WO2007001084A1

WO2007001084A1 - Biochemical analyzer and carrier for biochemical analyzer

Info

Publication number: WO2007001084A1
Application number: PCT/JP2006/313341
Authority: WO
Inventors: Osamu Hamada; Hiroyuki Hasebe; Shigeo Yamashita
Original assignee: Kabushikikaisya Advance
Priority date: 2005-06-28
Filing date: 2006-06-28
Publication date: 2007-01-04

Abstract

This invention provides a biochemical analyzer comprising a carrier having a plurality of reaction sites showing a biochemical reaction and a plurality of reading parts for reading the biochemical reaction. The carrier and the reading parts are disposed so that they are in a mutually movable state and the spacing between the reaction sites on the carrier is different from the spacing between the plurality of reading parts. According to this biochemical analyzer, optical measurement in a plurality of reagent reaction tanks corresponding to a very small amount of body fluid can be realized in a proper and quick manner in a simpler measurement circuit, and a smaller-size and simpler apparatus, which can be put in a place closer to patients or healthy people, for example, in diagnosis of life-style related diseases, can be realized. Obtaining a proper accurate reference points in the measurement of multiple item sample component on a single carrier and obtaining an accurate sample position in the measurement of multiple item sample component on a single carrier can be realized.

Description

Biochemical analyzer and carrier for biochemical analyzer

Technical field

The present invention relates to a biochemical analyzer for measuring a carrier having a plurality of sites exhibiting a biochemical reaction, and a carrier used therefor. The present invention also provides

Background of the Invention Related to Liquid Mixing Methods and Devices Useful in Biochemical Analyzers

Recently, diseases related to lifestyle such as diabetes, cancer, and cerebral infarction are closely related to lifestyle requirements such as eating habits, stress, etc. There is a demand for an environment where components can be measured quickly and diagnosed in a number of ways, and where diagnosis is possible. In addition, this type of device that analyzes and diagnoses body fluids can be used at home or in places where there are no facilities. It is preferable to be able to diagnose. '

In biological component measurement, light is radiated to a reaction tank in which a body fluid such as blood, urine, sweat, etc., and an enzyme reagent are colored and reacted to receive reflected or transmitted light, and the received light is measured. By obtaining the absorbance, the electrolyte items, tumor markers, infection items, thyroid items, endocrine items, and other immune items, glucose, total cholesterol, In the component analyzer to be measured, it is necessary to electrically recognize the color development data of each reagent reaction tank when measuring a single carrier in which a plurality of reagent reaction tanks are arranged. There is a point.

However, there are many problems with conventional biological component measurement. For example, in biological component measurement, light is irradiated to a reaction tank in which a body fluid such as blood, urine, sweat, etc., and an enzyme reagent are colored and reacted to receive reflected or transmitted light, and the received light is measured. In a component analyzer that optically measures the concentration of dalcose, total cholesterol, creatinine, low-density lipoprotein, and total bilirubin component by determining the absorbance, Japanese Patent Application Laid-Open No. 5-2009836 As shown in the official gazette, the received light is separated into RGB three primary colors and the light intensity is obtained from each light, or the reaction tank is irradiated with the light previously separated into the three primary colors and transmitted or reflected. A technique is used in which the absorbance is obtained from the received light of the three primary colors.

It was necessary to consider the following points regarding the equipment used as diagnostic information by obtaining multiple component values by such optical measurement.

(1) The absorbance of each reaction vessel may be output as time-series data while rotating a single carrier in which a plurality of reagent reaction vessels are arranged. In this case, it is necessary to accurately detect the base point in one circle in order to identify multiple reaction vessels. In the past, it was necessary to provide a means for mechanically, electrically, and optically detecting this base point separately from the means for measuring the absorbance of the reaction vessel.

(2) When the biochemical analyzer is driven by a smaller amount of sample, and from the sample supply to the optical measurement automatically, the optical reaction is caused by mixing bubbles in the reagent reaction tank. Destabilization of mechanical measurement became a problem

(3) In optical measurement, it is preferable that there is no irregular reflection part in the optical path, and effective irradiation of light to the site where the specimen and the reagent have reacted is desired.

(4) When trying to measure multiple components of biological components with a small amount of sample, the amount of sample used to measure each item becomes smaller and the carrier to be calibrated The effects of small manufacturing errors, burrs that occur in the transmission optical path, or movement errors of the carrier or optical measurement head, movement errors at times, light absorption by materials, and diffuse reflections are very large. Become.

In addition to this, in addition to the above-mentioned Japanese Laid-Open Patent Publication No. 5-2 0 9 8 3 6, the Japanese National Patent Publication No. 10-0-5 1 0 3 62, Japanese Laid-Open Patent Publication No. 3-2 5 3 5 1 No. 2, Japanese Laid-Open Patent Publication No. 2 0 0 3 —2 0 7 4 5 4, Japanese Laid-Open Patent Publication No. 5 —2 4 0 8 6 9, and the like.

The points pointed out above are explained in more detail as follows. -

'' After receiving multiple lights from one reaction tank at the same time, or after receiving the light and splitting it into the three primary colors, each light is subjected to photoelectric conversion to form parallel electrical signals and these parallel signals Therefore, a circuit configuration such as a multiplexer for converting to a serial signal string is required.

When multiple light beams are transmitted through a single reaction tank, if the diameter of the reaction tank is reduced, the position and size of the light source are limited, and a more precise condensing unit is required, which is expensive and cumbersome. Will come along.

Use of a multiplexer that requires a timing signal obtained by using a clock signal, etc. cannot be switched at an optimal time, and delays and distortion occur in the waveform, compared to when the reaction of the reaction vessel is fast. In some cases, it may not be possible to detect all of the spectral signals required at the same time.

In addition, adding a circuit for performing such processing increases the complexity of the device itself, requires an expensive semiconductor chip such as a microcomputer having a larger processing capability, and the size of the device itself. It also affects the price and is not suitable for realizing a device that is close to the patient, such as diagnosis of lifestyle-related diseases. Japanese National Standard Heisei 1 0-5 1 0 3 6 2 discloses that a reference substance such as water is placed in a reaction tank of blood and a reagent to form a reference tank, and is based on the wavelength of light transmitted through the reference tank. It describes that the light obtained through the reagent reaction tank is calibrated.

The use of the reference substance shown in the Japanese National Standard Heisei 10-5 1 0 3 6 2 publication must be able to reliably detect the color development reaction between the body fluid and the reagent as long as it does not interfere with the measurement. In addition, it is often necessary to pay attention to preservability.

Japanese Patent Application Laid-Open No. 3-25315 1 describes that light that has passed through detection of bubbles mixed in a nozzle-shaped reagent reaction vessel is photoelectrically converted and then differentiated and detected. However, in the optical detection in a reagent reaction tank having a smaller measurement surface and moving instantaneously, there is no description of a method for determining a necessary measurement region. 'Japanese Laid-Open Patent Publication No. 2 0 0 3-2 0 7 4 5 4 describes that the surface of the chip is painted black for measurement of transmitted light.

In addition, in order to stably measure the transmitted light, a device such as applying a black paint with absorptivity is disclosed, but in fact, the light from the light source at the boundary between the transmitted light measurement part and the black part is disclosed. Leakage becomes a problem.

In addition, errors contained in the received light signal prevent accurate component analysis and reduce the overall analysis capability of the device.

In addition, in these biochemical analyzers, the temperature must be kept constant at around 37 ° C to 38 ° C in order to effectively and effectively react with the reagents. As a technique for that purpose, a means for heating the carrier itself by operating an electric heater using a nichrome wire or the like in a heat insulating space is used.

By the way, Japanese Patent Application Laid-Open No. 2 0 0 1 — 2 6 4 3 3 7 discloses a sample and a reagent. By arranging a number of containers with etc. on the turntable, irradiating each container with a halogen lamp etc. and heating it, and measuring the temperature of the heated container at the opposite part on the turntable, It is described that the container is maintained at a constant temperature. However, this method of heating the entire container requires a sufficiently large heating lamp, which increases power consumption.

Further, in these biochemical analyzers, a carrier that detects a minute amount of a sample by forming a channel on a mouth or sheet-like carrier uses a smaller amount of sample, and has a minute space. Therefore, it is often not easy to mix liquid and solid by simply mixing them, and some kind of stirring configuration is required. In addition, it is necessary to store the diluted solution stably and prevent leakage to the outside. Furthermore, in order to prevent the specimen from leaking out, it is desired to simplify the mechanical coupling between the carrier and the reading device. '

By the way, in US Pat. Nos. 5, 1600, 702, and JP 10-0500 1340, both of them describe a disk-shaped body fluid analyzer, and the capillary force, Using centrifugal force, blood cell separation, quantitative dilution, and quantitative distribution are performed, and plasma components are quantitatively supplied to multiple reagent reaction tanks to cause color reactions, and individual color values are measured externally. The analysis is described as being performed.

In addition, JP 7-0500 7 9 4 discloses that a dilution container is arranged in the center, and dilution is performed by utilizing a deviation that occurs when the rotor is mounted on the core material that fixes the low angle. A configuration for breaking the container is described.

Further, U.S. Pat. No. 5,160,702 describes a connection configuration and a chucking configuration between a rotor and a rotating device.

However, the methods described in these patent documents are not simple configurations, such as adopting a complicated configuration in order to achieve a more robust connection. hard.

Furthermore, reducing the burden on patients by reducing the amount of collected body fluid is an important factor in diagnosis at home as well as in medical facilities such as hospitals. If measurement is possible with a small amount of sample, the carrier for measurement becomes smaller and the analyzer becomes smaller.

Recently, an increasing number of hospitals, institutions, and organizations use a general-purpose public network such as the Internet as a means of communication to perform health checks through self-collection. The Internet explains the blood collection and transportation process in an easy-to-understand manner, and then collects blood by itself and transports it to the hospital for measurement of blood and body fluid components. This is because it can be checked. However, the system including actual blood transport is time-consuming and extremely complicated because it is necessary to prepare a cold storage environment in advance.

In the situation of body fluid analysis in medical treatment, including at home, simplification of the body fluid analysis system, simplification of diagnosis, and speeding up are required to promote the reduction of body fluid collection. Regarding such a method, for example, JP 2 0 0 1 ^ 5 1 0 5 6 8, JP 2 0 0 1 — 1 6 5 9 3 9, JP 9 1 4 7 5 9 3 Please refer to gazettes.

Miniaturization of specimens is preferable for patients and collectors, and the miniaturization of carriers and analyzers that can be used in a wide range of applications at home and outdoors. In an environment where the space for mixing solids such as specimens and reagents is narrower, it is difficult to perform stirring operations, and it is necessary to deal with actions that have not been regarded as problematic so far, such as viscosity, capillary force, static electricity, etc. It becomes. Especially when mixing solids such as reagents and liquids such as plasma, the difference in specific gravity is large and difficult. It is.

Also, when oxygen is required for a chemical reaction, the reaction space is narrow, and when optical measurement is performed in that space, the oxygen supply method becomes a problem. Disclosure of the invention

The present invention has been completed in view of the problems and problems of the prior art as described above. The present invention can be roughly classified into the following four inventions.

Invention of cord 1

The first invention is

(1) a carrier having a plurality of reaction sites exhibiting a biochemical reaction, a plurality of reading units for reading the biochemical reaction, and the carrier and the reading unit are movable with respect to each other, and the carrier By adopting a combination configuration in which the interval between the reaction sites and the interval between the plurality of reading units are different, the configuration is simple and the measurement process is improved.

(2) To define the shape of a special identification tank for extracting the base point on the carrier using means for measuring the absorbance of the reaction tank without providing a separate base point detection means, and to extract it reliably. In other words, a carrier having a plurality of reaction sites showing a biochemical reaction, a reading means for reading the biochemical reaction, a detecting means for detecting the information at a predetermined time, and the detecting means An optical unit in the reagent reaction tank has a combined configuration including a calculation unit that calculates a predetermined number of the obtained information for a predetermined time and a determination unit that determines a reference part from the signal output from the calculation unit. This makes it possible to detect a more accurate reference position without being confused with information.

(3) A change amount converter that converts biochemical signals into signals indicating the amount of change. The combination of the measurement range determination means for determining the measurement range from the signal obtained by the change amount conversion means allows a plurality of reagent reaction vessels to move at a predetermined speed, so that the plurality of reagent reaction vessels When measured at regular intervals, the effective measurement area can be determined instantaneously, enabling efficient component measurement.

(4) A carrier comprising a translucent member provided with a reagent reaction tank, the reagent reaction tank supplied with the sample is irradiated with measurement light from the outside, and the light obtained through the reagent reaction tank is received to receive the sample. In a biochemical analyzer for measuring a component, an absorbing member that absorbs light having a constant window is disposed in a direction of an irradiation surface that irradiates measurement light to the reagent reaction tank, and the area of the measurement window is the reagent. By making it smaller than the area of the measurement light irradiation surface of the reaction tank, it is possible to prevent light from leaking from parts other than the reagent reaction tank and to secure a measurement area with few errors.

(5) A carrier composed of a translucent member provided with a reagent reaction tank, the reagent reaction tank supplied with the sample is irradiated with measurement light from the outside, and the light obtained through the reagent reaction tank is received to receive the sample. In a biochemical analyzer for measuring a component, by providing a reference portion for permeation measurement in the carrier, signal drift caused by an electric circuit mixed in a received light signal or due to uneven manufacturing of the carrier This makes it possible to obtain accurate data.

Here, the present invention is summarized as follows. ,

1. a carrier having a plurality of reaction sites showing a biochemical reaction, a plurality of reading units for reading the biochemical reaction, and the carrier and the reading unit are movable with respect to each other, and on the carrier A biochemical analyzer arranged such that an interval between reaction sites is different from an interval between the plurality of reading units.

2. The interval between the reading sections is the interval between reaction sites on the carrier. The biochemical analyzer according to 1 above, which is different from an interval multiplied by an integer.

3. The biochemical analyzer according to 1 above, wherein the reaction site is a site that causes a color reaction of a body fluid such as blood or urine according to a component.

4. The biochemical analyzer according to 1 above, wherein the carrier has a disk shape, and the reaction sites are arranged on the outer periphery at equal intervals.

5. A carrier having a plurality of reaction sites showing a biochemical reaction, biochemical reaction information acquisition means for obtaining biochemical reaction information from a plurality of reaction sites of the carrier, and acquiring the biochemical reaction information at a predetermined time Detecting means for detecting biochemical reaction information obtained from the means; computing means for computing a predetermined number of information obtained by the detecting means for a predetermined period of time; serving as a reference from a signal output from the computing means A biochemical analyzer consisting of judging means for judging the part.

6. A storage unit that temporarily stores information obtained by the biochemical reaction information acquisition unit is provided, and when determining a reference site, data is read from the storage unit for determination. Chemical analyzer.

7. The biochemical analyzer according to 5 above, wherein the reaction site is arranged in a state having an orbit, and includes a slit in a part thereof, and the non-light-absorbing region is a reference region.

8. The biochemical analyzer according to 5 above, wherein the predetermined time is a predetermined time ahead of the central time.

9. The biochemical analyzer according to 5 above, wherein the read information is an electrical signal relating to a color reaction between a reagent and a body fluid.

10. A biochemical analyzer having a change amount conversion means for converting a biochemical signal into a signal indicating a change amount, and a measurement range determination means for determining a measurement range from the signal obtained by the change amount conversion means.

1 1. The biochemical analyzer according to 1 0, wherein the signal indicating the amount of change is a differential signal. 1 2. The biochemical analysis means according to 10, wherein the measurement range is between peaks of the signal indicating the amount of change.

1 3. The biochemical signal is a carrier in which a plurality of reagent reaction tanks that perform a color reaction between a reagent and a specimen are arranged at equal intervals, and the reagent reaction tank is irradiated with measurement light from the outside to be reflected or reflected. 10. The biochemical analyzer according to the above item 10, which measures biochemical components by measuring transmitted light.

1 4. A carrier in which a plurality of reagent reaction vessels are arranged on the same orbit, a measurement unit for optically measuring the components in the reagent reaction vessel, and the measurement unit and the carrier move relatively. The biochemical analyzer according to the above 10, which is a biochemical analyzer that measures the amount in each of the reagent reaction tanks.

1 5, a reagent reaction tank detection means for detecting a part of the reagent reaction tank, and an interval of the parts detected by the reagent reaction tank detection means is a predetermined interval or more. 15. The biochemical analyzer according to 14 above, further comprising reagent reaction vessel site determination means for determining a predetermined interval as a site of the reagent reaction vessel when the measured value is 11 force or more.

1 6. A carrier composed of a translucent member provided with a reagent reaction tank, the reagent reaction tank supplied with the sample is irradiated with measurement light from the outside, and the light obtained through the reagent reaction tank is received to receive the sample. In a biochemical analyzer that measures components, the reagent reaction. Absorbing members such as a film that absorbs light, a printed surface, and a painted surface are provided in the direction of the irradiation surface that irradiates measurement light to the tank. A biochemical analyzer that is disposed and has an area of the measurement window smaller than an area of the measurement light irradiation surface of the reagent reaction tank.

17. The biochemical analyzer according to claim 16, wherein the area of the measurement window is smaller than the area of the irradiation surface of the reagent reaction tank so that the measurement light passes only through the central portion of the reaction layer. .

1 8. Biomass according to 16 above, wherein the measurement window is formed in a concave shape. Scientific analysis equipment.

1 9. A carrier consisting of a translucent member having a plurality of reagent reaction vessels, and the reagent reaction vessel to which the sample is supplied is irradiated with measurement light from the outside by relative movement, and is arranged on the orbit of the measurement light. A biochemical analyzer that receives light obtained through a reagent reaction tank and measures a sample component, wherein the carrier is provided with a reference site for permeation measurement.

2 0. The above, wherein the reference region is one or more of a black surface, a through-hole, a 'reference liquid tank, an empty reagent reaction tank, a dilution liquid tank, a measurement sample (plasma, etc.), and a sealed tank. 19 The biochemical analyzer according to 9.

21. The biochemical analyzer according to 19 above, further comprising calibration means for performing offset calibration based on a light reception signal when the reference site is black.

As can be easily understood from the following detailed description, the present invention can form an input electric signal by simply mixing a color signal obtained spectroscopically without requiring a special circuit configuration. Reading can obtain individual spectroscopic data just by taking the timing from the rotation speed and array position, and therefore, it is possible to perform rapid signal processing, etc., although it has a simpler configuration. Has an effect. -In the present invention, a predetermined reference position can be set on a carrier simply by providing a through hole having a specific shape in the arrangement of reagent reaction vessels. In addition to simplification, an accurate reference position can be detected.

In the present invention, when the color development reactions in a plurality of reagent reaction vessels are optically continuously measured over time, the biochemistry over multiple items can be performed more quickly by grasping the accurate measurement region based on the differential signal. The component can be measured. The present invention enables stable optical measurement even in smaller reagent reaction vessels, and enables automatic and simple biochemical component measurement. Second invention:

According to a second aspect of the present invention, there is provided a heating means for heating a part of one surface of the rotating carrier, a temperature measuring means for measuring a portion facing the portion of the heating means, and a temperature measured by the temperature measuring means. On the basis of this, the combined configuration of the control means for adjusting and controlling the heating amount of the heating means enables accurate temperature control while using the heating means with less power consumption.

Here, the present invention is summarized as follows.

1. a heating means for heating a part of the carrier, a temperature measuring means for measuring a portion facing the portion of the heating means, and the heating means based on the temperature measured by the temperature measuring means A biochemical analyzer consisting of a control means that adjusts and controls the amount of heating. '

2. The biochemical analyzer according to 1 above, wherein an endothermic member is disposed on the other surface of the carrier.

3. The biochemical analyzer according to 1 above, wherein the heating means is a halogen lamp.

4. The biochemical analyzer according to 1 above, wherein the carrier performs exercise having regularity.

5. A heating means for heating a part of the carrier, a temperature measuring means for measuring the surface of the carrier, and a heating amount of the heating means is adjusted and controlled based on the temperature measured by the temperature measuring means. A biochemical analyzer comprising: control means for performing heating by the heating means; and performing the temperature measurement means at different timings.

As can be easily understood from the following detailed description, the present invention can further reduce the consumption of electric energy in a body fluid analyzer that can measure body fluid components in a more compact and multi-functional manner. To reduce power consumption and reduce size.

Third invention:

The third invention is (1) After supplying the specimen, the carrier is arranged to be processed to perform a plurality of examinations, and a dilution member for diluting the specimen is arranged vertically movable in the carrier. When the diluting member moves downward, the diluting member is arranged on the lower side of the diluting member to prevent the leakage of diluting liquid when not in use. Realizes stable storage of liquids.

(2) After supplying the specimen, it is processed and processed, and a part of one or more of the side, top, or bottom of the carrier placed in a state for performing a plurality of tests, Alternatively, an annular concavo-convex member formed entirely of continuous concavo-convex portions, and a combination of a vibration member that vibrates a portion requiring stirring of the carrier when contacting the annular concavo-convex member. By applying vibration, it is possible to mix the reagent and specimen sufficiently.

(3) After supplying the specimen, the carrier is processed and arranged in a state for performing a plurality of examinations. The carrier is contained in the carrier and contained in the portion requiring stirring. Due to the combined structure of stirring members that are deformed inward by the rotation of-, sufficient mixing of the reagent and the sample is achieved with only centrifugal force.

