connecting them, it is possible to perform three or more times of reagent reactions, fluorescent substances, magnetic substance binding, etc. Example 8

 An eighth embodiment of the present invention will be described in detail with reference to FIGS. 13A and 13B.

 Fig. 1 3 A and Fig. 1 3 B show the formation of a recess in a disk-shaped base material such as polypropylene, PET, PP, etc., and these recesses constitute a blood inlet, a flow path, a blood cell separator, etc. It is a thing. In these drawings, the entire structure is omitted. For the entire structure of the force, see, for example, FIG. 7A and FIG. The surface of the base material on which the recess is formed is covered with a sheet made of the same material as the base material, and a unity is formed.

 In FIG. 13A, 3 0 1 is an input flow path, which is connected to a blood injection part formed in the vicinity of the central part O.

 30 2 is a separation serum part, and the volume between the overflow chamber 3 0 6 and the connection port of the output flow path 3 0 5 determines the amount of serum that moves to the next processing part.

Reference numeral 30 denotes a blood cell storage part, which is formed by a deeper recess than the separated serum part. It should be noted that the blood cell storage portion 30 3 depends on the height of the separation wall 3 0 4. That is, when the separation wall 304 is high, it may not be formed deeply. The separation wall 30 4 is set to such a height that the separated blood cells do not return to the separated serum part 30 2.

 In this embodiment, since blood cells having a large specific gravity move in the outer circumferential direction when rotating the low evening, blood cell separation is performed without the separation wall 3 0 4. At that time, the blood cell storage section 30 3 may be deeper or formed in a zigzag shape so that the blood cells do not return.

 The output flow path 3 0 5 has a flow diameter that utilizes the capillary phenomenon and forms a bent portion in the direction of the center point O, so that the centrifugal force generated by the rotational force and the capillary force of the flow path Adjust the movement.

 The overflow chamber 30 6 is a storage section when excess blood overflows from the separated serum section 30 2. The overflow chamber 3 06 is connected in the direction of the center point 0 of the separated serum part 30 2.

 30 7 is a distribution flow path, one of which is connected to the output flow path 3 0 5, and is a side surface of the distribution flow path 3 0 7, and a constant flow rate at a predetermined interval in the outer circumferential direction. Roads 3 0 8 a to 3 0 8 d connect. The fixed flow channels 30 08a to 30 08d are connected to the reagent reaction vessels 3009a to 3009d respectively, and the fixed flow channels are distributed according to the number of reagent reaction vessels 30. 7 and added to connect between reagent reaction tanks.

3 10 is 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 of the prosthetic portion 3 10 is exemplified by the use of an adhesive, but depending on the shape, it may be simply fitted. In the present embodiment, the low evening does not need to be detached because it is generally used once. However, in some cases, the fitting configuration may be adjusted so as to be removable. 3 1 1 is a stopper part made of a water-insoluble substance for blocking the flow path. The stopper part 3 11 1 uses an inkjet-type discharge tool that accurately positions the discharge site to inject a water-insoluble and curable solution into the target flow. A method of discharging to the road surface and blocking the flow path after curing is preferably used. The ink jet method is a method that suffices to change a commercially available ink jet ink to a hardening material, and is a preferable method when forming an embodiment of the present invention.

 Next, the operation of this embodiment will be described.

 At first, the rotor rotates around the center point 0, so that the blood collected through the input flow path 30 1 is separated into the separated serum part 30 2 and the blood cell storage part as shown in FIG. Supplied to 3 0 3. Here, there is a lot of blood supplied from the input flow path 30 1, the blood fills up to the opening surface of the overflow chamber 3 06, and if it continues to increase, it will overflow by the amount of increase Flows into chamber 3 0 6

Increase or decrease the number of revolutions of the low evening so that the blood cells are accommodated in the blood cell accommodating part 30 3 beyond the separation wall 30 4. After all of the blood cells are accommodated in the blood cell storage section 30 3, the rotational speed of the rotor is reduced. Then, due to the capillary force of the output flow path 30 5, after the serum exceeds the bent portion, the rotation speed of the mouth overnight is increased, so that the serum of the separated serum section 30 2 is distributed to the distribution flow path 3 0 7 Output in the direction of. The serum in the separated serum section 30 2 reaches the opening of the output flow path 30 5, and when the serum runs out, the fluid stops moving. The serum that reaches the distribution flow path 3 0 7 is immediately before due to the capillary force. The quantitative flow channels 3 0 8 a are sequentially filled. Quantitative flow path 3 0 8 a to 3 0 8 d and all other quantitative flow paths are filled with serum, then the number of revolutions is increased and the reagent reaction tank is centrifuged by centrifugal force 3 0 9 a to 3 0 9 d and other definitions The quantitative body fluid is pushed into the reagent reaction tank connected to the volume channel.