'(4) After supplying the specimen, process it' and place it in a state for performing a plurality of examinations.Rotating body for rotating the carrier, The rotation of the back surface of the carrier A metal member disposed at a site in contact with the body; a friction member that forms a contact surface between the rotating body and the carrier; and a magnetic member that provides magnetic coupling to the metal member in a non-contact manner. While the carrier can be easily mounted on the rotating body, the coupling between the two is strong, and a chucking configuration that can be easily removed is realized.

Here, the present invention is summarized as follows.

1. After supplying the sample, it is necessary to process it and perform multiple tests. In the carrier arranged in a state, a dilution member for diluting the specimen is arranged vertically movable in the carrier, and when the dilution member moves downward, an opening state is formed in the downward direction of the dilution member. A carrier for a biochemical analyzer comprising an opening member.

2. The biochemical analyzer carrier according to 1 above, wherein the diluting member is housed in the carrier via a pressable sheet member such as a bellows.

3. The dilution member has a configuration in which an opening surface of a cup member containing a diluent is covered with a thin film sheet, and the opening member is formed by a biochemical analysis formed by a puncture device capable of puncturing the thin film sheet. Device carrier.

'4. After supplying the specimen, process it and place it in a state for performing multiple tests. One or all of the side, top, or bottom of the carrier are placed on the side, top, or bottom. A biochemical analyzer comprising: an annular concavo-convex member formed by forming continuous concavo-convex portions; and a vibration member that contacts the annular concavo-convex member and vibrates a portion requiring stirring of the carrier.

5. In a carrier placed in a state for performing a plurality of examinations by supplying a specimen after supplying a specimen, the carrier is accommodated in a portion of the carrier that requires stirring, and is rotated inward by rotation of the carrier. Biochemical analyzer consisting of a stirring member that transforms into ..

6. After supplying the specimen, a processing operation is performed and a carrier arranged in a state for performing a plurality of examinations, a rotating body for rotating the carrier, and a part in contact with the rotating body on the back surface of the supporting body A biochemical analysis apparatus comprising: a metal member disposed on the surface; a friction member that forms a contact surface between the rotating body and the carrier; and a magnetic member that provides magnetic coupling to the metal member in a non-contact manner.

7. The biochemical analyzer according to 6 above, wherein a horizontal contact surface between the carrier and the rotating body is a friction member provided on the rotating body and a bottom surface of the carrier. 8. The biochemical analyzer according to 6 above, wherein the metal member is embedded in a bottom surface of the carrier.

As can be easily understood from the following detailed description, the present invention can facilitate the handling of the diluent while ensuring the storage stability of the diluted solution. In addition, the sample and the sample can be agitated by a simple method. Easily connect the carrier and the operating device, while having the effect of strong coupling, etc., so that multiple components can be tested from a small amount of sample on a single carrier. In this case, it is possible to construct a simple and simple carrier.

Fourth invention:

'' In the fourth invention, when mixing different substances, the centrifugal force does not occur in a relatively short time, and the necessary acceleration is increased over time to a given time, and then the opposite direction is reached. In a relatively short period of time, separation of the center does not occur, and the necessary acceleration is increased over time to a given time, and this is repeated until the difference in specific gravity is large. Also realized easy mixing.

In the present invention, it is sufficient that the liquid in the minute space to be mixed is given acceleration in one direction or alternately in the other direction periodically and intermittently. Rotational drive, linear drive, furiko drive, etc. can be used. Furthermore, the present invention is a method for mixing substances having different specific gravities arranged in the direction of the outer peripheral edge on the rotating body, and for supplying the quantitative sample to the measurement unit for measuring the result. A quantification supply channel extending in the circumferential direction, a finite first recovery channel extending in the circumferential direction, and a second recovery channel extending in the circumferential direction. On a carrier that performs various rotations and movements by providing a recovery channel that consists of a recovery channel and a connecting channel that connects the second recovery channel and that connects to the quantitative supply channel and recovers surplus samples. , The solution to be measured and the extra sample solution, etc. It was realized to be independent without leaking.

Furthermore, the present invention is a part for optical measurement, and in the part where the reagent and the sample are mixed, an air reservoir is formed in the central direction of the rotating body, so that optical measurement using transmitted light or the like is not hindered. In addition, a carrier that can sufficiently cope with reactions that require oxygen has been realized.

Further, the present invention is a flow path having a capillary force, and at least from the input port, the output port has a linear portion parallel to the diameter, or forms a flow channel extending in the circumferential direction. As a result, the movement and stoppage of the liquid was realized by adjusting the number of revolutions according to the cross-sectional area or length of the flow path without requiring a complicated flow path such as a so-called siphon.

In the present invention, the aerobic reaction tank has an elliptical shape or a gourd shape having a long axis in the central direction, so that the carrier is rotated and an air reservoir is formed in the central direction portion, thereby providing a stable measurement optical path. It can be secured.

Even if it is not oval or gourd, it may be sufficient to form a portion that protrudes slightly toward the center.

Here, the present invention is summarized as follows.

1. When mixing two or more different substances in a minute space, centrifugation does not occur in a relatively short period of time, and the rotation increases over time until the required acceleration is given for a predetermined time. Liquid mixing method in which angular acceleration is applied so that (positive acceleration) or decreases (negative acceleration).

2. A carrier having a micro space for mixing two or more different substances, and a rotational speed at which the carrier is not centrifuged in a relatively short time and a necessary acceleration is given for a predetermined time. A liquid mixing apparatus comprising driving means for applying angular acceleration to the carrier so as to increase or decrease rotation over time.

3. When mixing substances with different specific gravity in a minute space, Centrifugation does not occur in a short time, and after increasing the number of revolutions over time so that the required acceleration can be given to the substance for a specified time, centrifugation does not occur in the opposite direction in a relatively short time. 2. The liquid mixing method according to 1 above, wherein the acceleration is increased over time to a rotational speed that can be given for a predetermined time, and this is repeated.

4. A carrier having a mixing section for mixing substances having different specific gravities, and a rotation speed at which the support is rotated so that centrifugal separation does not occur in a relatively short time and a necessary acceleration is given to the substance for a predetermined time. In the opposite direction, centrifugal separation does not occur in a relatively short time, and the necessary acceleration for the substance is increased over time until the rotation speed is given for a certain period of time. 2. The liquid mixing apparatus as described in 2 above, which has a rotating means for repeating this.

5. When mixing two or more substances in a minute space in the carrier, centrifugal separation does not occur in a relatively short time, and a driving means for driving the carrier to give the substance the necessary acceleration for a predetermined time is provided. Biochemical analyzer with

6. The liquid mixing method and apparatus according to any one of 1 to 4 above, wherein the number of rotations is 2 000 rpm or less.

7. The liquid mixing method and apparatus according to any one of 1 to 4 above, wherein a time from the maximum rotational speed in one direction to the maximum rotational speed in the opposite direction is 0.5 to 2 seconds.

8. A measuring unit that mixes substances with different specific gravity arranged in the direction of the outer peripheral edge on the rotating body and measures the reaction state and results such as absorbance, and a quantifying unit for supplying a quantitative sample to the measuring unit A flow path for supplying a sample to the quantification unit, a quantitative supply flow path extending in the circumferential direction, a limited first collection flow path extending concentrically, and another collection flow path, and the first collection flow path. It consists of a flow path and a connecting flow path connecting the other recovery flow paths mentioned above and is in contact with the quantitative supply flow path. A carrier for a biochemical analyzer comprising a recovery unit for recovering surplus samples.

9. The carrier for a biochemical analyzer according to 8 above, wherein the connection part of the first recovery channel and the second recovery channel of the connection channel is formed with an acute angle.

10. The carrier for a biochemical analyzer according to 8, wherein the measurement unit and the quantification unit are connected by a flow path extending in a circumferential direction.

11. The carrier for a biochemical analyzer according to the above 8, wherein an air reservoir is formed in a central direction in the measurement unit.

1 2. The carrier is not centrifuged in a relatively short time, and the required angular acceleration is increased over time to a value that can be given for a predetermined time- 8. The method according to 8 above, further comprising a rotating device for increasing the rotational speed over time so that the required angular acceleration can be given for a predetermined time without repeating the centrifugation in a relatively short time in the direction, and repeating this. Carrier for biochemical analysis equipment.

1 3. A flow path having a capillary force, in which at least the output from the input port has a linear portion parallel to the diameter, the liquid is moved and stopped by adjusting the rotation speed of the carrier. Carrier for chemical analysis equipment.

1 4. Biochemical flow that has a capillary force, and that moves and stops the liquid by adjusting the number of rotations of the carrier with a configuration in which the calorie that exits at least from the input port extends in the circumferential direction. Carrier for analyzer. ~-As can be easily understood from the following detailed description, the present invention is capable of quantifying a very small amount of sample, mixing reagents of different specific gravity such as reagents, and adjusting the rotation speed and rotation direction. This makes it possible to easily perform body fluid tests, and to realize body fluid diagnosis in a wider area. Brief Description of Drawings

FIG. 1A and FIG. 1-B are schematic diagrams showing a preferred embodiment of the present invention, respectively. FIG. 2 is a waveform diagram showing the operation of one preferred embodiment of the present invention.

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FIG. 3 is a waveform diagram showing the operation of one preferred embodiment of the present invention.

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Fig. 4 is an enlarged cross-sectional view along line X-X 'in Fig. 1A.

FIG. 5 is a cross-sectional view showing another preferred embodiment of the present invention.

V,

FIG. 6 is a circuit diagram showing the operation of one preferred embodiment of the present invention.

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FIG. 7 is a perspective view showing a preferred embodiment of the present invention, and FIG. 8 is a circuit diagram showing the operation of another preferred embodiment of the present invention.

FIG. 9 is a waveform diagram showing the operation of another preferred embodiment of the present invention.

FIG. 10 is a circuit diagram showing the operation of another preferred embodiment of the present invention.

FIGS. 11A and 11B are schematic cross-sectional views showing another preferred embodiment of the present invention, respectively.

FIG. 12 is a waveform diagram showing the operation of the cold application shown in FIG.

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FIG. 13 is a circuit diagram showing the operation of one preferred embodiment of the present invention,

FIG. 14 is a waveform diagram showing the operation of the embodiment shown in FIG.

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FIG. 15 is a schematic diagram showing another preferred embodiment of the present invention,

Fig. 6 is a cross-sectional view along the line X-X 'in Fig. 15; FIG. 17 is a circuit diagram showing the operation of another preferred embodiment of the present invention.

FIGS. 18A to 18C are enlarged sectional views respectively showing another preferred embodiment of the present invention.

FIG. 19 is a perspective view showing another preferred embodiment of the present invention,

FIG. 20 is a waveform diagram showing the operation of another preferred embodiment of the present invention,

FIG. 21 is a schematic diagram illustrating another preferred embodiment of the present invention.

FIG. 2 2 is a perspective view showing one preferred embodiment of the present invention, FIG. 2 3 is a perspective view explaining the operation of one preferred embodiment of the present invention,

FIG. 24 is a cross-sectional view taken along the line segment 'in FIG. 23, and FIG. 25A and FIG. 25B are perspective views showing a preferred embodiment of the present invention, respectively. And

FIG. 26A is a circuit diagram showing the operation of one preferred embodiment of the present invention,

FIG. 26B is a schematic diagram showing an example of a drive circuit for the heat source shown in FIG. 26A. FIG. 27 is a circuit diagram showing the operation of one preferred embodiment of the present invention. Yes,

FIG. 28 is a waveform diagram showing the operation of a preferred embodiment of the present invention.

FIG. 29 is a graph plotting the relationship between time and voltage in one preferred embodiment of the present invention,

FIGS. 30A to 30C are each a preferred embodiment of the present invention. It is sectional drawing which shows an example,

FIG. 3 1 is a perspective view showing one preferred embodiment of the present invention, FIG. 3 2 is a schematic view showing one preferred embodiment of the present invention, and FIGS. 3 3 A to 3 3 C Each figure is an enlarged schematic view showing a preferred embodiment of the present invention.

FIGS. 3 4 A to 3 4 C are schematic views showing a preferred embodiment of the present invention, respectively.

FIGS. 35A and 35B are enlarged sectional views showing a preferred embodiment of the present invention, respectively.

FIGS. 36A to 36C are schematic views showing a preferred embodiment of the present invention, respectively.

FIGS. 37A and 37B are enlarged sectional views showing a preferred embodiment of the present invention, respectively.

FIGS. 38A to 38C are schematic views respectively showing a preferred embodiment of the present invention.

FIGS. 39A to 39E are schematic diagrams showing a preferred embodiment of the present invention, respectively. FIGS. 40.about.0 to 40.degree. C are respective changes in the rotational speed over time. Is a graph showing

FIG. 41 is a schematic diagram showing one preferred embodiment of the present invention, and FIGS. 4 2 and 4 2 are schematic diagrams showing one preferred embodiment of the present invention.

FIG. 43 is a schematic diagram showing one preferred embodiment of the present invention, and

FIG. 44 is a perspective view showing a preferred embodiment of the present invention. BEST MODE FOR CARRYING OUT THE INVENTION Subsequently, the present invention (first to fourth inventions) will be described with respect to preferred embodiments thereof, particularly with reference to the accompanying drawings. It should be understood that the present invention is not limited to the following embodiments. If necessary, the first to fourth inventions can be arbitrarily combined.

1st invention

• The present invention includes at least a carrier having a plurality of reaction sites exhibiting a biochemical reaction, a plurality of reading units for reading the biochemical reaction, and the carrier and the reading unit are movable with respect to each other. In addition, by having a combined configuration in which the intervals between the reaction sites on the carrier and the intervals between the plurality of reading units are different, a tabletop device can be easily realized, and body fluid components easily in various places Can be measured.

In the present invention, the biochemical reaction includes blood, urine, sweat, and other body fluids and reagents.

■ No

Examples are reactions that optically measure components related to the living body, such as color development reactions and fluorescence reactions utilizing immune responses.

Examples of reagents used to measure blood components include GPT, albumin, ALP, urea nitrogen (BUN), total protein, total pyrilvin, glucose, total cholesterol, GOT, and amylase in body fluid components. Enzymes for measurement are shown.

The carrier has a disk shape, a rectangular shape, or a sheet shape, and has a reaction tank containing or supplied with a reagent on the surface thereof arranged at regular intervals at an unspecified interval, and at least externally. Examples are those that have translucency in a region where photometry is possible.

On the carrier, there may be other parts such as a separation part that separates unnecessary blood cells for blood, and a quantitative supply part that supplies a certain amount of body fluid to the reagent reaction tank.

In the present invention, the plurality of reading units are the color development in the reagent reaction tank. It is only necessary to measure the color development information of the reagent, and a light source that outputs electromagnetic waves of visible light, ultraviolet light, infrared light, etc., such as lasers and light emitting diodes, and various lights output from the light source pass through the reagent reaction tank or Examples include a light receiving unit that receives light obtained by reflection and photoelectrically converts the light.

In addition, absorbance, colorimetry, and frequency components are measured from the obtained light, and it is only necessary to know how dark the color is developed and how the color value changes, and the signal processing configuration is also measured. It is adjusted appropriately depending on the subject.

The plurality of light sources need not be one, and examples include 2, 3, 4 or more light sources corresponding to the wavelength of the color spectrum of the reagent.

'A combination configuration in which the distance between the reaction sites on the carrier and the distance between the plurality of reading units in the present invention is different is, for example, that one light source irradiates light to one reading unit. In the evening measurement, the other reading units indicate that the color values in the reaction tank cannot be read.

It should be noted that all the reading units do not have to coincide with the position of the reaction tank. For example, in the state where the two reading units simultaneously obtain the coloring information in the reaction tank, the other reading units receive the coloring information. In some cases, it may be unreadable.

For example, the reading unit and the carrier need only be relatively moved, and the carrier is rotating or sliding on the stationary reading unit, or vice versa, and the stationary carrier. On the other hand, the reading part is shown rotating or sliding.

In the present invention, when the carrier is a rotating body, so-called low evening, the arrangement angle from the center of the reagent reaction tank is Θ, n is an arbitrary integer (n = l, 2, 3, 4,...), M is If the number of light sources (m = 1, 2, 3, ···), the arrangement angle K from the center of the measurement unit is

= θ X n-Θ / m It is represented by According to this equation, the size of the disk-shaped carrier, the arrangement position of the reagent reaction tank, and the position of the light measurement unit can be measured efficiently.

In the present invention, the biochemical reaction information includes visible or invisible color values, absorbance, frequency characteristics, etc. obtained by the reaction between the body fluid and the reagent. The biochemical reaction information acquisition means includes a reagent reaction. Examples include a combination of a light transmitting element and a light receiving element obtained by transmitting or reflecting through a tank, a combination of electromagnetic wave transmission and reception means.

The “predetermined time” of the detection means for detecting the biochemical reaction information obtained from the biochemical reaction information acquisition means at a predetermined time is, for example, two times at constant intervals before and after the center time T n. For example, as shown in FIG. 9 (c), four time intervals of tnl −; 6, tnl − α, tn 1 + α, tnl +; 6 are set for the time tn.

Further, “the biochemical reaction information obtained from the biochemical reaction information acquisition means is, for example, an amplitude value, a frequency component, etc. of a signal at a predetermined time after converting an optical output into an electrical signal. Either digital processing or analog processing may be used.

'In the case of Fig. 9 (c), for example, in the case of Fig. 9 (c), the "predetermined time" in the calculation means for calculating the information obtained by the detection means for a predetermined time and a predetermined number is the time It is a width and is a time width proportional to the size of the reference part, and the predetermined number only indicates the number of time intervals to be detected in this case, but is not limited to this. The “calculation means” includes, for example, multiplying or integrating the information obtained in the time interval.

The arithmetic means is exemplified by a logic gate if it is digital, and an analog arithmetic unit if it is analog.

The determination means for determining a reference part from the signal output from the calculation means is, for example, when there is an output of the calculation means at a predetermined time interval. For example, at time tn, an output indicating that the current position is the reference position or a case where the output of the calculation means exceeds a certain threshold at a predetermined time interval is exemplified.

The amount of change in the present invention indicates the amount of change in the electrical signal after the biochemical signal is converted into the electrical signal, and examples thereof include differentiation, integration signal, and other secondary differential signals.

In the present invention, a signal having a high peak is output at least when the photometric position between the reagent reaction tank and the optical unit is reached and when the photometric position has passed. Between the end of the high peak and the beginning of the last high peak, and during that time, when the peak of a certain amount of height appears, it is a state where unnecessary optical interference such as bubble contamination has occurred, By removing this part, an accurate measurement area can be recognized.

In the present invention, it is preferable to obtain the position of the reagent reaction tank from the light reception signal, but if the reagent reaction results in a very dark color and the amount of transmitted light is too small to detect the position of the reagent reaction tank, it is less. In both cases, the signal indicating the position of the reagent reaction tank that was detected before and the position of the reagent reaction tank that was detected next are calculated, and the part of the reagent reaction tank that could not be detected is predicted, and the information on that part is detected. It may be a thing. '

This is because the prediction range can be found if the reagent reaction chamber part of the chip and the rotation speed of the carrier are known in advance. In this case, since a reaction tank that cannot be measured will come out, it is more reliable to obtain the position of the reagent reaction tank that cannot be detected arithmetically from the position of the reagent reaction tank that can be detected as described above. Can be detected.

In the present invention, various reference parts are provided on a carrier, and the reference part is used as so-called calibration information or reference information. Factors that can cause calibration include light intensity error of light sources such as laser diodes and LEDs, sensitivity error of photodiodes, DC offset voltage caused by errors in electrical circuits such as amplifier circuits, and unevenness of materials forming the carrier. Uneven processing at the bottom of the reagent reaction tank, adhesive intervening on the interface between the carrier and the lid, diffuse reflection of light in the adhesive, refraction, absorption, individual differences in body fluid components, component differences in diluent, measurement component errors Etc. are exemplified.

For such error factors, for example, by adding the following configuration to the part corresponding to the optical measurement part of the carrier, the received light signal can be corrected ^ calibrated.

1. Place a black pattern with the same or larger area as the reagent reaction tank.

By measuring the black pattern optically, it is possible to measure the offset information generated in the amplification circuit, etc., and by removing this offset information from the optical information of the reagent reaction tank actually obtained, etc. Accurate component information can be obtained.

2. Form a through-hole equal to or larger than the reagent reaction tank.

By receiving the light output from the light source that has passed through the through-hole, the actual intensity, wave length, etc. can be known, so that the measured color value can be corrected. Note that the through hole may be used as a reference portion.

3. Place an empty reagent reaction tank.

In an empty reagent reaction tank, the state of measurement light due to processing irregularities at the bottom of the tank is measured, and it is possible to verify the measurement value that can obtain true optical information.

4. Also, by filling high-purity water, the bottom surface and top surface can be removed, and accurate calibration values such as uneven processing on the bottom surface of the reagent reaction tank can be obtained. The

5. Place a reagent reaction tank filled with diluent.

The absorbance of the diluted solution can be obtained and used to calibrate the actual color value.

6. Place a reagent reaction tank filled with plasma components. This is preferably the same as the plasma when plasma is supplied to other reagent reaction vessels.

The optical measurement of plasma alone can be used to measure the state of the subject's body, which changes every moment, and to calibrate the color value with the reagent.

These calibration target areas can be expressed by optical measurement results of transmitted light through the reagent reaction vessel containing only the respective media, for example, the size of the D value.

Penetrating light (0D value 0) <Air (diluent) <Plasma only <Plasma + Reagent reaction Black (∞) ''. The measured values of air (diluent) or plasma only are used to correct the intensity of the light source, the sensitivity deviation of the receiver, and the absorbance of the carrier itself. The black (completely shaded) part is used to correct the offset value (measured output value when there is no incident light) of the photoreceptor and the electrical circuit that amplifies its output.

'Note that the measurement in an empty reagent reaction tank is due to residual water vapor and clouding of the bottom, etc., so it is preferable to use a diluent having the same OD value when actually measured.

Example 1 — 1

1A and 1B show an embodiment of the present invention, and the present invention will be described in detail.

FIG. 1A is a diagram for explaining the combination relationship between a carrier in a state where the housing of the measuring device is omitted for explanation and the reading portion. FIG. B is a view of the carrier 10 viewed from above.

10 is a carrier, which is made of polyester, PMMA, PC, PS, PET, PDMS, glass, etc., and has a concave portion corresponding to a flow channel, reaction tank, etc. formed on the surface, and a sheet made of the same material from above. It has a shape in which the lid is bonded by pressure-sensitive adhesive, adhesive, or self-adsorption ability.

The carrier 10 is configured to perform the operation of separating the blood supplied to the center, mixing the diluent, etc., and supplying a fixed amount to the reaction tank based on the relationship between the centrifugal force generated by the rotation and the capillary force of the flow path. Illustrated.

In the case of blood, the configuration includes a blood cell separation chamber, a dilution / mixing chamber, plasma quantification, etc., but any configuration can be adopted, and the detailed configuration is omitted.

11 is a metal plate for joining with the reading device, and is preferably arranged so as to be partially embedded in the back surface of the carrier 10. A concave portion 1 1 ′ for inserting and fixing to the connecting shaft on the reading device is formed at the center through the joining metal plate 1 1 from the back side of the carrier 1 0 and partially through the carrier 1 0. Yes. .

1 2 is an example of the operation unit, and illustrates a mixing tank for a diluent and the like. The operation unit 12 is arranged in the outer circumferential direction of the carrier 10 0 by adjusting the capillary force and centrifugal force generated in the flow path and reaction tank in the carrier 10 by arbitrarily rotating and controlling the carrier Γ 0. In the reagent reaction tank row 15 a to 15 h, blood cells are separated, and a conditioned sample such as quantified plasma is supplied.

1 3 is a sample supply unit that supplies body fluids such as blood from the outside, and is composed of a concave liquid tank or flow path for the supply unit so that the sample does not leak to the outside as necessary. A lid may be provided.

14 is a distribution flow path, and is a flow path for supplying adjusted specimens to individual reagent reaction tanks 15 a to .15 h. 1 8 shows one of the supply channels, the distribution channel 14 and the respective reagent reaction tanks 15 15 For connecting to 5 h, a plurality of supply channels may be provided for one reagent reaction tank. In some cases, the volume of the supply channel 18 is a quantitative value of the processed specimen.

15 a to 15 h are examples of a reagent reaction tank, in which a target reagent is contained in a cylindrical recess in a dry, gel, or liquid state. For example, the size is about 1 mm in diameter and 3 mm in depth,

1 6 a to l 6 c are light sources that output three primary colors. For example, light source 1 6 a is a red R laser, and light source 1 6 b is a green G laser.

1 6 c shows a blue B laser.

1 7 a to 1 7 c are photoreceptors, and photodiodes, phototransmissions, etc. are used.

The distribution channel 14 and the reagent reaction tanks 15 a to 15 h are covered with a cover made of a translucent sheet such as polyacryl or PET when in use.

FIG. 1B is a view of the positional relationship between the reagent reaction tanks 15 a to 15 g shown in FIG. 1A and the light sources 16 a to 16 c as viewed from above.

The individual reagent reaction tanks are arranged at intervals of 15 degrees from the center 0 of the carrier 10 to the reagent reaction tank 15 a, and the light sources are arranged at intervals of 40 degrees with the light source 16 a as the center. Yes. .

Fig. 4 shows the relationship between the light source, the light receiving section, and the reagent reaction tank of the carrier. FIG. 4 is a cross-sectional view taken along a line Χ_Χ ′ in FIG. 1A. In Fig. 4, some of the readers omitted in Fig. 1A are also shown.

In FIG. 4, the same components as those in the embodiment shown in FIG. 1 are designated by the same reference numerals and the description thereof is omitted. In Figure 4,

Reference numeral 19 denotes a lid portion, which is formed so as to cover the flow path or the like of the carrier 10. The lid part 19 is composed of the distribution channel 14 shown in Fig. 1A, the supply channel 1 8 It covers the upper part of the reagent reaction tank 15a, etc., and is formed of a light-transmitting member for measurement by reflected light or transmitted light.

20 is a light-shielding portion, which is formed on the back surface of the carrier 10, and is mainly formed by covering or coloring a sheet formed in black or a color close to it, a light source, and a reagent reaction tank It is arranged other than the optical path through the passage hole between them.

The passage hole 25 may have an area smaller than that of the light source 16a to suppress reflected light and scattered light generated when light is irradiated from the light source to the reagent reaction tank.

2 1 is an electric lead wire on the light source side for electrically connecting the light source 16 a to the power source and the light source control circuit. For example, the electrical lead wire 21 is connected to the electrical connection wire 3 2 6 shown in FIG.

2 2 is an electric lead wire on the light receiving side for electrically connecting the light receiving body 17 a to the signal processing circuit.

2 3 is a measuring device lid, which is equipped with a light receiving element 17 a etc., for example, a part that can be moved to take out the carrier to the outside

24 is the carrier mounting part of the measuring device, for example, the light source 16 6a is inscribed so that it comes directly under the reagent reaction tank of the carrier, the carrier is placed, the motor that is chucked and rotated, etc. Is housed. The overall shape of the carrier mounting portion 24 is shown in FIG.

Next, FIG. 6 shows an example of a circuit configuration for processing signals received by the photoreceptors 17a to 17c shown in FIG. 1A.

In Figure 6,

3 1 0 a to 3 1 0 c are light sources of three primary colors, and correspond to the light sources 16 a to 16 c in FIG. 1A, for example.

3 1 1 schematically shows the reagent reaction tank on the carrier 10 shown in FIG. 1A. is doing. The carrier 10 shown in FIG. 1A rotates and each of the reagent reaction tanks passes through between the light source and the light receiving unit.

Reference numerals 3 1 2 a to 3 1 2 c denote light-receiving portions, which indicate a state in which an optical path is formed with each of the three primary color light sources 3 1 0 a to 3 i 0c. The light receiving unit is also a part that converts the received light signal into an electrical signal. The light receiving sections 3 1 2 a to 3 1 2 c correspond to the light receiving bodies 17 a to 17 c shown in FIG. 1A, respectively.

3 1 3 a to 3 1 3 c are composed of an amplifier circuit and filter circuit using an OP amplifier, etc., and are electrically connected to the individual light receiving parts 3 1 2 a to 3 1 2 c respectively. Amplify, filter, etc. to make it electrically processable.

3 14 is a mixing unit, which is mainly composed of an adder circuit, and the received light signals individually amplified by the amplifying units 3 1 3 a to 3 1 3 c are multiplexed on, for example, one signal line. It is a part for mixing. One

The mixing unit 3 14 is composed of an analog addition circuit using an operational amplifier or the like, for example.

-.3: 1 5 is a filter that passes the frequency band required for measurement in the received light signal and removes aliasing noise caused by sampling. -

3 1 6 is an A / D converter (AZD converter), which includes a sampling circuit, a quantization circuit, etc., and converts received light signals into digital signals.

3 1 7 is ROM, which stores programs, parameters, etc. for operating CPU 3 24 etc .:

3 1 8 is: R A M, which is a part for storing temporary data etc. during program execution.

3 1 9 is a display unit, a print interface, RS— 2 3 2 C, Monitor, Speaker, Wireless LAN interface, Infrared and other wireless output unit, Modem, etc. This part is for displaying, transmitting, and transmitting the obtained blood information.

3 2 0 is a bus, which is a transmission path for transmitting command signals, data signals, and the like used in CPU, ROM, RAM, and the like.

3 2 1 is a rotation control unit, which is a drive driver for rotating the carrier left and right or in a shifting manner. .

3 2 2 is a temperature control unit, and blood and reagents operate effectively at around 38 ° C. Therefore, the carrier is heated by controlling the heating of a heater such as a halogen heater to keep it constant. It is a circuit for keeping the temperature at

Reference numeral 3 2 3 denotes a drive unit that controls an electrical output for causing the light sources 3 1 0 a to 3 1 0 c to emit light. For example, when measurement is not required, the control is such that the electrical output to the light source is stopped.

3 2 4 is a CPU, which transmits control signals to the rotation control unit 3 2 1, temperature control unit 3 2 2, etc. via the bus 3 2 0 based on the program stored in R 3 This is to control the operation of the element.

3 2.5 is an electrical lead wire, which is formed by jumper wires, board wiring, etc., and has a configuration in which the filter 3 1 5 and the A / D converter 3 1 6 are electrically connected. .

3 26 is an electrical connection line, and has a configuration in which the individual light sources 3 10 a to 3 10 c and the drive unit 3 2 3 are electrically connected separately as described above. Next, the operation of the embodiment shown in FIG. 1A will be described in detail with reference to other drawings.

In Figure 1A,

Cover the specimen supply unit 1 3 with blood to supply blood and close the supply port. The lid is provided as required, and may not be necessary if the supply section has a smaller diameter.

The carrier 10 to which the specimen has been supplied is placed, for example, on the carrier mounting portion 24 of the measuring apparatus shown in FIG.

In Figure 7,

1 1 a is a rotating body, provided with a rotating shaft 1 1 b at the center, a concentric magnetic member, and a friction member 1 I d on the outer side.

When the concave portion 1 1 ′ of the carrier 10 is inserted into the rotating shaft 1 lb, the joining metal plate 1 1 of the carrier 10 and the magnetic member 1 1 c attract each other by magnetic force, but the friction member 1 1 d becomes the magnetic member 1 lc. Since the rotating body 1 1 a and the carrier 10 are strongly coupled with each other because they are in a non-contact state, the size of the reader shown in FIG. 7 is, for example, an accessory for a personal computer. The external or built-in type CD-ROM reader is shown.

In addition, a CPU, ROM, RAM, and a liquid crystal display may be directly incorporated in the reading device to make a stand-alone type.

When the measuring device lid portion 2 3 and the carrier mounting portion 24 are closed, the inside is in a state as shown in FIG. 1A.

The CPU 3 24 shown in FIG. 6 outputs control signals to the temperature control unit 3 2 2, the rotation control unit 3 2 1, and the drive unit 3 2 3, and controls the temperature of the carrier 10 shown in FIG. Adjust the rotation of the carrier while keeping it around.

The blood supplied to the center is controlled by the centrifugal force generated by the rotational force and the capillary force, and the blood cells are first separated by the blood cell separation unit. On the other hand, when the amount of blood is small, a dilute solution that has been sealed in advance is released from the sealed body for the dilution operation with effective physiological saline.

Furthermore, the centrifugal force generated by the rotation of the carrier 10 shown in FIG. Plasma obtained by separating blood cells by the action of capillary force generated by the miniaturization of the tract is mixed with the centrifugal force that changes the dilution.

The diluted plasma is quantitatively supplied to the individual reagent reaction tanks through, for example, the distribution channel 14 and the supply channel 18 shown in FIG. 1A by centrifugal force and capillary force generated by the rotational force.

In each reagent reaction tank, the diluted plasma fluid and the reagent are mixed, a color reaction occurs, and measurement of absorbance, etc. is started.

Depending on the reagent, the color development time varies, so it may be preferable to measure in order of color development.

First, the description starts when there is a reagent reaction tank 15a on the measurement optical path formed by the light source 16a and the photoreceptor 17a shown in FIG. '

C PU 3 2 4 shown in FIG. 6 drives the drive unit 3 2 3, and the light sources 3 1 0 a to 3 1 0 c output laser light by the drive of the drive unit 3 2 3.

Since the light source 1 6a shown in Fig. 1A and the photoreceptor 1 7a coincide with the transmission part of the reagent reaction tank 15 5a, the light emitted from the light source 1 6a is the reagent reaction tank 1 5 Passes through a and is received by photoreceptor 1 Ί a. For example, an electrical signal as shown by R 1 in Fig. 2 (a) is output from photoreceptor 17 a shown in Fig. 1A.

At this time, the light sources 16 b and 16 c shown in FIG. 1A are blocked by the light shielding portion 20 shown in FIG. 4, and the light receivers 17 b and 17 c receive the light. It is not in the state.

When the output light of the light source 3 1 0 a shown in Fig. 6 is received by the light receiving unit 3 1 2 a via the reagent reaction tank 3 Ί 1, the light receiving unit 3 1 2 a receives the received light as an electrical signal. Is amplified by the amplifying unit 3 1 3 a, and the signal shown in FIG. 2 (a) is output at the connection point 3 a. At this time, the output light of the light source 3 1 O b is blocked by the light blocking portion 20 shown in FIG. 4, and the light receiving portion 3 1 2 b does not receive the light from the light source 3 1 O b. At connection point 3b, there is no output as shown in Fig. 2 (b).

The output light of the light source 3 1 0 c is also blocked by the light shielding portion 20 shown in FIG. 4, and there is no output at the connection point 3 c shown in FIG. 6 as shown in FIG. 2 (c). .

The mixing unit 3 1 4 shown in FIG. 6 inputs the amplification signals of the individual amplification units 3 1 3 a to 3 1 3 c, but as shown in FIG. 2 (d), the amplification unit 3 1 3 b Only the light reception signal R1 from is output.

Next, when the carrier 10 shown in FIG. 1A rotates clockwise around the center point O,

The red laser light output from the light source 16a shown in FIG. 1A is blocked by the light shielding unit 20 shown in FIG. 4, and the green laser light output from the light source 16b shown in FIG. Pass through the inside of tank 1 5 e.

By this light transmission, the photoreceptor 17b receives the light through the reaction reagent; after it is converted into an electric signal, it is amplified by the amplification unit 3 1 3b shown in FIG. 6, and the amplification unit 3 1 3 The signal amplified at b is output to the mixing unit 3 14 as the signal G 5 shown in Fig. 2 (b) via the connection point 31). The other photoreceptors 1 7 a and 1 7 are blocked by the light output from the light sources 1 68 and 16 c, so there is no output from the light receivers 3 1 2 a and 3 1 2 c. The output of 3 1 4 is the signal of G 5 only.

Next, when the carrier 10 shown in FIG. 1A rotates clockwise around the center point 0,

The green laser light output from the light source 16 b shown in FIG. 1A and the red laser light output from the light source 16 a are blocked by the light shielding portion 20 shown in FIG. 4, and the light source 16 c shown in FIG. 1A The blue laser light output from the reagent reaction Pass through the inside of tank 1 5 h.

Photoreceptor 17 c receives the light that has passed through the reaction reagent and converted it into an electrical signal, which is then amplified by amplification section 3 1 3 c shown in FIG. 6 and the signal that appears at connection point 3 c 2 The signal B 1 0 shown in Fig. 2 (c) is output to the mixing unit 3 1 4. The other photoreceptors 1 7 b and 1 7 a shown in FIG. 1A have the light receiving parts 3 1 shown in FIG. 6 because the light output from the light sources 16 b and 16 a is blocked in the same manner as described above. 2 b and 3 1 2 a have no output, and as shown in FIG. 2 (d), the output of the mixing unit 3 14 is only a signal of B 1 0.

By repeating the rotation as described above, the output of the mixing section 3 14 that appears at the connection point 3d becomes a single signal sequence as shown in FIG. 2 (d).

The output of the mixing unit 3 14 shown in FIG. 6 is extracted by the single filter 3 1 5 only in the frequency band necessary for analysis, and input to the A / D converter 3 1 6.

AZD Comparator 3 1 6 is an A / D conversion operation performed by the control signal from CPU 3 2 4 transmitted via bus 3 2 0, and the output signal of mixing unit 3.1 4 is converted into a digital signal. , Temporarily store in RAM318 etc. '

FIG. 3 is a signal output diagram when 12 types of coloring reagents are used. FIG. 2 is an enlarged view of a part of the signal train of FIG. 3. The output waveform of the amplifier 3 1 3 a appearing at the output end 3 a of FIG. 6 is, for example, FIG. ) Indicates the red laser light reception signal sequence, and the numbers are the numbers assigned to the reagent reaction vessels.

Fig. 3 (a) is a signal appearing at connection point 3a, which is a signal sequence obtained by measuring light with a red laser from the first arbitrarily determined number in the reagent reaction tank. The output waveform of amplifier 3 1 3 b appearing at connection point 3b in Fig. 6 shows the green laser light reception signal train shown in Fig. 3 (b), and the numbers in the figure are the numbers assigned to the reagent reaction vessels .

Fig. 3 (b) shows that, for example, photometry is performed with the green laser from No. 5 in the reagent reaction tank.

The output waveform of the amplifier 3 1 3 c appearing at the connection point 3 c shown in Fig. 6 is shown in Fig. 3 (c), showing the blue laser light reception signal string, and the numbers in the figure are attached to the reagent reaction tank Number.

Figure 3 (c) shows that photometry is performed from the 5th reagent reaction tank using a green laser.

The output of the mixing section 3 14 that appears at the connection point 3d shown in FIG. 6 is a composite signal sequence as shown in FIG. 3 (d). The symbols R, G, and B in the figure indicate red, green, and blue, respectively, and the numbers indicate the numbers assigned to the reagent reaction tanks.

The absorbance of the reagent reaction vessel to be measured first is measured by electrical and electrical processing such as picking up the pulsed signals R1, G1, B1 from the signal sequence at a predetermined timing and superimposing them. can get.

Since the rotation of the carrier is constant, R 1 can be detected at a fixed timing, so that the red light receptions R 2 and R 3 in other test reaction vessels can also be picked up at a fixed timing.

In the case of the green laser light reception signal, for example, in the case of Fig. 1B, it is the 4th reagent reaction tank from the beginning, and with respect to the green laser of the other reagent reaction tanks at regular intervals with reference to this first signal. You can get a light reception overnight.

In the case of a blue laser light reception signal, for example, in Fig. 1B, it starts from the 7th glaze reaction tank from the beginning, and the data is picked up at regular time intervals based on this first signal. Other reagents It is possible to obtain light reception for the blue laser in the reaction vessel.

In this way, the CPU 3 2 4 shown in FIG. 6 only needs to process one signal sequence shown in FIG. 3 (d), as shown in FIGS. 3 (a), (b), and (c). As shown in Fig. 3 (d), the pulse interval is constant and the same because it corresponds to the distance between the reagent reaction vessels. If a pulse at every interval is picked up, it is possible to easily obtain the light reception pulse for each spectral light source shown in FIGS. 3 (a), (b), and (c) again.

It should be noted that a reference tank capable of obtaining a specific light receiving pulse is provided in the row of reagent reaction tanks, and the light receiving pulse indicating this reference tank may be the first pulse.

The processing of the signal sequence shown in Fig. 3 is performed by temporarily storing data in a storage medium such as a memory or heart disk every rotation or every several rotations, and reading and processing the data at the timing required for processing. It is also possible to perform sequential processing.

In this embodiment, three pairs of R (red), G (green), and B (blue) primary light emitting portions and light receiving portions are arranged at a predetermined interval. (6 5 nm) may be used, or a pair of four photometric units consisting of a light-emitting part and a light-receiving part may be arranged at the above-mentioned intervals. In addition, there may be a case where four or more pairs of photometric units are used.

Example 1 1 2

Another embodiment will be described with reference to FIG.

Figs. 1A and 1B show a disk-shaped carrier, which is rotated to perform sample and sample mixing, quantification, and other component measurement, while Fig. 5 shows the measurement device, Measure by sliding the carrier relatively! ) Show the configuration. The sliding may be repeated left and right.

The carrier 2 1 0 is made of polyacrylic material having light permeability, P It is formed of ET or the like and has a rod shape or a rectangular parallelepiped shape.

Reference numeral 2 19 denotes a lid, which has translucency, and is bonded to the carrier 2 10 by an adhesive, an adhesive, a self-adsorption ability, and the like.

2 1 5 a to 2 1 5 h are reagent reaction tanks, in which a reagent is enclosed in advance, and when a sample such as blood is quantitatively supplied from the outside, a color reaction is performed.

Reference numeral 2 20 denotes a light-shielding portion, which is colored with black and has a sheet, and light-transmitting holes 2 25 a to 2 25 h are formed only in the portion located at the bottom of each reagent reaction tank.

2 2 1 a to 2 2 1 c are electrical connection lines, and correspond to, for example, the electrical connection lines 3 2 6 in FIG.

2 2 2 a to 2 2 2 c are electrical connection lines, and correspond to, for example, a portion that electrically connects the light receiving unit 3 1 2 a and the amplification unit 3 1 3 a in FIG.

2 1 6 a to 2 1 6 c are light sources, for example, lasers that emit light of individual colors of R G B, L E D, and the like.