 By the way, if the necessary amount of blood can be reduced by reducing the number of reagent items, insert prosthesis 3 1 0 to reduce the volume of the separated serum part 3 0 2 as shown in Fig. 1 3 B. To do.

 Furthermore, an unnecessary reagent reaction tank is separated by discharging the curing material to a predetermined position of the distribution flow path 30 7 by using an injection method or the like and curing it to form a plug 3 1 1.

 The formation of the plug part 3 1 1 is preferable because the injection method makes it possible to form a plug part of any size in any place, such as a commercially available printer. It is.

 In addition, the number of test items can be increased or decreased by forming the state shown in Fig. 13 B, and even for blood test units that are mass-produced and fixedly formed, the required items can be tested. Can only be done. Industrial applicability

 According to the present invention, since the transfer of a very small amount of blood can be simplified, it becomes possible to sufficiently utilize a testing apparatus capable of measuring various blood components even with a very small amount of blood. In the evening type analysis unit, handling can be simplified.

 In addition, according to the present invention, blood component measurement can be realized without any special training, overcoming the problems in mass production of units that can be handled disposablely by individual patients, and stable measurement can be achieved. And can expand the blood measurement field.

 Furthermore, according to the present invention, even in a small amount, accurate blood measurement can be performed without waste, simplification of blood tests and easy health check of healthy persons can be achieved.

In addition, according to the present invention, the super-flux having a flow path configuration that is difficult to adjust. It is possible to provide a simpler blood test unit by expanding the range of use of the small blood analysis unit and reducing the cost of manufacturing the analysis unit.

Claims

1. For transferring and inspecting body fluid, comprising a body fluid impregnated portion that can be impregnated with body fluid by contact with the body fluid, and a support portion that supports the body fluid impregnated portion, A bodily fluid transfer tool characterized by having a shape and dimensions that can be accommodated in a bodily fluid test section of a bodily fluid testing device.

 Contract

 2. The bodily fluid transfer device according to claim 1, further comprising a gripping portion.

3. Body fluid transfer tool according to claim 1 or 2 that Ru features and to As range ¹ having a diluent reservoir releasable made et dilution when accommodated in humoral testing unit. Picture

 4. The body fluid transfer device according to any one of claims 1 to 3, wherein the body fluid is blood.

 5. The bodily fluid transfer device according to claim 4, wherein the blood is expressed on the skin surface.

 6. The bodily fluid transfer device according to any one of claims 1 to 5, wherein the bodily fluid impregnated portion contains a blood coagulation inhibitor.

 7. The bodily fluid transfer device according to any one of claims 1 to 6, further comprising a puncture device for bodily fluid expression.

 8. The bodily fluid transfer device according to any one of 1 to 7, wherein the bodily fluid inspection device is a low-humidity bodily fluid component inspection device.

 9. A body fluid collecting puncture device, a body fluid collecting puncture device, a body fluid impregnated portion that can be impregnated with the body fluid by contact with the body fluid, and a support portion that supports the body fluid impregnated portion. A bodily fluid inspection system comprising: a bodily fluid transfer device provided; and a bodily fluid inspection device to which the bodily fluid transfer device can be attached.

1 0. The body fluid testing device is a mouth fluid type body fluid component testing device. The body fluid test system according to claim 9, wherein

 1 1. The body fluid testing device includes a placement unit for the body fluid transfer tool, an extraction unit for extracting a test element from a body fluid impregnation unit of the body fluid transfer tool, a quantification unit for quantifying the extracted test element, and the quantification. The body fluid test system according to claim 9 or 10, further comprising a detection unit that reacts the test element quantified by the unit with the reagent component to obtain specific component information.