2 1 7 a to 2 1 7 c are photoreceptors, and are composed of, for example, phototransistors, CDS, and the like.

In this embodiment, the carrier 2 10 is placed on the carrier mounting portion 2 2 4 and the reading device lid portion 2 2 3 is closed. '

When light source 2 1 6 a and photoreceptor 2 1 7 a are arranged with reference to the first reagent reaction tank 2 1 5 a, light source 2 1 6 b, photoreceptor 2 1 7 b and light source 2 1 6 c And the photoreceptor 2 1 7 c are in a positional relationship shifted from directly below the reagent reaction tank, and are in the same state as shown in FIG. 1A.

By sliding the carrier 2 10 at a constant speed, it is possible to form a single signal sequence shown in FIG. 3 (d).

If measurement is possible with a single slide, the configuration may be simpler than the rotating configuration. Example 1 1 3

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

In Figure 8,

1 0 1 is a photoelectric conversion means, which consists of a combination of a laser light source and a light receiving semiconductor, etc., and receives a color value obtained by mixing and developing reagents and a sample to receive transmitted light and reflected light and convert them into electrical signals. It is means to do.

1 0 2 is an amplifying means, which is a combination of an amplifier circuit, a filter, etc. for filtering noise and amplifying a necessary frequency band from an electrical signal obtained by photoelectric conversion. Become.

'1 0 3 is an AZD conversion unit, which is a circuit for converting the obtained electrical signal into a digital signal for digital processing, and is mainly composed of an AZD comparator.

1 0 4 is a control unit that controls other output signals such as a storage unit 1 0 5 and a read signal output unit 1 0 6, and is configured by a CPU or the like.

1 0 5 is a memory unit, and is mainly composed of a storage medium such as RAM, DVD-R, RW, CD-R, RWS D card, etc., and RAM is suitable because it is often stored temporarily.

1 0 6 is a read signal output unit, which is composed of a clock output unit and a pulse output unit with other time adjustment, and is a signal output unit for sequentially reading data stored in the storage unit, and a reference This signal is necessary to set the time width for determining whether or not it is a part.

1 0 7 a is a first detection unit that detects optical data at a timing of 1; 6 hours with respect to the reading time tn as a digital signal or a quantized signal.

Reference numeral 10 7b denotes a second detection unit that converts optical data at a certain timing with respect to the reading time tn into a digital signal or a predetermined time width. Detected as a quantized signal with a fixed time width.

1 0 7 c is a third detection unit, which detects + time-determining optical data as a digital signal or a quantized signal with respect to the reading time t n.

1 0 7 d is a fourth detection unit, which detects optical data of + ^ 6 hours of evening imaging with respect to the reading time t n as a digital signal or a quantized signal.

1 0 8 is a multiplication unit for multiplying the signals obtained by the first detection unit 1 0 7a to the fourth detection unit 1 0 7d in the previous stage, for example, the first detection unit When the signal output from 1 0 7 a to the fourth detection unit 1 0 7 d is a digital signal, a combination of logic such as an AND gate may be sufficient.

1 0 9 is a time width setting unit. For the signal tn output from the read signal output unit 10 6, a time width signal from + jS to __ / 3 is shown, for example, as shown in FIG. 9 (e). This is a part for forming and outputting a waveform.

1 1 0 is a decision unit for judging the reference signal from the multiplication signal obtained by the previous multiplication unit 1 0 8 and the time width setting unit 1 0 9 in the previous stage and outputting the decision signal. It is a part of.

The output signal of the judgment unit 110 appearing at the output terminal 10 g is used for the recognition of the reagent reaction tank.

The above configuration is formed for explanation, and the control unit 104 may include all or a part of these configurations. The storage unit 105 may be unnecessary when processing in real time simultaneously with optical measurement.

In this example, in order to explain only the operation for detecting the reference site, an example of a carrier in which 10 or more reagent reaction vessels are arranged at equal intervals on the circumference is shown. This is shown in Fig. (A). FIG. 9 (a) shows a part of the carrier and shows a rectangular shape, but when it has a rotor shape as shown in FIG. 1A, it is formed in an arc shape, and the reagent reaction tank Are formed as part of the column.

FIG. 9 (b) shows a cross section along the line XX ′ in FIG. 9 (a). In FIG. 9 (a), the lid 1 1 7 is omitted.

In FIG. 9 (a), 1 1 1 a and 1 1 1 b are reagent reaction tanks, which are formed by forming a recess on a base material 1 16 such as polycarbonate, and contain the reagent therein. ing. The reagent reaction tank is connected to a flow path for supplying a sample from the outside and a supply path 1 1 2 a and 1 1 2 b such as a capillary tube. 'The supply path may be unnecessary depending on the type of sample or reagent and the supply form.

1 1 3 is a slit, and at least a non-translucent member is formed. The thickness of the slit 1 13 is not particularly limited as long as the non-translucent portion is formed. Small slit: 1 1 3 may be formed integrally with the base material -1 1 6 or may be joined separately.

1 1 4 is a gap, and is formed in the same size on both sides across the slit 1 1 3. The air gap 1 1 4 is preferable because it is more conspicuous in terms of measurement than the sample reaction tank 1 1 la ′ and 1 1 1 b, but it is preferable in terms of measurement. As long as the size is detected at a distance of the gut.

In FIG. 9), a slit 1 13 and a gap 1 1 4 are combined to form a reference portion 1 15.

Reference numeral 1 17 shown in FIG. 9 (b) denotes a lid, which may be formed of the same material as that of the base material 1 16 and has a translucency as a whole.

The lid 1 1 7 and the substrate 1 1 6 are preferably joined by, for example, an adhesive, a pressure-sensitive adhesive, or a self-adsorption ability.

1 1 8 is a non-translucent member, black or equivalent color scheme It is a member that does not transmit light. The non-translucent member 118 is preferably, for example, in a seal shape or a thin plate shape, and is bonded with an adhesive, an adhesive, or a self-adsorption ability.

Next, the operation of the embodiment shown in FIG. 8 will be described in detail with reference to FIG. .

In FIG. 9, the quantitative sample supplied to the reagent reaction tanks 1 1 1 a and 1 1 1 b via the supply channels 1 1 2 a and 1 1 2 b is the reagent previously stored in the reagent reaction tank. To develop a color reaction. When the reaction is stable, irradiate each reagent reaction tank with laser light or other visible light. The optical signal reflected or transmitted through the reaction solution in the reagent reaction tank is received by the photoelectric conversion means 10 1 shown in FIG. The photoelectric conversion means 101 converts the received optical signal into an electrical signal, and then amplifies and filters the amplified signal, and the amplified and filtered signal is sent to the A / D conversion section 103. Supply. The signal output to the connection point 10 a in FIG. 8 is, for example, as shown in FIG. 9 (c).

'The AZD conversion unit 103 shown in Fig. 8 converts the input analog signal into a digital signal, and then outputs this digital signal to the storage unit 10 5.

Storage unit 1 0 5, FIG. 9 ^(a); temporarily or continuously records the data round the orbit of reagent reaction vessel train indicated by.

Control unit 104 causes read signal output unit 106 to start outputting a read signal.

The control unit 10 04 detects the digital data at the time of ± α, saturating i6 time with respect to the time signal tn output from the read signal output unit 10 06, and each detection unit 1 0 7 a to '1 0 7 Control to detect with d.

The time signal tn is output continuously according to the clock. The first detection unit 107 7a detects the digital received light waveform at the time signal tn— ^. The second detector 1 0 7 b detects the digital received light waveform for the time signal tn-α, and the third detector 1 0 7 c detects the digital received light waveform for the time signal tn + The fourth detector 1 0 7 d detects the digital light reception waveform at time signal tn + ^ 8.

The received waveform is digital data, and once quantized it is shown in Fig. 9 (d). Each detection unit does not necessarily need to be restored until quantization, and may be a code signal as long as the signal can be multiplied by a multiplication unit and the signal is not noise but an actual received light signal. .

For example, each detection unit converts a digital value output from the storage unit 105 shown in FIG. 8 and outputs a pulse as a light reception signal when a predetermined threshold value is exceeded. good.

The tnl, tn2, and tn3 shown on the time axis in Fig. 9 (c) are given as samples for explanation, and the actual time tn moves continuously over time in the time axis direction. The detection unit detects the received light signal stored in the storage unit every time of ±, ± / 3 along with the movement.

For example, when the read signal output unit 106 shown in FIG. 8 outputs the time tnl signal to the storage unit 10.5, the first detection unit 10 07a shown in FIG. 8 reads from the storage unit 105. Among the received light signals, the light signal value at the time of 120 a in Fig. 9 (c) is detected, and the output shown in Fig. 9 (d) is output at the connection point 10 b in Fig. 8 Do. The first detection unit 1 0 7 b shown in Fig. 8 detects the received light signal value at the time of 1 2 O b in Fig. 9 (c) among the received light signals read from the storage unit 1 0 5. Then, the output shown in FIG. 9 (d) is output at the connection point 10c in FIG. The first detection unit 1 07 c shown in FIG. 8 detects the received light signal value at the time 1 2 0 c of FIG. 9 (c) from among the received light signals read from the storage unit 10 5. The output shown in Fig. 9 (d) is made at the connection point 10d in Fig. 8. The first detection unit 10 07 d shown in FIG. 8 receives the received light signal read from the storage unit 105. Among these signals, the received light signal value at the time 1 2 0 d in Fig. 9 (c) is detected, and the output shown in Fig. 9 (d) is performed at the connection point 10 e in Fig. 8.

These four signals are input to a multiplication unit 10 8 shown in FIG. 8, and the multiplication unit 1 0 8 performs logical multiplication. In the case of the first incoming light pulse in Fig. 9 (c), the outputs of the third detector 1 0 7 c and the fourth detector 1 0 7 d shown in Fig. 8 are 0. The output of the unit 1 0 8 is 0.

The time width setting unit 10 9 receives the time width signal having tn ± i6 as the pulse width as shown in FIG. 9 (c) from the output signal of the read signal detection unit 10 6 as shown in FIG. 1 0 Output to judgment unit 1 1 0 via ί.

The determination unit 1 1 0 checks whether or not there is an output from the multiplication unit 1 0 8 based on the time width signal from the time width setting unit 1 0 9, but the output of the multiplication unit 1 0 8 at time tnl is Since it is 0, the determination unit 1 1 0 determines that this is not the reference unit, and outputs a signal to that effect to the output terminal 10 g. Next, at time tn2 among the time signals sequentially output from the readout signal output unit 106 shown in FIG. 8, the first detection unit 10 07a receives the light received from the storage unit 105. The received light signal at the time position indicated by 1 2 1 a is detected and output to the connection point 1 Ob shown in FIG. .

'The first detector 1 0 Ί b detects the received light signal at the time position indicated by 1 2 1 b in Fig. 9 (c) among the received optical signals read from the storage unit 105. Output to connection point 1 0 c shown in Fig. 8.

The first detection unit 1 0 7 c detects the light reception signal at the time position indicated by 1 2 1 c in FIG. 9 (c) among the light reception signals read from the storage unit 10 5. Is output to the connection point 1 0 d indicated by.

The first detection unit 1 07 d outputs the received light signal at the time position indicated by 1 2 1 d in FIG. 9 (c) among the received light signals read from the storage unit 1 0 5; Output to terminal 10 e shown in the figure.

Connection point 1 0! ) ~ 1 0 e The output signal indicated by e is input to the multiplier 1 0 8 Are multiplied, but at this time all correspond to 1, so the output is 1.

When the output 1 of the multiplication unit 10 8 is input to the determination unit, the determination unit 110 detects t n2 from the time width signal input from the time width setting unit 10 9, and FIG. As shown by), a pulse indicating that it is the reference position is output at that position.

Next, in the case of the time tn3 shown in FIG. 9 (c) among the time signals tn output from the readout signal output unit 106 shown in FIG. 8, the first detection unit 1 0 7 shown in FIG. a detects the received light signal at the time position indicated by 1 2 2 a in FIG. 9 (c) among the received light signals read from the storage unit 105, and the connection point 1 0 shown in FIG. Output to b.

The first detection unit 1 0 7 b detects the light reception signal at the time position indicated by 1 2 2 b in FIG. 9 (c) among the light reception signals read from the storage unit 1 0 5. It outputs to the connection point 1 0 c shown by.

The first detection unit 10.7 c detects the light reception signal at the time position indicated by 1 2 2 c in FIG. 9 (c) among the light reception signals read from the storage unit 105, Output to connection point 10 d shown in the figure.

The first detection unit 10 07 d detects the light reception signal at the time position indicated by 1 2 2 d in FIG. 9 (c) among the light reception signals read from the storage unit 10 5. Is output to the connection point 1 0 e indicated by.

The output signals indicated by the connection points 10 b to 10 0 e are input to the multiplication unit 10 8 and multiplied, but at this time, as shown in FIG. 9 (d), the first detection unit 10 Since the outputs of 7 a and the second detection unit 1 0 7 b are 0, the multiplication unit 1 0 8 shown in FIG. 8 outputs a signal that is 0 as a result of the multiplication.

Since the signal input from the multiplier 1 0 8 is 0 for a predetermined time width, the determiner 1 1 0 outputs a signal indicating that it is not the reference unit as shown in FIG. 9 (f). To do. As described above, since the reference portion is detected computationally, the accurate reference portion can be electrically confirmed.

Example 1 1 4

'An embodiment for obtaining an effective measurement point when measuring components from light passing through a reagent reaction tank in the present invention will be described in detail with reference to the drawings.

FIG. 10 is a block diagram showing an embodiment of the present invention.

1 3 0 1 is an amplifying means for inputting a biochemical signal obtained by photoelectric conversion from an input terminal la, amplifying and filtering.

'1 3 0 2 is a differentiating means for differentiating the amplified biochemical signal.

Differentiating means 1 3 0 2 have at least two output terminals, one is connected to the means for determining the measurement area, and the other is the averaging means, adding average, integral restoration, etc. Connected with the means to be.

1 3 0 3 is a full-wave rectifier, and is a circuit for setting the peak of the differential signal to either + or-polarity.

1 3 0 4 is a measurement area detection means, which is a measurement determined by the measurement width determination means 1 3 0 6 Inputs a signal indicating the width, detects and outputs the measurement area based on the measurement width Is for the purpose.

1 3 0 5 is a peak detection means for detecting the peak value of an input signal, such as a Schmitt trigger circuit that detects a peak pulse that exceeds a certain threshold value. It may be.

Reference numeral 1 3 06 denotes measurement width determination means, which may detect the measurement region from the pulse width and pulse interval of the peak pulse input from the preceding peak detection means 1 3 0 5. In addition, in order to detect the occurrence of peaks due to the introduction of foreign substances such as bubbles, a threshold of a predetermined height is further set. It may be fixed.

1 3 0 7 is an averaging means, and is a means for outputting the differential signal output from the measurement area detecting means 1 3 0 4 as a signal obtained by averaging the averaging signals. 1 3 0 7 An averaging means for converting to an integral signal may be used.

An example of the structure of the carrier connected to the analysis circuit is shown in Fig. 11A. FIG. 11A shows another example of the configuration of the same part as FIG.

Reference numeral 401 denotes a carrier, which is made of a translucent plastic material such as PET or polyacrylic, a glass material, or the like, and has a disk shape or a sheet shape in which one or more reagent tanks are formed.

4 0 2 is a lid, which is the same material as the carrier, for example, and is bonded to the carrier by an adhesive, an adhesive, and self-adsorption.

Reference numeral 40 3 denotes a light-absorbing member, which is formed of black or a gray sheet close to black, and a measurement window 40 4 formed of a circular through-hole is formed immediately below the reagent reaction tank 45. Has been.

The light-absorbing member 40 3 may be disposed at least near the reagent reaction tank 45 at least.

40 4 is a measurement window, and the area of the measurement window 40 4 is preferably, for example, an area slightly smaller than the measurement area of the reagent reaction tank 4 5. This is because light leaking to the side surface of the reagent reaction tank may reach the light receiving element if the area is the same as the measurement surface area of the reagent reaction tank 45.

405 is a reagent reaction tank, which is a portion where solid or liquid reagent is sealed in advance and reacts with body fluid supplied from outside, such as a supply channel, and develops color. . 4 0 6 is a light source, which includes a laser light source, an LED, a UV light source, and the like.

Reference numeral 40 7 denotes a first lens body, which is an ordinary lens, formed in a spherical shape, and mainly has an arrangement shape for condensing light in the reagent reaction tank 45 5, and forms parallel rays. The shape and arrangement are correct.

Reference numeral 40 8 denotes a second lens body for converting the diffused light beam into a light beam suitable for light reception by the light receiving element 40 9 by condensing or collimating it.

One or both of the first lens body 4007 and the second lens body 4008 may be unnecessary depending on the performance and shape of the light source 4006 and the light receiving element 4009.

409 is a light-receiving element that converts an optical signal into an electrical signal, and is made of a semiconductor such as a CDS, a photodiode, a diode, or a diode.

Reference numeral 4 10 denotes a supply flow path port, which is a connection part with a flow path for supplying a liquid specimen to the reagent reaction tank 4 0 5 preferably, preferably quantitatively.

4 1 1 is an electrical lead wire for the light source, and is a supply path for supplying electrical energy for driving the light source 4 0 6.

4 1 2 is a light receiving side electric lead wire, which is a light receiving element for supplying a photoelectrically converted signal to the input terminal 1 a in FIG. For example, the carriers 401 may be arranged at equal intervals on the outer periphery of a disc-shaped carrier as shown in FIG.

Next, the operation of the embodiment shown in FIG. 10 and FIG. 11A will be described in detail with reference to FIG.

The carrier 40 01 shown in FIG. 11 is a rotating body, and the quantitative sample is supplied from the supply channel 4 10 to the reagent reaction tank 4 0 5, and is colored after stirring and mixing. For example, it rotates at a speed of about 600 rpm. When the reagent reaction tank 4 0 5 comes directly under the light source 4 0 6, the measurement light output from the light source 4 0 6 passes through the first lens body 4 0 7, and from the measurement window 4 0 4, After passing through the carrier 40 1, the reagent reaction tank 4 0 5, the lid 4 0 2, the second lens body 4 8 8 receives light that is converted into parallel light and condensed light for the light receiving element 4 0 9. Light is received by element 4 0 9. 4 1 3 shows an example of the optical path.

The light receiving element 4 0 9 inputs the photoelectrically converted signal to the input terminal 1 a shown in FIG. 10 via the light receiving electrical lead 4 1 2.

In Figure 10

The electrical signal input to this input terminal is amplified and filtered by the amplification means 1 3 0 1 and input to the differentiation means 1 3 0 2 as the signal shown in Fig. 2 (a) at connection point 1 M. Is done.

3 1 a shown in FIG. 12 (a) is an example of a peak generated when bubbles are present in the reagent reaction tank.

Differentiating means 1 3 0 2 outputs the differential signal shown in Fig. 1 2 (b), and this differential signal is the full-wave rectifying means 1 3 0 3 shown in Fig. 1 0 and measurement area detecting means 1 3 0 Enter 4 'sa-':

After the full-wave rectification means 1 3 0 3, the differential signal is full-wave rectified, and then as a full-wave rectification signal shown in FIG. Supplied to 5.

The peak detection means 1 3 0 5 sets the threshold value REF 1 and converts the portion exceeding this threshold value into a pulse with a constant amplitude as shown in Fig. 12 (d). Output to measurement width determining means 1 3 0 6 via le. Measurement width determination means 1 3 0 6 uses the pulse shown in Fig. 12 (e) as the connection area, with the rising edge of the next pulse from the falling edge of the first pulse as a stable area width for measurement analysis. 1 Π Output.

When determining the width of this measurement area, the pulse is The detection range until the rise of the cell is preferably a case where a provisional range determined based on the rotation speed of the carrier and a predetermined timing of the reagent reaction tank is calculated in advance and included in the range.

The measurement area detection means 1 3 0 4 allows the output of the differentiation means to pass between the measurement width pulses obtained by the measurement width determination means shown in FIG. 1 2 (e), and to the averaging means 1 3 0 7 Input the passage amount.

Averaging means 1 3 0 7 integrates and averages the passages to obtain the true measurement area (3 1 b, 3 lc) as shown in Fig. 12 (ί). Output to.

'Fig. 11 B shows an example in which the optical measurement state is further improved by protecting the part corresponding to the optical path for handling.

In FIG. 11B, the same components as those in FIG. 11A are denoted by the same reference numerals and description thereof is omitted.

4 14 is a recess formed at the bottom surface of the carrier 4 0 1 and corresponding to the portion immediately below the reagent reaction vessel 4 0 ′ 5. The area of the recess 4 14 is preferably at least equivalent to the width of the light passing through the light source 40 6 and the first lens body 40 7. -

The height of the recess 4 1 4 may be such that the recess 4 1 4 prevents the attachment of fingerprints when the user handles the carrier 4 0 1. Examples are about 5 to 1 mm.

4 1 5 is a light-shielding printing surface, which is formed by a screen printing method or the like. The light-shielding printed surface 4 15 may be other colors having a density that does not transmit light at least in addition to black printing.

4 1 6 is an adhesive tape, which is a transparent tape having a pressure-sensitive adhesive formed on one side, and a double-sided adhesive tape formed of a translucent tape with the pressure-sensitive adhesive exposed on only one side.

4 1 7 is a fitting lid, the same material as the carrier 4 0 1, thickness Is about 1mm and may or may not be translucent.

Reference numeral 4 18 denotes a hole, which is formed by a through-hole having an area sufficient to allow the light that has passed through the reagent reaction tank 45 to pass therethrough.

Reference numeral 4 19 denotes a fitting hole, which is formed in the carrier 40 1, and is formed so that the fitting portion is difficult to be removed by forming the diameter of the lower portion slightly larger than that of the upper portion. In addition, when making by molding, it may be a through hole.

Reference numeral 4 2 0 denotes a fitting protrusion, which is formed integrally with the fitting lid 4 15, and the tip portion forms a fitting tip portion 4 2 1 that can be contracted laterally 1 1 1 In the embodiment shown in FIG. B, an adhesive tape 4 1 6 is applied to the carrier 4 0 1, and further, the fitting lid 4 1 7 is covered from above, and the fitting hole 4 1 9 on the carrier 4 0 1 is covered. By inserting the fitting protrusion 4 2 0 and opening the fitting tip 4 2 1 outward at the tip of the fitting hole 4 1 9, the fitting lid 4 1 7 and the carrier 4 0 1 Is mechanically coupled.

In the vertical direction of the reagent reaction tank 4 0 5, the portion corresponding to the optical path is covered with the concave portion 4 1 4 and the hole portion 4 1 8 so that the user's fingertip does not touch the optical path surface. Loss of transmitted light due to fingerprints is reduced.

The light output from the light source 40 6 is collected by the first lens body 40 7 and passes through the reagent reaction tank 4 0 5 from the recess 4 1 4 to the hole 4 1 8, the second lens body. Light is received by the light receiving element 4 0 9 through 4 0 8. The second lens body is not required and may not be required.

Since the light-shielding printing surface 4 15 is a thin film but does not allow light to pass therethrough, it is possible to prevent mixing of irregularly reflected light and the like into the transmitted light.

Next, another embodiment will be described with reference to FIG.

Fig. 13 'shows the reaction in the reagent reaction tank in addition to the configuration shown in Fig. 10. This is an embodiment with a configuration to enable detection of optical information even when the amount of received light is small, such as when the light is not sufficiently transmitted and the amplitude of the electrical signal is small because the result is too dark. .

1 3 27 is a peak interval detection means for detecting the interval time of the peak signal output from the preceding peak detection means 1 3 0 5.

1 3 2 8 is a comparison means, which compares the preset interval signal with the peak interval signal output by the peak interval detection means 1 3 2 7 and outputs a mismatch signal if they do not match roughly To do.

'1 3 0 6 is a measurement width determination means. In addition to the functions described in FIG. 10, the output signal from the comparison circuit 1.3 28 is output from the peak interval detection means 1 3 2 7. When the peak interval signal is a mismatch signal when the interval signal is longer than the preset interval signal, the value obtained by dividing the length by the preset interval signal is a value n (where n≥ 1) However, only a preset peak interval and a preset measurement width signal are output in combination.

These operations may be realized by a control element such as a one-chip microcomputer. ·

Next, the operation of FIG. 13 will be described in detail with reference to FIG.

The transmitted light signal input to the amplifying means .1 130 shown in FIG. 13 is amplified and filtered to output the signal shown in FIG. 14 (a).

3 0 a and 3 O b are transmitted light generated through the periphery without passing through the inside of the reaction tank, and are noise.

30 0 c is noise generated by bubbles generated in the reagent reaction vessel. -The signal outputted from the amplifying means 1 3 0 1 is differentiated by the differentiating means, and the differential waveform shown in Fig. 14 (b) is outputted to the connection point lc. After that, full-wave rectification is performed by the full-wave rectification means 130, and a waveform as shown in Fig. 14 (c) is output to the connection point Id.

The peak detection means 1 3 0 5 shown in FIG. 13 outputs a pulse at a portion exceeding the threshold REF 2 shown in FIG.

The peak interval detection means 1 3 2 7 shown in FIG. 13 stores this pulse, and when the next peak is inputted, for example, with reference to the rise of the pulse, the peak interval 11 shown in FIG. 14 is detected, Output to comparison means 1 3 2 8 shown in Fig. 13.

The comparison means 1 3 2 8 shown in FIG. 13 compares the peak interval 11 shown in FIG. 14 with the reagent reaction vessel interval 12 predicted in advance, and n = ll / 12−l is 0≤η If <1, the correct reagent reaction tank interval is assumed, and if it is 1 or more, a signal indicating that there is an undetected part in the reagent reaction tank is output.

The measurement width determination means 1 3 0 6 receives the signal output from the comparison means 1 3 2 8, and sets a preset width 13 for each preset interval 12 by the number of values of n. Output.

In the case shown in FIG. 14, since n = l, a predetermined time width 13 obtained from the moving speed of the carrier and the diameter of the measurement surface of the reagent reaction tank after a predetermined interval 12 is measured. (See Fig. 14 (f)).

For example, when n is 2, the measurement region 13 is set after a predetermined time interval 12, and then the measurement region 13 is set after a predetermined time interval 12.

The measurement area detection means 1 3 0 4 allows the differential signal to pass through the preset time interval 13 and the averaging means 1 3 0 7 is an average with higher sensitivity than other parts. To do.

In Fig. 14, the measurement range is indicated by a dotted rectangle.

By the above operation, a stable concentration measurement range can be realized even when the reaction concentration in the reagent reaction tank is large and no transmitted light can be obtained. Example 1 1 5

Next, an embodiment for removing noise caused by scattered light or the like when irradiating light to the reagent reaction tank will be described in detail with reference to FIG. 15 and FIG. FIG. 16 is a cross-sectional view taken along line X—X ′ in FIG.

Reference numeral 400 denotes a lid, which is made of, for example, the same material as the carrier and is bonded to the carrier by an adhesive, an adhesive, or self-adsorption.

'4 0 3 is a light absorbing member, which is formed of black or a gray sheet close to black, and immediately below the reagent reaction tank 4 0 5 is a measurement window 4 0 4 consisting of a circular through hole. Is formed.

Reference numeral 400 denotes a reagent reaction tank, which is formed in a cylindrical shape on the carrier 4 0 1.

Reference numeral 4 10 denotes a supply channel, which is formed in a concave shape on the carrier 4 0 1 and is used for supplying a sample from the outside for a fixed amount.

4 2 2 is a distribution channel for supplying specimens to individual reagent reaction vessels.

The diameter of the bottom 30 g of the reagent reaction tank shown in Fig. 16 is about 1.5 mm, whereas the diameter 30 0 f of the measuring window is about lmm.

In this state, when measuring light is transmitted from below into the reagent reaction vessel described above, the whiskers 30a and 30b shown in Fig. 14 (a) do not occur, and a stable waveform is obtained. It is done.

Example 1 1 6

Next, another embodiment of the present invention for removing unnecessary signals generated depending on the circuit, the shape of the carrier, and the processing state will be described in detail with reference to FIGS. In Figure 17

Reference numeral 5 0 1 denotes a photoelectric conversion means for converting the transmitted light that has passed through the reagent reaction tank into an electric signal and outputting it by a combination of a laser, a LED light source, and a light receiving element.

5 0 2 is an amplifying means, for example, for amplifying an input photoelectric conversion signal in an analog manner, filtering it, and outputting it.

Offset value correction means 5 0 3 connects the calibrated signal by performing operations such as removing the input offset signal from the signal related to the transmitted light that has passed through the reagent reaction tank. The calculation for calibration, which is a means to output to the point 5c, is, for example, a method of calculating after converting it to a digital signal and an analog calculation method, but depending on the size, speed, etc. of the device It is selected appropriately.

Reference numeral 5 0 4 is an offset value determining means for discriminatingly selecting a received light signal obtained from the calibration region of the carrier, forming an offset signal, and outputting it to the offset value correcting means 5 0 3 belongs to.

5 0 5 is a timing signal forming means that detects the timing when the measurement unit and the reagent reaction tank coincide with each other in synchronization with the state in which the carrier and the measurement unit are relatively moving, and outputs a coincidence signal. Is for.

Reference numeral 56 denotes reference data forming means, for example, means for temporarily storing the results of optical measurement using transmitted light in a reagent reaction tank containing a diluent, pure water, and the like.

In some cases, it may be preferable to memorize the value obtained by performing the same measurement multiple times and averaging.

In addition, there are cases where the value of optical measurement results of plasma only, etc. is stored. Such memory is stored as a 0D value, and that value is used as the reference value for OD = 0. To do.

Reference numeral 5 07 denotes calibration means, which is corrected by subtracting the stored value from the optical measurement result of each reaction tank. Calibration includes the meanings of correction and correction.

The timing signal may be obtained by detecting the reference portion of the carrier and then oscillating predictably from the rotational speed and a fixed arrangement angle of the reagent reaction tank. If the reagent reaction tank position is detected from the amplitude value of the signal, etc., and the color density drops out during the process, the detected reagent reaction tank position signal and the predetermined diameter of the reagent reaction tank are arranged. It may be obtained predictively based on the distance (angle).

In addition, when a stage subsequent to the amplification means is used as a means for digital processing, an AZ D converter or the like may be newly added and executed by a single microcomputer storing the program.

An example of the carrier is shown in FIG. Fig. 19 shows only the parts that are considered necessary for the explanation. In addition, the part where blood and diluent are mixed, the part that is quantified, the blood inlet, etc. are omitted.

The carrier 500 is formed of a translucent member such as polyacrylic or PET.

5 0 a is a red light receiver, and 5 O b is a red light source. 5 1 a is a green photoreceptor, and 5 l b is a green light source. 5 2 a is a blue light receiver, and 5 2 b is a blue light source.

Examples of the light source include lasers and LEDs, and examples of the light receiver include CDs and phototransistors.

5 3 a to 53 h are a part of the reagent reaction tank, for example, cylindrical bodies having a diameter of about 1 mm are arranged at equal intervals. Each reagent reaction vessel is filled with different reagents in liquid or solid form. These reagent reaction tanks are a part, and in addition, reagent reaction tanks of the same size in which other reagents are enclosed are arranged at equal intervals on the optical path.

5 4 indicates the calibration area provided for calibration and correction.

In calibration area 54,

Reference numerals 5 4 a and 5 4 b are calibration medium storage units, for example, provided with a reagent reaction tank in a diluted liquid only, plasma only, pure water, and empty state. Although two of these calibration medium storage units are shown, they may be increased by the number of necessary calibration information. The calibration medium container is also an example, and other calibration medium containers may be arranged at equal intervals.

5 4 c is the black region, which is black with the same area as the reagent reaction tank.

5 4 d is a reference area, which is a hole that penetrates vertically, and is slit in the diameter direction. The reference area 5 4 d is a part that serves as various reference points such as the start point, end point, and position recognition point for measurement in the reagent reaction tank, and uses a point that is penetrating light to receive light from the light source. A reference value for measuring the maximum amount of light received between bodies may be obtained.

5 5 a is a flow channel for distribution, and 5 5 b is a flow channel for supply having quantitativeness.

5 6 shows, for example, two chucking holes for coupling with the reading device.

5 7 is a body fluid supply port, which is a hole used for supplying body fluid from the outside. The body fluid supply to the body fluid supply port 57 is preferably performed using a simple injection tool such as a microphone port pipette or a spot.

The configuration from the body fluid supply port 57 to the various reagent reaction tanks is composed of a mixture of body fluid and diluent, and a part for separating unnecessary blood cells from the body fluid. But this part was omitted.

The body fluid is supplied to the carrier 500 which is a rotating body from the central blood inlet, and unnecessary components such as blood cells are removed by centrifugation and mixed with the diluted solution. A diluted mixed plasma solution is quantitatively supplied and mixed. These actions are preferably performed by rotation and capillary force.

Quantitative mixture fluid is in each reagent reaction tank 5 3 a-5 3 h Other distribution channels 5 5 a, supply channels 5 5 Supplied through b and mixed with liquid, particulate reagent in the reagent reaction tank to cause a color reaction.

The carrier 500 is rotated to form a state in which the reagent reaction tank, the calibration medium storage unit, and the reference unit move between each light source and the photoreceptor.

FIG. 18A is a cross-sectional view along the line XX ′ in FIG. FIG. 18A shows an arrangement in which the carrier 50 0 0 is actually installed in the reader, and the photoreceptor 5 0 a and the light source 5 Ob reach the vertical direction of the reagent reaction vessel 5 3 a. For example, the same configuration as in Fig. 4 is shown.

In FIG. 18A, 5 O l a is the upper part of the reading device, and a light receiver 50 0 a is attached. An electrical lead wire 50 c for transmitting an electrical signal to the outside is connected to the photoreceptor 50 a. Reference numeral 5 0 1 b denotes a lower part of the reading device, and a light source 50 b is arranged in a portion corresponding to a portion immediately below the photoreceptor 50 a.

An electric lead wire 50 d for supplying electric energy is connected to the light source 50 b.

The reagent reaction vessel 5 3 a is filled with a plasma component-reagent mixed solution 5 0 1 c.

The carrier 5 0 0 is formed by forming various flow paths with a reagent reaction tank as a recess, and a lid 5 0 Connect O b with adhesive, adhesive, and self-adsorption ability.

Further, in order to efficiently obtain transmitted light, a light absorbing member 500 c is applied and connected in addition to the optical path passing through the reagent reaction tank.

FIG. 18B shows a state in which the carrier 50 0 0 further rotates and the calibration medium container 5 4 a is placed between the red light source 5 0 b and the red light receiver 5 0 a. Diluent 5 2 a is contained inside. Although the supply channel is not connected because it has been pre-injected, when supplying blood and developing the diluted solution, supply only the diluted solution to the calibration medium container 54a. May be.

'FIG. 18 C shows a state in which the black region 54c is placed between the red light source 50b and the red photoreceptor 50a.

The black area 5 4 c does not necessarily have a reagent reaction tank.

As shown in FIG. 8C, it is preferable that a light-absorbing member 500 c is disposed at the bottom of the carrier 500.

Next, the operation of the embodiment having the above-described configuration will be described.

A plasma component is quantitatively supplied to the reagent reaction tank containing the reagent on the carrier 500 shown in FIG. 19 via the supply channel.

The quantitative sample is agitated by a change in rotation in the reagent reaction tank and reacts with the reagent.

At a timing at which color development measurement is possible, the carrier 5 0 0 is rotated at a rotational speed of about 6 0 0 rpm, and the reference region 5 4 d on the carrier 5 0 0 is a red light source 5 O b and a red photoreceptor 5 On the optical path of 0 a, green light source 5 lb and green light receiver 5 1 When light passes through the optical path of 1 a and blue light source 5 2 b and blue light receiver 5 2 a, the light reception measurement is performed. Figure 21 shows the light reception waveform of one of the three light receiving units.

In FIG. 21, 5 10 S is a waveform when the reference region 54 d shown in FIG. 19 is received, and the center slit indicates two bilateral signals. is doing.

The reference signal 5 10 S is converted into an electric signal by the photoelectric conversion means 5 0 1 shown in FIG. 17 and then input to the timing signal forming means 5 5. For example, a signal sequence as shown in FIG. 20 is output to the connection point 5a in FIG. The signal sequence in FIG. 20 is the combination of the red light source 5 O b and the red light receiver 50 0 a shown in FIG. 19, the combination of the green light source 5 lb and the green light receiver 5 la, and the blue light source. The electric signal train obtained from one of the combinations of 5 2 b and blue light receiver 5 2 a is shown. V o if is the offset voltage, which is a voltage generated from the characteristics of the element.

The timing signal forming means 5 0 5 is based on 5 1 OS shown in Fig. 2 1, and for example, performs 5 M of free-running pulse output as shown in (b). This pulse interval is equally spaced. This corresponds to the distance between the arranged reagent reaction vessels, and the pulse width corresponds to the area in the optical path typified by the reagent reaction vessel.

Fig. 21 (a) shows the output signal sequence when the reagent reaction vessels 5 1 1 a to 5 1 1 e are measured at regular intervals with 5 10 S as the reference site. Fig. 21 (1) In the signal sequence shown in Fig. 21 (a), 5 1 1 a to 5 1 1 e receive the transmitted light that has passed through the colored state in the reagent reaction tank containing the actual reagent and photoelectrically convert it. It is a subsequent signal sequence.

Further, when the light source and photoreceptor unit reach the black area 54c shown in Fig. 19, only the offset voltage Voff signal shown in Fig. 20 is received. This is a voltage unique to an electronic circuit such as a phototransistor, an amplifier circuit, and the like. In FIG. 17, the photoelectric conversion means 51 1 1 receives the black region and converts it into an electric signal, and then amplifies and filters it by the amplification means 50 2. The output signal of the amplification unit 5 0 2 is shown in 5 1 2 &, 5 1 2 b, 5 1 2 c in Fig. 2 1).

These output signal voltage values are added and averaged by the offset value determination means 50 4, and temporarily stored or set as one offset voltage value.

Next, the reagent reaction vessel 53 a shown in FIG. 19 is replaced by the photoelectric conversion means 50 01 shown in FIG. 17 (for example, between the light source 50 b and the light receiving element 50 a shown in FIG. 19). When passing the light, the color reaction reaction obtained by the light receiving element 50a is amplified by the amplifying means 502, and input to the offset value correcting means 5.03.

The offset value correction means 50 3 reduces the offset voltage VoH input from the offset value determination means 50 4 to the amplified color development reaction, thereby reducing the error with a smaller error. Evening (for example, V 5 11 shown in FIG. 21 (a)) is obtained and outputted to the connection point 5c and also outputted to the correcting means 507 and the reference data forming means 5106.

Note that it is not necessary to obtain an offset voltage value for each photoreceptor associated with each primary color, and it may be sufficient to store the total sum of the photoreceptor output voltages. In FIG. 5, the reference de-evening means 5 0 6 shows that the reagent reaction tank filled with only water and diluent passes through the photoelectric conversion means 5 0 1 according to the timing signal from the timing signal forming means 5 0 5. Then, it is detected that the calibration data calibrated by the offset value correction means 50 3 is output to the connection point 5 c, and the value is temporarily stored (for example, FIG. 21 (a)). All of 5 1 3 a to 5 1 3 c shown in).

Furthermore, optical data of only the diluted solution adjacent to each other is stored for each rotation, and added up and averaged, and attenuation data due to reflection and scattered light generated by the carrier. It is preferable to memorize the evening and convert it into an OD value after averaging (for example, Vt shown in Fig. 21 (a)) and memorize it.

Further, the reference data forming means 50 06 shown in FIG. 17 stores the optical data 0D value of the penetrating light from the reference area 54 d shown in FIG. A value (for example, the value related to Vmax shown in Fig. 21 (a)) is obtained.

〇 D value is indicated by, for example, loglO (V in / Vout).

By subtracting the optical data (0D value Vt) of the diluted solution from the optical data for penetrating light (5 10 S shown in Fig. 21 (a)) (0 D value Vmax), the carrier Attenuation ○ D value Vg (Vmax—Vt) is obtained, which is temporarily recorded. .

The light reception signal V 5 11 shown in FIG. 21 (a) relating to the light transmitted through the reagent reaction vessel 53 3a shown in FIG. 19 is converted into the photoelectric conversion means 5 0 1 and the offset value correction means shown in FIG. When the data is input to the correction means 5 0 7 via 5 0 3, the reference data forming means 5 0 6 shows the carrier attenuation data Vg shown in FIG. 21 (a) in FIG. Output to correction means 5 0 7.

Correcting means 5 0 7, the Isseki optical de relates to a reagent and OD-value conversion, by adding the carrier attenuation de Isseki Vg of the 2nd 1 view (a), values that are produced by ¹ loss of carrier Complementing V 5 11+ Vg makes it possible to obtain a true color and color.

In addition to the diluted solution data, the optical data of only the sample filled in the reaction tank that does not contain the reagent (for example, plasma only) is converted into a D value and used as reference data (add the carrier attenuation value Vg). It is also possible to obtain a more accurate color reaction value by calculating.

2nd invention-2nd invention is the temperature which measures the temperature of the part which heats a part of one surface of the support | carrier which performs rotation or a periodic motion, and the site | part facing the said heating means Temperature control is possible while suppressing power consumption by measuring means, control means for adjusting and controlling the amount of heat to heat the carrier of the heating means based on the temperature measured by the temperature measuring means, and a heat absorbing member arranged on the back surface of the carrier Suppose that

Examples of the heating means in the present invention include those that irradiate infrared rays and far infrared rays, infrared lamps, halogen lamps, and the like.

The temperature measuring means in the present invention is exemplified by a non-contact type temperature sensor (thermopile etc.).

The heating unit and the temperature measuring unit may be located at different positions on one carrier, but are preferably arranged diagonally. The distance between the heating means and the carrier is exemplified as 5 to 10 mm, and the distance between the temperature measuring means and the carrier is exemplified as 5 to 10 mm.

The heat-absorbing member in the present invention is a black material or a member that absorbs and holds heat, and examples include a member formed by applying a solution or a gel material on the back surface of the carrier or attaching a black sheet.

When heating a part of the upper part of the carrier, the upper surface of the carrier is first heated, and the heat-absorbing member is heated by passing through the inner part of the carrier. Since the carrier rotates, the entire carrier is heated from both sides.