 1 2. The body fluid test system according to any one of claims 9 to 11, wherein the puncture device is movable up and down.

 13. The body fluid testing system according to any one of claims 9 to 12, wherein the body fluid is blood.

 1 4. In the blood reagent reaction measurement unit, which includes a reagent reaction system in which the serum after blood cell separation undergoes color reaction with multiple types of reagents and tests for multiple test items, the required blood volume is determined according to the required test items. A blood reagent reaction measurement unit characterized by having blood supply means that can be supplied under control.

 15. Stimulation means for applying a physical stimulus to a body fluid collection site, body fluid expression puncture means, body fluid absorption means abutting on the body fluid collection site for absorbing and impregnating body fluid exposed by the puncture means, and A bodily fluid examination system comprising: a measuring means for extracting bodily fluid from the bodily fluid absorption means and performing separation processing to measure biological information.

 16. The body fluid testing system according to claim 15, wherein the stimulation means is vibration means, suction means, or a combination thereof.

 17. The blood test system according to claim 15, wherein the puncture means is incorporated in the body fluid absorbing means.

 18. The body fluid test system according to any one of claims 15 to 17, wherein the body fluid is blood.

1 9. Operate fluid and measure optically while rotating the rotor A blood biometer, a standard tank containing a standard substance provided on the circumference of the blood biometer, and a variation in the optical path length of the standard tank. A bodily fluid inspection system comprising: a correction means that measures optical information such as a dimensional error by measuring the measurement.

 20. The body fluid test system according to claim 19, wherein the correction of the optical information is correction of a calibration curve.

 21. The body fluid testing system according to claim 19 or 20, wherein a plurality of the standard tanks are arranged at equiangular intervals on the circumference.

 2 2. The body fluid test system according to any one of claims 19 to 21, wherein the standard substance has a known concentration value.

 2 3. For optically measuring reagent reaction due to blood components, while rotating a rotary unit having many measurement reaction chambers arranged concentrically, and while rotating the rotary unit, In a blood test system equipped with a transmission type optical measurement means capable of optically measuring reagent reactions in a measurement reaction chamber sequentially,

 The rotating body unit includes a plurality of adjacent dummy windows on the optical path trajectory for measurement, controls the beam irradiation position of the light source based on the amount of light passing through the dummy window, and is always in the measurement reaction chamber. A blood test system characterized by irradiating measurement light.

 24. The dummy window according to claim 23, 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 unit. Blood test system.

25. The blood test system according to claim 23, wherein in the plurality of adjacent dummy windows, the individual dummy windows are arranged so as to be shifted in the circumferential direction.

26. The blood test system according to any one of claims 23 to 25, wherein there are three or more dummy windows.

 27. The blood test system according to claim 23, further comprising a light receiving portion corresponding to the dummy window.

 28. The method according to claim 8, 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 any one of 2 3 to 2 7.

 29. The blood test system according to any one of claims 23 to 28, wherein one or a plurality of the dummy windows are arranged for each of the rotating body units. .

 3 0. Body fluid detection system that obtains information such as component concentration from color reaction of body fluid components and reagents after separating body fluids by capillary force and centrifugal force and performing quantitative mixing with reagents. In

 A first reagent reaction tank having an input port for containing a first reagent and an output port for outputting a mixed sample solution of the first reagent to the outside;

 An input port for receiving a mixed sample solution supplied from the first reagent reaction tank; and a second reagent reaction tank having a configuration capable of measuring the color reaction from the outside. A body fluid inspection system characterized by comprising:

 31. The body fluid test system according to claim 30, wherein the color development reaction is measured by optical measurement.

3. 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. 1. The body fluid inspection system according to 1.

3. The body fluid test system according to claim 3, wherein the flow path, the first reagent reaction tank, and the second reagent reaction tank are formed on one row.

 3 4. In a humor testing system that measures blood color reaction values by performing blood cell separation, etc. on the rotating body at the blood operation section formed on the rotating body, and reacting the serum with the reagent.

 A bodily fluid test system further comprising a prosthesis for performing prosthesis in order to adjust the volume in the blood operation section.

 35. The bodily fluid examination system according to claim 34, wherein the prosthesis is for adjusting the amount of serum obtained in a blood cell separation region.