In the present invention, a disk-shaped carrier having a thickness of several millimeters made of a hard polymer such as polyacryl is exemplified, but in addition, a sheet-like carrier and the like, in which a reagent reaction tank is arranged in the longitudinal direction, etc. Is exemplified.

In the present invention, a thin and compact reading device can be realized by arranging a heat absorbing member on the back surface of the carrier, heating a part of the front surface, and measuring the temperature of the opposite part of the carrier. As with a built-in CD-ROM drive device of a personal computer, a built-in personal computer is illustrated as an example, and a stable environment can be formed. Example 2-1

An embodiment of the present invention will be described in detail with reference to the drawings. Fig. 22 shows the combined arrangement configuration with the heat generating member, temperature sensor, and photoreceptor removed, Fig. 23 shows the actual lid closed, and Fig. 24 shows the second 3 The section along line _ 'is shown. 25A and 25B show the carrier, FIG. 25A shows the front surface, and FIG. 25B shows the back surface.

In FIG. 25A and FIG. 25B, 2500 is a carrier and is composed of a rotating body made of polyester, PMMA, PC, PS, PET, PDMS, glass, etc., for example, blood in the center Each reagent reaction tank 2 5 0 is provided via a supply port, a diluent storage part, etc., and a blood cell separation part, a mixing part, a quantification part, a distribution flow path 2 5 0 1 f and a supply flow path 2 5 0 1 c It has a configuration in which a fixed amount of mixed liquid is supplied to lb by adjusting the rotation speed and direction.

The lid portion 25 O la is translucent, and is made of a double-sided adhesive tape, a single-sided adhesive tape, etc., which has a single-sided shape and has a backing member peeled off only on one side, but preferably has a degree of non-deformability. It has a plate shape with a thickness of around 1 mm. Actually, the lid 250 1 a and the carrier 2 5 0 1 shown in FIG. 25A are provided with a supply port for supplying blood from the outside.

25 O l d shown in FIG. 25B is an endothermic member, which indicates a black sheet, a state of black coloration, etc., and at least a color that can form an endothermic state is arranged.

2 5 0 1 e is a measurement hole drilled to optically measure the bottom surface of the reagent reaction tank, and is a window having a diameter slightly smaller than the diameter of the reagent reaction tank.

2 5 1 2 is a metal member for chucking that acts on the magnetic member to attract and repel any member, such as steel, ferrite, other ceramics, plastic, etc. Non-metal and metal composites are shown.

2 5 1 2 a is a recess and extends to the inside of the carrier 2 5 0 1 as shown in FIG.

It is preferable that the lower portion 2 5 0 9 and the upper portion 2 5 10 of the reading device shown in FIG. 24 and the like include a heat insulating member such as a resin to keep the inside warm.

In FIG. 22, reference numerals 2 5 02 a to 2 5 0 2 c denote light sources, which are composed of laser light, LED, etc., and a plurality of light sources are arranged for each primary color.

For example, 2 5 0 2 a is composed of a red light source, 2 5 0 2 b is composed of a green light source, and 2 5 0 2 c is composed of a blue light source. Shown in 3c. 2 5 0 3 a is a red light receiver, 2 5 0 3 b is a green light receiver, and 2 5 0 3 c is a blue light receiver.

These light sources and an optical unit having a pair of photoreceptors are arranged at regular intervals.

2 5 04 is a heat generating member, and has a configuration in which, for example, a halogen lamp is arranged in a light shielding cover having a visible light blocking film 2 5 0 4 b in the irradiation direction.

Reference numeral 2 5 0 5 is a temperature sensor, which measures the surface temperature in a non-contact manner (for example, thermopile).

In FIG. 24, 2 and 5 06 are rotating bodies, and the center part of the upper surface is formed with a rotating shaft 2 5 0 6 c and an annular magnetic member 2 5 0 6 b on the outer peripheral portion Are joined mechanically or by an adhesive or the like, and friction members 25 0 6 a are concentrically formed on the outer periphery.

The height of the friction member 2 5 0 6 a is configured to be higher than the height of the magnetic member 2 5 0 6 b, and when the carrier 2 5 1 2 is mounted on the rotating body 2 5 0 6, the metal member 2 for chucking 5 1 2 and the magnetic member 2 5 0 6 b are not in contact with each other.

The rotating body 2 5 0 6 includes a rotating motor, a transmission and the like as shown in FIG. Connected to the drive means 2 5 1 1.

2 5 0 7 is a heating element lead wire for supplying electric energy to the heating element.

2 5 0 8 is a sensor lead wire for supplying an electrical signal obtained by the temperature sensor to a signal processing device, a microcomputer control conversion means, and the like.

The lead wire for the heating element and the lead wire for the sensor need only be wired in the device, but in these figures, they are extended to the outside for explanation.

Next, the operation of the embodiment shown in FIGS. 22 to 25B will be described. First, a sample such as blood or urine is supplied to the carrier 2500 shown in FIG. 25A, and a diluent is also supplied as necessary.

After the sample is supplied, as shown in FIG. 24, the concave portion 2 of the carrier 2 5 0 1 is placed on the rotating shaft 2 5 0 6 c on the rotating body 2 5 0 6 of the lower part 2 5 0 9 of the reading device. Insert the 5 1 2 a together.

The magnetic member 2 5 Q 6 b of the rotating body 2 5 0 6 and the metal member for chucking 2 5 1 2 try to couple by magnetic force, but the friction member 2 5 0 6 a is the metal member for chucking 2 5 1 2, or carrier 2 5 0 1 Since it contacts the back surface, it is fixed in a non-contact state.

In this state, the driving means 2 '5 1 1 drives the rotating body 2 5 0 6 to rotate.

The friction member 2 5 06 a rotates the carrier 2 5 0 1 to separate blood cells, quantitate, and supply a blood sample to each reagent reaction tank.

As shown in FIG. 22, electric energy is supplied to the heat generating member 2 5 0 4 via the heating element lead wire 2 5 0 7 and joined to the support 2 5 0 1 by the temperature sensor 2 5 0 5. Lid 2 5 0 1 Temperature suitable for the reagent reaction while measuring the surface temperature of the heating element 36.5 ° C to 37.5 ° C Electric energy to 5 0 4 is controlled.

A heat absorbing member 2 5 0 1 d is attached to the carrier 2 5 0 1, and heat is generated on the surface due to local heat generated by the heat generating member from the upper surface. Reaching the target temperature is achieved relatively quickly because it generates heat at 2 5 0 I d.

Next, FIG. 26 shows a specific example of feedback control means for controlling the amount of heat generated by the heat generating member based on the temperature value obtained by the temperature sensor.

2 0 5 0 a is a sensor and corresponds to the temperature sensor 2 5 0 5 shown in FIG.

'2 0 5 0 b is an AZD conversion unit for converting an input analog signal into a digital signal.

2 0 5 0 c is a feedback control unit for comparing the digital voltage information related to the temperature information inputted before and after with the digital voltage information related to the predetermined temperature information to perform feedback output. It is.

A specific example of the feedback control unit 20 50 is shown in FIG.

In Figure 27,

2 0 0 5 a is an input unit and corresponds to the input unit of the feedback control unit 2 0 5 0 c in FIG.

2 0 5 1 a is an adder for adding the previous digital signal value to the currently input digital signal value.

2 0 5 1 b, 2 0 5 1 d, 2 0 5 1 f are multipliers, each of which multiplies the input signal by a set coefficient K1 to K3 and outputs it. is there.

2 0 5 1 c is a storage unit for temporarily storing an input signal. 2 0 5 1 a, 2 0 5 1 b, 2 0 5 1 c, and 2 0 5 1 d constitute a first-order low-pass digital filter.

2 0 5 1 e is a subtraction unit for subtracting a signal input from the threshold voltage V r e f.

In FIG. 26A, 2 0 50 0 d is a D / A converter for converting the feedback digital signal into an analog signal and outputting it, for example, the output of the PWM output unit at the subsequent stage Analog output that controls the pulse width.

2 0 5 0 e is a PWM output unit for adjusting and controlling the pulse width according to the input analog signal value.

For example, the PWM output unit 205 0 e shows a combination of a free-running oscillator that oscillates a sawtooth wave or a triangular wave, a Schmitt circuit having a variable threshold input, and a comparison circuit.

The DZA conversion unit 2500 d and the PWM output unit 2 0500 e can be replaced by one digital PWM circuit 2500 as shown by the dotted line in the figure.

The PWM circuit may be a single program type that is made into a single chip and has an internal memory and CPU. Based on the program, the heating value indication value output from the feedback controller It is effective in that the desired PWM signal can be output directly by outputting the Duty F actor's digital value (eg, 0 to 5 volts), which is almost proportional to, and the circuit can be made compact.

2 0 50 0 f is a heat source, for example, a halogen lamp, a heating wire, a resistor, or the like disposed inside the heat generating member 2 5 0 4 in FIG. Fig. 26B shows an example of the drive circuit for the heat source 20 5 0 when the digital PWM circuit 2 5 0 0 is used.

2 5 0 0 a is the feed pack controller shown in Fig. 2 7 2 0 5 0 c 2 5 0 Ob indicates a switching element such as an FET or a transistor.

The switching element 2 5 0 0 b is turned on / off by the pulse of the digital PWM circuit 2 5 0 0, and current flows from the power input terminal V d to the heat source 2 0 5 0 f during the period when the switching element 2 5 0 0 b is turned on. It generates heat and has a configuration capable of controlling the amount of heat generation by intermittently repeating this heat generation.

Therefore, numerical data indicating the amount of heat output from the feedback controller 2 0 5 0 c is input to the digital PWM circuit 2 5 0 0, and a pulse having a duty factor that is substantially proportional to the numerical data is input to the digital PWM circuit. By outputting 2500, the amount of heat generated by the heat source 2500f can be adjusted variably by simply turning on / off the switching element 2500b. Note that the frequency of the digital pulse output from the digital PWM circuit 2500 is preferably selected, for example, from 10 to 100 kHz, but the heat source, heat generation adjustment, and other Other ranges may be possible due to differences in the elements.

• Next, the operation of the embodiment shown in FIGS. 26A, 26B and 27 will be described with reference to FIGS. 28 and 29. FIG.

While the carrier 2 5 0 1 is rotating, its surface temperature is measured by the sensor 2 0 5 0 a shown in FIG.

The analog sensor signal output from the sensor 20 0 50 a is converted into a digital signal value by the AZD conversion unit 2 0 5 0 b and input to the feedback control unit 2 0 5 0 c.

The temperature data X n input to the input unit 2 0 0 5 a shown in Fig. 2 7 is added to the data obtained by multiplying the previously input temperature data by the coefficient K1 in the addition unit 2 0 5 la. Is output to the multiplication unit 205 I d as the addition temperature data yn. In addition, the temperature data yn added and output from the previous temperature data in the adding unit 2 0 5 1 a is temporarily stored in the storage unit 2 0 5 1 c and the previous temperature data yn--1 Is input to the multiplier 2 0 5 lb, multiplied by the coefficient K1, and output to the adder 2 0 5 la.

The multiplier 2 0 5 1 d forms a multiplication data K2 * yn by further multiplying the input temperature data yn by a coefficient K 2 and outputs the result to the subtraction circuit 2 0 5 1 e.

The multiplication data K2 * yn is subtracted from the preset reference voltage Vref, and further multiplied by the coefficient K3 in the multiplication section 2 0 5 1 ί, and the output section 2 0 0 5 b is multiplied by the multiplication data (K3 * (Vref- (K 2 * yn))) is output.

In other words, if the difference between the value obtained by adding the previous temperature data to the current temperature data and the reference voltage is large, a signal indicating that a pulse with a large pulse width is output is output to the subsequent PWM output section, and the difference is small. As a result, by outputting a signal indicating that a pulse having a small pulse width is output, the temperature information voltage K2 * yn is always adjusted so as to be the same as the reference voltage Vref.

The D / A conversion unit 20 50 d shown in FIG. 26 A performs DZA conversion on the feedback data output from the feedback control unit 20 50 c and is shown in FIG. 28 (a). The PWM output section 2 0 5 0 e shown in Fig. 26 A shows a pulse signal whose pulse width is adjusted based on this analog feedback data (see Fig. 28 (b)). ) Is output to the heat source 2 0 5 Of shown in Fig. 26 A.

In other words, if the difference between the preset reference voltage Vref and the temperature data voltage is large, data based on the difference is output to the connection point 2 0 0 5 b, and the DZA conversion unit 2 in FIG. 0 5 0 d outputs an analog signal based on this data to the PWM output unit 2 0 5 0 e and outputs a pulse having a pulse width based on this analog signal 2 0 5 0 The

According to such feedback, when the surface temperature of the carrier is low, the output of the PWM output unit 2 5 0 5 0 e continuously outputs a pulse with a large pulse width 2 0 5 0 As the temperature reaches around 37 ° C, control is performed to output 50 pulses of a pulse with a small pulse width. Fig. 2-9 shows the output voltage of the sensor (thermopile) 2 0 5 0 a and DZA conversion The relationship of the output voltage of the part 2 0 5 0 d is shown. First, the output voltage of the D / A converter 2 0 50 0 d shown in Fig. 26 A is the maximum voltage, and the pulse width of the output pulse from the PWM converter 2 0 5 0 e is large. As the output voltage of the sensor increases, the output of the D / A converter 2 0 5 0 d also decreases, and the output pulse width from the PWM converter 2 0 5 0 e also decreases. Then, the heat generation amount of the heat source 2 0 50 0 f is reduced to a predetermined temperature 37. C Adjust to around 38 ° C.

When a heat source and a sensor are installed on one side of the carrier α 熱 The heat rays emitted by the heat source may be transmitted directly to the sensor, so the heat generation of the heat source and the timing of measurement by the sensor By repeating (-), it is possible to prevent erroneous sensor measurement and fc is good.

For example, heat generation from the heat source is performed for a predetermined time (for example, 25 seconds to 30 seconds), then the heat generation is stopped, and temperature measurement using a sensor, for example, is performed for 1 second to 5 seconds. Next, the temperature measurement of the sensor is interrupted and heat generation from the heat source is resumed.

The method of repeating this is preferably applied to the present invention.

When heat generation and temperature measurement are repeated alternately, the positional relationship between the heat generation source and the sensor may not be particularly limited.

3rd invention The third invention has the following features.

1. Built-in configuration of diluent reservoir

If the diluent in the present invention is blood, examples thereof include physiological saline, saline, and other solutions for dilution.

The diluting member in the present invention includes, for example, an opening edge of a cup-shaped hard member enclosing a diluting solution, a heat-bonding of a puncturable flexible sheet, ultrasonic welding, a bonding configuration using an adhesive, and the like. The one in which a diluent is put into a bag-like body formed by sex sheet is shown.

In the present invention, “the diluting member for diluting the specimen is arranged vertically movable in the carrier” means, for example, that a part of the lid formed on the carrier is integrally or separately in a thin sheet shape. A configuration in which a circular bellows is formed physically and the center of the bellows is connected to the side opposite to the opening target portion of the diluent reservoir, or an extending member is arranged on a part of the lid portion is shown.

When the diluting member moves downward, the opening member for forming an opening state in the downward direction of the diluting member is, for example, a puncturing member provided for a puncturable region of the diluting member, An example is one in which a part of the diluent member is fixedly connected so that a part of the diluent member is broken due to the displacement of the diluent member.

2. Stirring structure 1 "In this invention," an annular concavo-convex member formed by forming unevenness partially or entirely on one or a plurality of one or more of the side surface, top surface and bottom surface " Triangular, rectangular or circular pitches on the surface of the carrier, at least in the vicinity of the part where mixing and stirring are performed, showing continuous or partially continuous irregularities formed depending on the magnitude of vibration. Therefore, it is preferable that these irregularities have such a height that the magnitude of vibration does not affect other components.

A vibrating body that touches the unevenness and vibrates is in contact with the unevenness only when necessary. It is preferable that a touching state is formed, and it is preferable that a moving means that moves only at the timing is also provided, but there may be a case where it is manual.

3. Stirring configuration 2

The stirring member that is deformed inward by the rotation of the carrier in the portion that needs to be stirred accommodated in the carrier has a portion that can be moved by centrifugal force at least in the region where mixing and stirring is performed. If there is no centrifugal force, or if it is below a certain rotation (eg 700 RPM or less), it is preferable that the original position is restored and fixed so that there is no hindrance to the measurement.

The stirring member is preferably formed in a state in which it is movably attached to the inside of the stirring member with, for example, rubber or resin.

In addition, it is preferable that an iron ball, a plastic ball or the like having a different mass is connected to the rotatable portion.

4. Chucking configuration

The metal member in the present invention may be any member (such as a stainless plate or a copper plate) that can be coupled to the magnetic member. ''

The magnetic member in the present invention is preferably annular around the rotating body, but may be a part of the magnetic member when the magnetic force is strong.

The friction member in the present invention may be formed of natural rubber, artificial rubber, resin, or the like, and may be a metal member or a member having a large friction with the carrier surface.

In addition, when using a friction member as a reference surface, it is preferable to have non-deformability.

The annular convex member in the present invention may be any member that has at least a height and an inner area so as to uniformly contact the side surface of the rotating body, and is preferably formed integrally with the carrier. The metal member on the bottom surface of the carrier only needs to have an attractive force between the magnetic material, steel, magnetic stainless steel, etc., metal-ceramic composite, metal-plastic composite, magnetic metal, magnetic metal , Plastic, 'paper, ceramics, composites with non-magnetic metals. In the present invention, the contact portion between the carrier and the rotating body is formed by a friction member, and the coupling is performed by the magnetic force acting between the magnetic member and the metal member in a non-contact state. The distance between the magnetic member and the metal is 0.1 to 1.0 mm is exemplified. Example 3— 1

An embodiment of the present invention will be described in detail with reference to the drawings.

'FIG. 3 O A to FIG. 30 C are sectional views showing an embodiment of the present invention.

3 1 0 1 is a sheet-like lid, which is made of a translucent member such as PP, PET, or polyester, or a semi-translucent member, and uniformly covers the surface of the blood analysis carrier. It can be pasted with materials, etc. For the lid part 310, a transparent double-sided tape or a single-sided tape is preferable in terms of easy handling.

3 1 0 2 is a carrier substrate, which is made of a translucent member such as PP, PET, or polyester, or a semi-translucent member, and is formed by a groove formed on the surface. Configure the flow path, mixing tank, etc.

In FIGS. 3A to 30C, only the diluent reservoir holding space is shown.

3 1 0 3 is a bellows portion, and a part of the collar portion 3 1 0 1 is processed into a concentric bellows.

3 1 0 4 is a diluent reservoir, a hard force cup 3 1 0 6 that opens downward, and a thin film that is connected to the periphery of the opening surface of this hard cup by thermocompression bonding or adhesive 3 1 0 7 has a combined structure.

3 1 0 5 is a diluting solution and consists of physiological saline. Contains various additives such as preservatives.

3 10 8 is a locking member, which is formed integrally with the carrier, and can be deformed outward from the center, and can be inserted into the diluent reservoir in two directions, four directions, Provided in other directions.

3 10 9 is a puncture member, preferably constructed integrally with a carrier, and preferably has a hardness and an acute angle that can puncture and break the thin film 10 7.

3 1 10 is a flow path for the diluent, and is exemplified by a groove shape and a flow path that is somewhat wide.

Next, the operation of the embodiment shown in FIGS. 30A to 30C will be described. Prior to use, the diluent reservoir is fixed to the inside of the distal end of the locking member 3 10 8 while being coupled to the central portion of the bellows 3 1 0 3.

When blood is introduced into the carrier and used, the upper part of the diluent reservoir 3 10 4-is pressed (F) as shown in FIG. 30B. The pressing force F causes the edge of the diluent reservoir 3 1 0 4 to push the locking member 3 1 0 8 outward and open the diluent reservoir 3 1 0 4 to the piercing member 3 1 0 Press in the 9 direction. As the bellows 3 1 0 3 extends, the diluent reservoir 3 1 0 4 moves, and the thin film 3 1 0 7 of the diluent reservoir 3 1 0 4 is punctured by the puncture member 3 1 0 9 At the same time, it is locked and fixed inside the locking member 3 1 0 8.

As shown in FIG. 30 C, the carrier substrate 3 1 0 2 rotates around the central axis 0. The thin film 3 1 0 7 is broken, and the diluent B is exposed to the outside and moved outward by centrifugal force.

Since the carrier substrate 3 1 0 2 and the lid 3 1 0 1 were originally sealed, the thin film 3 1 0 7 of the dilution reservoir 3 1 0 4 was broken and the internal dilution was exposed. However, it is safe and stable without leaking outside. Example 3-2

FIG. 31 is a schematic diagram showing another embodiment of the present invention.

3 2 0 1 is a disc-shaped carrier, which has a blood supply part in the center, a blood cell separation part, a mixing part with diluent, a quantification part, a blood cell separation part, and a reagent reaction tank 3 2 O la There are several.

Reference numeral 3 2 0 2 is a coupling hole for coupling to the carrier operating device, and is drilled twice at a predetermined interval from the center.

3 2 0 3 is a concavo-convex portion, and has, for example, a sawtooth wave shape and a triangular wave shape. The pitch and height of the unevenness are not particularly limited, but if the pitch is short, fine vibrations can be generated, and if the pitch is long, large vibrations can be generated.

3 2 0 4 is a drive unit for slidingly driving a vibrating body composed of a combination of a vibration convex part 3 2 0 5 and a leaf spring-like elastic member 3 2 0 6. The state which incorporated etc. is shown.

The combination of the convex portions for vibration 3 2 0 5 of the vibrator and the elastic members is merely an example, and various shapes are appropriately selected depending on the size of the carrier reader.

Next, the operation of the embodiment shown in FIG. 31 will be described. When stirring operation is required, drive part 3 2 0 4 is driven to bring vibrator's vibration convex part 3 2 0 5 into contact with uneven part 3 2 0 3 (see Fig. 3 (b)) .

As shown in Fig. 31 (c), the convex portion for vibration 3 2 0 5 force in contact with the concave and convex portion 3 2 0 3 of the carrier is pushed outward by the crest of the rotating carrier (Fig. 3 1 (d )), And when the trough comes due to the movement of the uneven portion 3 2 0 3, the vibration convex portion 3 2 0 5 becomes the uneven portion 3 of the carrier 3 2 0 1 by the restoring force of the elastic member 3 2 0 6. Vibration is given by hitting the surface of 203 (see Fig. 31 (e)). By repeating this, continuous vibration is generated around the plurality of outer peripheral reagent reaction tanks 3 2 0 la to increase the stirring motion.

Example 3 — 3

FIG. 32 is a schematic diagram showing another embodiment of the present invention.

FIG. 32 (a) is, for example, the back surface of the blood analysis carrier 3 201 shown in FIG. 31 (a), and a black member having absorptivity and endotherm in the region around the reagent reaction tank. 3 2 1 0 is arranged, and an observation window 3 2 1 0 a for allowing measurement light to pass is provided immediately below the reagent reaction tank.

3 2 0 7 shown in FIG. 3 2 is an annular concavo-convex portion, and a part thereof is shown in FIG. 3 2 (b). FIGS. 32 (b) and 32 (c) are views of the carrier 3220 from the side.

3 2 0 9 shown in FIG. 3 2 (c) is a vibration convex portion, and 3 2 0 8 is an elastic member.

Similarly to the embodiment shown in FIG. 31, this embodiment also has a moving portion for bringing the vibrating convex portion 3 2 0 9 into contact with the annular concave and convex portion 3 2 0 7. Omitted in Figure 32. .

In the embodiment shown in FIG. 32, as in the embodiment shown in FIG. 31, the vibration convex portion 3 2 0 9 moves on the surface of the annular uneven portion 3 2 0 7 (FIG. 3 2 (d )), And the convex part of the annular concavo-convex part 3 2 0 7 pushes the vibration convex part 3 2 0 9 (see FIG. 32 (e)), and the carrier 3 2 0 1 rotates to make the annular part When the concave portion of the concave / convex portion 3 2 0 9 comes to the pressed portion of the vibrating convex portion 3 2 0 9, the restoring portion of the elastic member 3 2 0 8 causes the vibrating convex portion 3 2 0 9 to Vibration is generated by striking the annular uneven part 3 2 0 7 (Fig. 3 2 (see Π)).

In this way, the reagent and the plasma component can be agitated and mixed reliably by applying vibration to the carrier.

Example 3-4 FIGS. 3A to 3C are other embodiments of the present invention.

FIGS. 3A to 3C show an enlarged state of the reagent reaction tank 3 2 0 1 a shown in FIG. 3 1, for example.

3 3 0 1 is a reagent reaction tank, which is formed as a cylindrical recess in the carrier. The size is exemplified by a diameter of 1 and a depth of about 2 mm, and a supply channel 3 300 for supplying a sample such as plasma is connected to the inner surface in the center direction. The reagent reaction vessel contains reagent powder, granules, liquid, etc. in advance.

3 30 3 is a stirring ring formed of an elastic material such as rubber or resin, and connected and fixed to the inner periphery of the reagent reaction tank 3 30 1 except for a part in the center direction.

3 3 0 4 is a metal particle composed of relatively heavy particles such as metal, and is embedded and arranged in a site that receives the centrifugal force most effectively generated by the rotation of the carrier. ·

The cross section indicated by the line XX 'in Fig. 3 3B is shown in Fig. 3 3C. The stirring ring 3 3 0 3 is disposed between the bottom surface of the reagent reaction tank 3 3 0 1 and the flow channel opening of the supply flow channel 3 3 0 2.

Reference numeral 3 3 0 5 denotes a lid, which is made of a translucent member such as PP or PET, or a semi-translucent member.

Reference numeral 3 3 06 is a black sheet, which has endothermic and light absorbing properties, and an observation hole 3 3 0 7 for allowing measurement light to pass therethrough is formed immediately below the reagent reaction tank.

Next, the operation of FIGS. 3 3A to 3 3 C will be described.

The sample is supplied into the reagent reaction tank 3 30 1 and comes into contact with the pre-arranged reagent to start dissolution.

By increasing the rotation of the carrier, the stirring ring in the reagent reaction tank 3

3 0 3 is a part that is not joined in the reagent reaction tank due to centrifugal force And the part containing the metal particles 3 3 0 4 moves in the centrifugal direction. At that time, as shown in FIG. 3 3 B, a gap is formed in the stirring ring 3 3 0 3 and the reagent reaction tank 3 3 0 1, and the sample or the like flows into this portion. .

When the number of rotations of the carrier is reduced, the stirring ring 3 3 0 3 returns to its original position, and the specimen, etc. that enters the gap returns to its original position so that it is pushed out (No. 3 3

(Figure A)

By repeating the above operations, stirring can be easily performed without any problem in optical measurement.

Embodiment 3-5 Hereinafter, a portion where a carrier according to an embodiment of the present invention is attached to a carrier reader, that is, a chucking configuration will be described in detail.

In Figures 3 4 A to 3 4 C,

3 4 0 1 is a carrier, in which a blood supply port, a diluent storage part, a blood cell separation part, a mixing and stirring part, a quantitative distribution part, a reagent reaction tank, etc. are formed in a groove shape or a concave shape on a disk-shaped substrate. ing.

On the upper part of the carrier 340, a light-transmitting lid is disposed so as to cover the whole.

FIG. 34 shows an example of the reagent reaction vessel 3 4 0 4 among the constituent elements configured on the carrier 3 4 0 1.

Reference numeral 34 0 2 denotes an annular convex portion, which is an annular body having an inner diameter that coincides with the side surface of the rotating body 3 4 0 5, and is preferably formed integrally with the carrier 3 4 0 1.

3 4 0 3 'is a metal member, which is made of a thin plate of metal, ceramic, or other composite material that can be combined with a magnetic material, and is the bottom surface of the carrier 3 4 0 1, which is an annular convex portion 3 4 0 The inside of 2 is connected by adhesive, mechanical fitting, etc. The metal member 3 4 0 3 preferably has a high friction coefficient. It is preferable to have a rough surface.

3 4 0 5 is a rotating body, and is connected to a motor gear, a transmission gear, etc. on the bottom surface. The rotating body 3 4 0 5 is formed of resin or plastic, and it is preferable to reduce the weight. The rotating body 3 4 0 5 is arranged in a reading device (not shown), and a part thereof is shown in FIGS. 3 4 A to 3 4 C.

3 4 0 6 is a friction member, which is formed of an annular rubber, vinyl resin, etc., and protrudes uniformly from the upper part of the rotating body 3 4 0 5 and is bonded and arranged by an adhesive, mechanical fitting, etc. . If the width of the annular friction member 3 4 0 6 is wide, the contact area with the carrier 3 4 0 1 will be wide and the frictional force will be strong, but about 1 to 3 mm is preferable for driving the carrier.

3 4 0 7 is a magnetic member, which is formed of a permanent magnet or an electromagnet formed in an annular shape. If the width of the magnetic member 3 4 0 7 is wide, the bond with the carrier becomes dense, but 2 to 4 mm is suitable for easy handling.

In some cases, the width of the magnetic member 3 4 0 7 and the width of the friction member 3 4 0 6 are more suitable than the above ranges depending on the surface condition of the carrier, the material of the magnetic member, and the like.

The height of the magnetic member 3 4 0 7 is lower than that of the friction member 3 4 0 6, and even when the carrier is mounted as shown in FIG. 3 4 B, the metal member of the carrier is in a non-contact state. Forming.

3 4 0 8 is a rotating body convex portion, and is formed integrally with the rotating body 3 4 0 5, and the outer peripheral side thereof is in contact with and coupled to the inner peripheral side surface of the annular convex portion 3 4 0 2. The vertical reference plane 3 4 0 8 a is formed.

A contact surface between the upper surface of the rotating body projection 3 4 0 8 and the metal member 3 4 0 3 forms a horizontal reference surface 3 4 0 8 b. Both vertical reference plane 3 4 0 8 a and horizontal reference plane 3 4 0 8 b

It is a uniform contact with the bottom surface of 3 4 0 1 and maintains a perpendicular relationship with each other, thereby causing a stable rotation of the carrier 3 4 0 1.

In the embodiment shown in FIGS. 3 4 A to 3 4 C, the rotating body 3 4 0 5 in the reader is inserted inside the annular projection 3 4 0 2 of the carrier 3 4 0 1, and the vertical reference Surface 3 4 0 8 a and inner surface of annular projection 3 4 0 2 and horizontal reference surface 3

4 0 8 b and the metal member 3 4 0 3 are in contact with each other and the friction member 3 4 0 6 and the metal member 3 4 0 3 are in contact with each other, the magnetic member 3 4 0 7 and the metal member 3 4 0 By magnetically coupling the three members in a non-contact state, the rotating body 3 4 0 5 and the carrier 3 4 0 1 in the reading device are coupled and fixed.

Figure 34 shows the combined state. At that time, stable rotation is performed by uniform contact of the vertical reference plane 3 4 0 8 a and the horizontal reference plane 3 4 0 8 b to the respective carriers 3 4 0 1, and the rotating body 3 4 0 5 Also in the case of rotation, the carrier 3 4 0 1 rotates without slipping due to the contact friction of the friction member 3 4 0 6.

Thus, by simply inserting the annular convex portion 3 4 0 2 of the carrier 3 4 0 1 into the rotating body 3 4 0 5, the chucking is completed, and the magnetic member 3 4 0 7 and the metal member 3 4 are also removed. 0 3 is not in contact, so it can be easily removed.

FIGS. 35A and 35B are the same as those shown in FIGS. 34A to 34C except that the carrier 3 4 0 1 provided with the annular projection 3 4 0 2 is used. An example of is shown.

FIG. 3 5 Stepped coupling portion 3 4 0 9 is formed on the outer periphery of rotating body 3 4 0 5 shown in FIG. 3A, and the lower surface of coupling portion 3 4 0 9 and the tip of annular projection 3 4 0 2 The end plane part comes into contact to form the horizontal reference plane 3 4 0 9 a shown in FIG. 3 6 B, and the side part of the coupling part 3 4 0 9 and the inner side part of the annular convex part 3 4 0 2 are in contact with each other Thus, the vertical reference plane 3 4 0 9 b shown in FIG. 3 6 B is formed. 3 4 0 6 is a friction member, which has the same configuration as that shown in FIGS. 3 4 A to 3 4 C, and 3 4 0 7 is an annular magnetic member, It has the same configuration as that shown in FIGS. 34A to 34C. The height of the magnetic member 304 is preferably maintained at such a level that it does not come into contact with the metal member 304 even when the friction member 304 is coupled and contracted. FIG. 35B shows a state in which the carrier 3 4 0 1 and the rotating body 3 4 0 5 are combined. Although it is a simple coupling relationship, the coupling force due to the coupling of the magnetic member 3 4 0 7 and the metal member 3 4 0 3 and the frictional force between the friction member 3 4 0 6 and the bottom surface of the carrier can be used even in a severe rotational environment. Stable rotation is achieved without slipping.

The embodiment shown in FIGS. 35A and 35B simplifies the configuration of the horizontal reference plane and the vertical reference plane more than the embodiment shown in FIGS. 34A to 34C. The carrier 3 4 0 1 can be easily coupled to or detached from the rotating body 3 4 0 5.

Example 3-6

FIGS. 36A to 36C are diagrams showing another example of the chucking configuration of the present invention.

In FIGS. 3 6 A to 3 6 C, 3 4 0 1 is a carrier, and has the same structure as that shown in FIGS. 3 4 A to 3 4 C. As shown in Fig. C, it consists of a combination of reagent reaction tank 3 4 1 3 and distribution channel.

3 4 1 1 is a metal member, and is preferably embedded in the bottom surface of the carrier 3 4 0 1. In the center of the metal member 3 4 1 1, a soot entrance 3 4 1 0 is formed which partially communicates with the carrier 3 4 0 1.

If the rod inlet 3 4 1 0 is formed in a columnar shape, the rotating shaft 3 4 1 6 of the rotating body 3 4 1 2 can be inserted.

3 4 1 2 is a rotating body, and the projecting rotating shaft 3 4 1 6 is at the center. Is formed. The side surface of the rotating shaft 3 4 1 6 forms a vertical reference surface 3 4 1 6 a shown in FIG. 3 6 B in the state of being inserted into and contacted with the insertion port 3 4 10.

3 4 1 7 is a friction member, which is formed of a material having a high coefficient of friction and elasticity, rubber, natural resin, synthetic resin, and the like. The friction member 3 4 1 7 in this example is a portion where the friction member 3 4 1 7 and the bottom surface of the carrier 3 4 0 1 are in contact with each other. The horizontal reference surface 3 4 shown in FIG. In order to form 17a, it is preferable to have non-deformability as much as possible, and a harder member is preferable.

In this embodiment, it is preferable that a friction member 3 17 having a relatively wide width is disposed as compared with the other embodiments, and the width is exemplified by a width of 3 to 5 mm, for example. It may be set outside this range depending on the state and size of the bottom surface.

3 4 1 4 is a magnetic member, which is formed by a permanent magnet and an electromagnet, and is arranged at a height lower than that of the friction member 3 4 1 7.

The embodiment shown in FIGS. 36A to 36C is a simplified version of the embodiment shown in FIGS. 34A to 34C and FIGS. 35A and 35B. is there. When the rotating shaft 3 4 1 6 of the rotating body 3 4 1 2 is inserted into the insertion port 3 4 1 0 of the carrier 3 4 0 1, the magnetic coupling between the metal member 3 4 1 1 and the magnetic member 3 4 1 4 is in a non-contact state. The vertical reference surface 3 4 1 6 a shown in FIG. 3 6 B is formed by contact between the side surface of the rotating shaft 3 4 1 6 and the side surface of the inlet 3 4 1 0 and the carrier 3 4 0 1 And the friction member 3 4 1 7 are in frictional contact with each other to form a horizontal reference surface 3 4 1 7 a shown in FIG. The rotation of the rotating body 3 4 1 2 is transmitted to the carrier 3 4 0 1, and in response to the severe rotation of the carrier 3 4 0 1 that changes the direction of rotation, stops it, or starts a sudden rotation. However, stable rotation can be achieved without blurring. Example 3-7

FIGS. 37A and 37B are sectional views showing another embodiment of the present invention.

In FIGS. 37A and 37B, the carrier 3400 is the same as the carrier in FIGS. 36A to 36C, and the same reference numerals are given and description thereof is omitted. . Similarly for the rotating body 3 4 1 2, the same numbers are assigned to the same parts as in the other embodiments, and the description thereof is omitted.

An annular projection 3 4 1 8 is attached to the upper outer peripheral surface of the rotating body 3 4 1 2.

7 and ¾¾-shaped convex portion 3 4 1 '8 is in contact with the bottom surface of carrier 3 4 0 1 / | ¾¾, 3 7B forming horizontal reference surface 3 4 1 8a as shown in FIG. It is a part to do.

The friction member 3 4 1 9 is the same as the friction member of the embodiment shown in FIGS. 3 4 A to 3 4 C, 3 5 A and 3 5 B.

It is made of annular rubber, vinyl resin, etc.

3 4 1 4 is a magnetic member, FIGS. 3 4 A to 3 4 C, 3 5

The same material as Fig. A, Fig. 35B and Fig. 36 A to Fig. 36C

It has a shape.

'The height of magnetic member 3 4 1 4 is lower than that of friction member 3 4 1 9

When the carrier and the rotating body are combined, the magnetic member 3 4 1 4 is also the carrier 3 4 0

1 Metal member 3 4 1 1 Keep in a non-contact state.

The side surface of the rotating shaft 3 4 1 6 formed integrally with the center of the rotating body 3 4 1 2 is inserted into the inlet 3 4 1 0 of the carrier 3 4 0 1. The vertical reference surface 3 4 1 6 a is formed.

The embodiment shown in FIGS. 37A and 37B is similar to that shown in FIGS. 36A to 36C. Just by inserting it into 3 4 1 0, the magnetic member 3 4 1 4 and the metal member 3 4 1 1 are coupled by magnetic coupling, and as shown in Fig. 3 7 B, the rotating body 3 When the upper surface of the annular convex part 3 4 1 8 arranged on the outer periphery of 4 1 2 comes into contact with the carrier 3 4 0 1, the horizontal reference surface 3 4 1 8 a is formed, and the side surface of the rotating shaft 3 4 1 6 Since the contact surface with the inner peripheral surface of the inlet 3 4 10 forms the vertical reference surface 3 1 6 a, the stable support and the rotating body can be coupled. 4th invention

(4) The micro space in the invention of (4) is, for example, a cylindrical reagent reaction tank of a type in which a reagent is stored, a quantitative specimen is supplied from the outside, and color is developed by mixing, However, the present invention is not limited to this, and the present invention is not limited to this, but can be applied to a part intended only for mixing.

Substances with different specific gravities include, for example, body fluids such as blood, body fluids and urine, and solids

Examples include mixing of powdered and granular reagents, and other liquids having different concentrations.

Centrifugation does not occur in a relatively short time, and the rotation speed at which the acceleration required for stirring is given for a predetermined time is the rotation speed at which centrifugation does not occur in a relatively short time. The predetermined time is approximately 1 Examples are around seconds. In other words, this rotational speed indicates the vicinity of the rotational speed boundary where separation by centrifugal force occurs in a relatively short time, and the rotational speed at the boundary is the degree of difference in specific gravity, viscosity, from the rotational center. Although it depends on the distance, etc., it is sufficient that the number of rotations is at least so that the centrifugal separation does not occur immediately.

The “opposite direction” indicates counterclockwise rotation when the previous rotation is clockwise.

The rotation speed is increased from a state where the target rotational speed is reached to a rotational speed in which the direction is different and the rotational speed is such that separation by centrifugal force does not occur in a relatively short time. The target number of revolutions is adjusted as appropriate according to the substance to be mixed, the difference in specific gravity, and the mixing time. It is arranged and not limited. .

Specifically, for example, when the minute space for mixing is about 2 to 3 cm away from the center of rotation on the carrier, the number of rotations is first increased clockwise from 0 rpm to 200 rpm. Then, after the rotation speed reaches 2 00 rpm, this is continuously increased counterclockwise until 2 0 00 rpm, and after reaching 2 0 00 rpm, it switches to reverse rotation again. It is shown that the change is continuously increased to 200 rpm in a clockwise direction, and this is repeated at intervals of several hundred msec to several sec.

The time from the maximum rotational speed in one direction to the maximum rotational speed in the opposite direction is from 0.1 msec to 2 sec, preferably from 0.5 sec to L sec (in terms of relatively gentle mechanical conditions. This is preferable in that an inexpensive apparatus is used.

In addition, by devising the shape of the reaction / measurement chamber, for example, when measuring while rotating at 600 rpm or higher, liquid collects or sticks to a part of the measurement chamber (like the outer wall). If measurement is enabled and rotation is stopped (or the rotation speed is reduced), the liquid spreads to the bottom of the measurement chamber, and this change in the shape of the liquid is repeated. And allows measurement during rotation.

The number of recovery channels is not particularly limited as long as it is two or more, but two may be sufficient depending on the case where the carrier is smaller or the purpose of use.

In the present invention, the “circumferential supply channel” refers to, for example, a tangential direction with respect to the circumference, and is not limited to being perpendicular to the radial direction, but approximately ± 30 ° with respect to the vertical. If it is the range.

According to the present invention, “a flow path having a capillary force, and at least from the input port, the output port has a linear portion parallel to the diameter, and the liquid is moved and stopped by adjusting the rotation speed of the carrier. ”Means diametrically Flow paths on parallel straight lines are shown. It should be noted that at least the center of rotation of the carrier may be parallel to the diametrical direction, and there may be a bent portion that faces in all directions before and after that.

Further, according to the present invention, a flow path having a capillary force can be stopped and started by adjusting the number of revolutions even when the output port extends in the circumferential direction from at least the input port. And The direction extending in the circumferential direction is a flow path having the same curvature as the circumference, and indicates a state of extending on the circumference, but the curvature does not necessarily have to coincide with the circumference. Even if the curvature is somewhat large and vice versa, it can be used as a switch to control the flow of liquid.

Example 4-1

FIG. 38 is a schematic diagram for explaining one embodiment of the present invention.

4 1 1 8 is a first supply flow path, and a plurality of reagent reaction tanks 4 1 1 6 are connected to each other in the outer circumferential direction through a quantitative tank 4 1 1 4 and a quantitative supply path 4 1 1 5. Figures 38A to 38C show an example of the overall configuration of one of the reagent reaction tanks, as shown in Figure 43. At this time, the diameter of the outermost periphery of the carrier 4 1 0 0 is 6 0 Din! About 70 mm. Figures 3 A to 3 & C are part of it, so they have the same number.

38 1, 4 1 1 4 shown in FIG. 3A is a quantification tank, and is a part for securing a volume of specimen together with the volume of the quantification supply channel 4 1 1 5. . 4 1 1 5 is a constant supply channel, extending in the circumferential direction. The direction of the fixed supply flow path is exemplified by a tangential direction, but is not limited thereto, and may be inclined at about + 0 ° to 30 ° with respect to the tangential line. ·

4 1 1 6 is a reagent reaction tank in which dry or liquid reagent SY is enclosed in advance or supplied at the time of use. 4 1 1 6 a is a reaction region, which is formed by a cylindrical recess as shown in FIG. 3 8 B. The size is, for example, 1 mm in diameter and about 3 mm in height.

4 1 1 6 b is an air reservoir, and the height is about half the height of the reaction region, and is formed in the same range as the reaction region.

FIGS. 39A to 39E illustrate an example of a state in which the specimen is quantitatively supplied to the reagent reaction region.

First, the carrier rotates in one direction, and the specimen 3 A flowing through the first supply channel 4 1 1 8 is filled in the quantification tank 4 1 1 4 according to the rotational force ( (See Figure 39 A).

The sample supply path 4 1 1 5 is also filled with the specimen 3 B, and the state shown in FIG. 39B is formed. The volume of the specimen 3 B quantified at this time is an amount satisfying the reaction region 4 1 1 6 a, but may be smaller than an amount satisfying all 4 1 1 6 a and 4 1 1 6 b.

Depending on the reaction mechanism of the reagent, its properties, or depending on the purpose, part of the necessary reagent is also enclosed in this quantification tank, and mixing with the supplied sample or primary reaction is performed. It may be performed in a quantification tank. As an example, a so-called two-reagent reaction system that is stored in a physically or chemically separated state in order to prevent conflict between reagent components during storage is assumed.

Next, the rotational speed is increased to about 5 0 0 0 to 6 0 0 0 r pm. As a result, the specimen 3 C is filled into the reagent reaction region as if it was pushed (see FIG. 39C).

In this state, a sample liquid (unmixed) containing the solid or liquid reagent SY supplied in advance or immediately before use as shown in FIG. 38B is formed.

Next, the carrier is rotated as shown in FIGS. 40A to 40C. For example, the rotation shown in Fig. 4 OA is initially clockwise. Rotate the body.

When the first clockwise rotation reaches 1500 rpm at the predetermined angular acceleration, the rotational speed is decreased at the predetermined angular acceleration, and when the rotational speed reaches 0, the counterclockwise direction is 1 After increasing to 500 rpm with a predetermined angular acceleration and reaching 1500 rpm, the rotational speed is decreased at a predetermined angular acceleration to zero, and then rotated clockwise. Repeat. Thereby, sufficient mixing is performed for 10 to 120 seconds.

It should be noted that the period P 1 at this time is an appropriate force for 1 to 2 sec. As shown in Fig. 40B, even if the period P 2 is lengthened, the time until stirring and mixing is slightly increased. In some cases, sufficient mixing can be expected, and it is adjusted appropriately according to the size of the reaction vessel.

It should be noted that the shift to the above-described rotation speed and the shift to the lower limit rotation speed based on the predetermined angular acceleration may be performed by linear increase, decrease, and exponential increase / decrease.

In addition, the expression by angular acceleration is an example, and at least rotation from the lower limit rotation speed to the upper limit rotation speed or from the upper limit rotation speed to the lower limit rotation speed in the above-described manner in a manner as described above. Anything that can be achieved.

Furthermore, as shown in FIG. 40C, there may be a case in which strength is increased with a predetermined angular acceleration in one direction of clockwise or counterclockwise without alternating. In other words, a positive acceleration and a negative acceleration may be added alternately.

In addition, the waveform indicating the change in rotation in FIGS. 40A to 40C is shown as a sawtooth DC or alternating wave, but is not limited to this, and is rectangular, triangular function wave, intermittent triangle. It may be a change in the number of rotations corresponding to a waveform such as a wave, intermittent rectangular wave, intermittent sine wave, direct current or alternating wave.

Figures 40A to 40C show that the angular acceleration is continuous and constant. In some cases, however, it may be possible to stop the rotation once after increasing to a certain rotation and then increase it again to a certain rotation in the opposite direction. At this time, the range of acceleration given to the liquid in the reaction tank is preferably 10 to 500 m / s ^2, but is not particularly limited. FIG. 38 The shape of the embodiment shown in FIG. For example, an elliptical reagent reaction vessel 4116f as shown in Fig. 38C may be used.

In the case of an elliptical reagent reaction vessel 4 1 1 6 f, the sample volume to be quantified is filled slightly less than the volume of 4 1 1 6 f, so that the 3 8 As shown by 4 1 1 6 fa in Fig. C, an air reservoir can be created, and the optical path length can be secured for optical measurement using the optical unit arranged in the outer circumference.

Further, in the present invention, simple stirring can be realized by increasing the amount of empty space remaining in the reagent reaction tank and increasing or decreasing the number of rotations.

Figures 39D and 39E show cross sections along line Y—Y 'in Figure 38C.

TA is a carrier and is similar to the carrier 4 100 shown in FIG. 43, and is made of transparent, translucent acrylic, PET, PP, polyester resin, or the like.

FT is a lid, made of the same material as the carrier TA, and made of an acrylic thin plate coated with double-sided or single-sided adhesive tape, adhesive, and adhesive.

Fig. 39D shows the state in which the sample 4 1 1 6 fb is rotated at a low speed (rotation of 600 rpm or less) with all or part of the reagent reaction vessel 4 1 1 6 supplied. It is in a stationary state.

4 1 1 6 fa is a reservoir and SY is a solid reagent, for example. is there.

Next, set the rotation speed to 60 rpm or more. Specimen 4 1 1 6 f b is biased to the outer wall surface of reagent reaction vessel 4 1 1 6 ί by centrifugal force as shown in Fig. 39E.

When the rotational speed is lowered again to below 600 rpm or stationary, the state shown in Fig. 39D is obtained.

By alternately repeating these two states, the reagent S Y and the sample 4 1 1 6 f b can be efficiently stirred.

In addition, the influence of the capillary force of the quantitative supply channel 4 1 1 5 on the sample 4 1 1 6 fb is lower due to the air in the air reservoir 4 1 1 6 fa, so the sample moves to the quantitative supply channel 4 1 1 5 Without mixing, the sample is mixed only by centrifugal force.

Fig. 39D and Fig. 39E show the method of mixing by causing the liquid to move due to the change in centrifugal force generated by increasing / decreasing the number of revolutions. Similarly to the above, after increasing to a predetermined number of rotations, rotation with angular acceleration that rotates in the opposite direction may be given to the carrier, or it may be temporarily stopped.

In this case, the relationship between the increase / decrease of the rotation speed and the increase period and the decrease period may be performed with the same value as in the other examples, and at least the same acceleration may be given to the liquid.

Example 4 1 2

An embodiment of the present invention will be described with reference to FIG. 41 and FIGS. 4 2A and 4 2B.

The configurations shown in FIG. 41, FIG. 4 2 A, and FIG. 4 2 B show part of the overall configuration of the carrier shown in FIG.

4 1 1 8 is the first supply flow path, which is substantially concentric with the disc-shaped carrier. It is formed by an arcuate channel. Since it is a substantially concentric arc, it is not always necessary to have a concentric curvature, as long as it can obtain a good distribution of plasma components during carrier rotation.

However, it is preferable that the outer wall of the first supply channel 4 1 1 8 be concentric with the center of rotation of the carrier when discharging excess samples or performing quantification in the quantification tank.

4 1 1 7 a is a surplus sample storage part for storing a surplus sample after each quantification tank 4 1 1 4 is filled with a sample, and has two substantially arcuate shapes in the outer circumferential direction. The first surplus accommodating part 4 1 1 7 aa and the second surplus accommodating part 4 1 1 7 ac and the connecting path 4 1 1 7 ab connecting these accommodating parts are located at the end of the supply channel. One or both of them are connected via a flow path 4 1 1 7 ad for the excess storage section.

The position of the excessively diluted mixed liquid container 4 1 1 7 a is not limited to the end of the supply flow path, but may be in the center or the like.

The connecting channel 4 1 1 7 ab is sharpened at the connection point with each surplus accommodating portion, and prevents leakage of surplus liquid due to backflow into the first supply channel 4 1 1 8.

4 1 1 4 shows one of each of the quantification tanks, arranged at equal intervals or unequal intervals on the outer periphery of the first supply channel 4 1 1 8, and the volume indicates the target liquid amount .

4 1 1 5 is a fixed supply channel, which extends in the circumferential direction and substantially tangentially.

4 1 1 6 a is a reaction area, a reagent is arranged inside, and is connected to the quantitative supply channel 4 1 1 5 through an air reservoir 4 1 1 6 b.

The configuration from the quantification tank 4 1 1 4 to the reaction zone 4 1 1 6 a has a configuration as shown in FIG. 38B, for example.

Fig. 4 Operation of the configuration shown in Fig. 1 is shown in Fig. 4 2 A and 4 2 B. This will be described in detail with reference to the drawings.

The sample supplied to the first supply channel 4 1 1 8 is in a state where the carrier is rotating, and the remaining sample that is filled and held in the quantification tank 4 1 1 4 by centrifugal force or the like is stored in excess. 4 1 1 7 a via the second surplus storage section 4 1 1 7 ac through the ad and to the first surplus storage section 4 1 1 7 aa through the connection path 4 1 1 7 ab Is done.

While any sample tank 4 1 1 4 is filled with the sample, and the sample supply channel 4 1 1 5 is also filled with the sample, the rotation speed is increased and the sample is supplied to the reaction region 4 1 1 6 a. To do.

In order to mix the reagent in the reaction region 4 1 1 6 a and the sample, rotation with the angular acceleration increased or decreased alternately as shown in FIGS. 40A to 40C is performed.

At that time, if the rotation direction is counterclockwise as shown in FIG. 4 2 A, the surplus specimens 4 a and 4 b gather at the left end of the surplus container, and the rotation direction is shown in FIG. 4 2 B. As shown, in the clockwise direction, the surplus specimens 4a and 4b gather at the right end of each surplus container.

In this way, even when a centrifugal force due to rotation is applied, even if the direction of rotation changes alternately, that is, even if the direction of acceleration changes, the surplus sample is held in the surplus sample container 4 1 1 7 a. Depending on the wettability of the flow path and the surface of each tank, specimens that easily leak from other parts do not leak to the first supply flow path 4 1 1 8 and the liquid in each reagent reaction tank is independent. Stable low-speed agitation is possible while maintaining the properties.

Next, an example of the entire carrier including the embodiment of the present invention is shown.

Fig. 43 shows a disk-shaped carrier 4100 formed of transparent, translucent acrylic, PET, PP, polyester resin, etc., forming grooves and recesses on the channel, reservoir, and excess storage Each component such as a part is formed Reference numeral 4 1 0 1 is a blood reservoir, which is a part for supplying blood collected by a pipet or other holders from blood collected from a human body or the like. 4 As shown in Fig. 3, the side of the storage tank is not provided with an acute angle, and has a shape that reduces residual blood.

Reference numeral 4 1 0 2 denotes a diluent storage part that stores the diluent leaked to the outside by, for example, destroying the sealed diluent-containing bouch. The blood reservoir 4 10 1 has an open upper surface, and the adjacent diluent reservoir 4 1 0 2 is stored in the bouch and arranged in advance. At the top is a lid.

When used, blood is supplied to the blood reservoir 4 10 1 by a pipette or the like, or a porous material in which body fluid is immersed in cancer is inserted, and the lid is slid to slide the blood reservoir Cover the upper surface of 4 1 0 1 with a lid, and move the inside of the dilution reservoir 4 10 0 2 due to the sliding of the lid, destroy it, and dilute the diluent 4 1 0 A configuration that enables supply from 2 to the outside is preferable. For example, the configuration of Japanese Patent Application No. 2 0 0 5-1 6 8 8 8 5 is preferably used. Although not shown in the figure, the grooves provided on both sides of the blood reservoir 4 1 0 1 and the diluent reservoir 4 1 0 2 are guides that allow the lid to slide slidably. It can be used as a groove.

Reference numeral 4 1 0 3 denotes a blood distribution unit, which includes a blood quantitative supply channel for supplying blood toward the two blood cell separation units.

4 1 0 4 is a surplus blood reservoir for storing the blood that has overflowed after the blood has filled the first blood cell separator 4 1 0 6 and the second blood cell separator 4 1 0 7. It is a part of.

4 1 0 5 is a flow channel for the surplus part, and after the first blood cell separation unit 4 10 6 and the second blood cell separation unit 4 1 0 7 are filled with blood, the excess blood is removed. This is a flow path for flowing into the excess blood reservoir 4 10 4. -

4 10 06 is a first blood cell separation unit, and 4 10 07 is a second blood cell separation unit. The volume of each space is formed to indicate the required amount of liquid.

4 1 0 8 is the first blood cell storage unit, which is connected to the second blood cell separation unit 4 1 0 7 via a relatively narrow channel, and 4 1 0 9 is the second blood cell storage unit, It connects with the 1st blood cell separation part 4106 through a thin channel. Such a connection by a relatively narrow channel prevents the blood cells from flowing backward when the centrifugal force weakens, such as when the carrier rotates at a low speed or when the direction of rotation is alternated.

4 1 1 1 is a first flow path having a bent portion in the center direction, and connects the second blood cell separation portion 4 1 0 7 and the mixing portion 4 1 1 2.

4 1 1 3 is a second flow path having a bent portion in the center direction, and is for connecting the first blood cell separating portion 4 10 6 and the adjustment tank 4 1 1 0.

4 1 1 4 shows one each of the quantification tanks, and has the same configuration as in FIGS. 3 8 A to 38 C, and is equidistant from the outer periphery of the first supply channel 4 1 1 8 Or they are arranged at unequal intervals, and their volumes indicate the target liquid volume

4 1 1 5 is a quantitative supply channel, which has the same configuration as that shown in FIGS. 38A to 38C and extends in the circumferential direction. For connecting tank 4 1 1 6

4 1 1 6 is a reagent reaction tank, which has the same configuration as that shown in FIGS. 38A to 38C, and is formed in a substantially tangential direction of the carrier, as shown in FIG. 38 and the like. The reagent is arranged inside. If oxygen is required for the color reaction, depending on the type of B-type drug, the reagent reaction tank 4 1 1 6 has the third 3 8

An air reservoir as shown in Fig. B may be provided.

4 1 1 7 a to 4 1 1 7 d are redundant shapes having the same shape and size. As shown in Fig. 41, it is a superdiluted liquid mixture storage part, and is constructed by connecting concentric first surplus storage part and second surplus storage part at the connecting part.

Reference numeral 4 1 1 8 denotes a first supply channel, which is concentrically formed, and a plurality of reagent reaction tanks 4 1 1 6 having a quantitative tank 4 1 1 4 are arranged in the outer circumferential direction.

4 1 1 9, 4 1 2 1 and 4 1 2 7 are deaeration ports, a mixing part that prevents liquid movement in the flow path, and an opening part for releasing the air in the buffer part to the outside .

4 1 2 0 is a third flow path, which has a bent portion in the middle “L” direction, and is used to connect the adjustment tank 4 1 1 0 and the first supply flow path 4 1 1 8.

4 1 2 2 is a fourth flow path for connecting the mixing section 4 1 1 2 and the second supply flow path 4 1 3 0 with a bent portion in the center direction.

Reference numeral 4 1 2 3 denotes a fifth flow path, which is a straight flow path for connecting the diluent storage section 4 10 0 2 and the diluent measurement section 4 1 2 4.

4 1 2 4 is a diluent quantification unit, one end of the sixth channel 4 1 2 5 is connected in the center direction, and the other end of the sixth channel 4 1 2 5 is the surplus dilution solution storage unit 4 1 2 6 connects. '

4 1 2 6 is a surplus dilution liquid storage part, and a part for storing the dilution liquid overflowing in the dilution liquid determination part 4 1 2 4.

4 1 2 8 is a preparatory tank, which uses the concentricity of the liquid surface remaining in the preparatory tank 4 1 2 8 by applying centrifugal force, and quantifies the liquid quantified by the dilution liquid quantification unit 4 1 2 4 This is to improve the accuracy and is connected to the diluent quantification unit 4 1 2 4 in the outer circumferential direction.

4 1 2 9 is a seventh flow path that extends parallel to the diameter direction and is connected to the mixing portion 4 1 1 2 through two bent portions.

4 1 3 1 and 4 1 3 1 'are chucking holes, It is a part for connecting with the device.

FIG. 44 shows an example of a reading device.

4 1 3 2 is a lower part of the apparatus, and a recess for accommodating the carrier 4 1 0 0 0 is formed in the center. In the center, the two chucking holes 4 1 3 1 and 4 1 3 Rotating body 4 1 34 having projections 4 1 3 5 and 4 1 3 5 for insertion and fixing to 1 and 2 is provided. Although not shown, the rotating body 4 1 3 4 is connected to a stepping motor, a transmission gear or the like.

4 1 3 3 is the upper part of the device and is connected to the lower part of the device 4 1 3 2 so that one side can rotate.

4 1 3 6 a to 4 1 3 6 c are primary color light sources, which are formed by laser light, LED, infrared light source, etc., and 4 1 3 7 a to 4 1 3 7 c are light receiving elements. , And are respectively disposed at portions facing the light source.

Next, the operation when blood and diluent are supplied and developed on the carrier of the embodiment shown in FIGS. 43 and 44 will be described.

When blood is supplied to the blood reservoir 4 10 1 of the stationary carrier 4 1 0 0, the diluent is developed into the diluent reservoir 4 1 0 2.

At this time, the chucking holes 4 1 3 1 and 4 1 3 1 of the carrier 4 1 0 0 are inserted into the protrusions 4 1 3 5 and 4 1 3 5 ′ of the rotating body 4 1 34 shown in FIG. Lower unit 4 1 3 2 Set.

Measure by rotating each reagent reaction tank on the carrier 4 1 0 0 by closing the upper 4 1 3 3 on the storage 4 1 3 2 and closing it. The carrier 4 1 0 0 accommodated in the apparatus is rotated at a rotational speed of about 5 0 0 0 jpm.

The blood in the blood reservoir 4 10 1 is supplied to the first blood cell separator 4 10 6 and the second blood cell separator 4 1 0 7 via the two channels of the blood distributor 4 1 0 3. The dilution liquid in the dilution liquid storage 4 1 0 2 is the fifth flow path 4 1 2 3 Is supplied to the diluent storage unit 4 1 2 4.

The blood supplied to the first blood cell separation unit 4 10 6 and the second blood cell separation unit 4 1 0 7 passes through the first blood cell storage unit 4 1 0 8 and the second blood cell storage unit 4 1 0 9 by centrifugal force. While filling, the first blood cell separation unit 4 10 6 and the second blood cell separation unit 4 1 0 7 are filled, and the surplus is stored in the surplus blood storage unit 4 1 via the surplus portion channel 4 1 0 5. Housed in 0-4. This configuration requires a small excess blood reservoir while having two or more quantifiers, and proposes a simplified configuration.

The diluent supplied to the diluent quantification unit 4 1 2 4 gradually fills the diluent quantification unit while filling the spare tank 4 1 2 8, and the surplus is passed through the sixth channel 4 1 2 5. It is stored in the surplus dilution liquid storage section 4 1 2 6.

The blood supplied to the blood cell separation unit tries to move to fill the first channel 4 1 1 1 and the second channel 4 1 1 3 by capillary force, but the movement is hindered by centrifugal force. It is in the state.

The diluent also tries to move due to the capillary force of the seventh flow path 4 1 2 9, but the movement is blocked by the centrifugal force.

By continuing the rotation, the blood cells in the first blood cell separation unit 4 1 0 6 and the second blood cell separation unit 4 1 0 7 are moved to the first blood cell storage unit 4 1 0 8 and 4 1 0 9, Perform blood cell separation. Since the blood cell separation part and the blood cell storage part are connected by a thin flow path, the blood cells that have once entered the blood cell storage part are held and do not flow backward even by low-speed rotation.

After the separation is sufficiently performed and the blood cell separators 4 1 0 6 and 4 1 0 7 are filled with only the plasma components, the rotation of the carrier 4 1 0 0 is lowered. The centrifugal force is weakened, and the blood in the first flow path 4 1 1 1 and the second flow path 4 1 1 3 moves to fill the flow path, and in the seventh flow path 4 1 2 9 The dilute solution in the same way also moves in the mixing section 4 1 1 2 direction.

When the rotation speed is increased again, the first flow path 4 1 1 1 and the second flow path 4 1 1 3 The plasma moves to the mixing unit 4 1 1 2 and the adjustment tank 4 1 1 10, and the diluted solution also moves to the mixing unit 4 1 1 2.

At this time, the output port is located farther from the center of rotation than the input ports of the first channel 4 1 1 1, second channel 4 1 1 3, and seventh channel 4 1 2 9 The plasma and the diluted solution quantified by the blood cell separation units 10 6 and 10 7 and the diluted solution quantification unit 4 1 2 4 move to the mixing unit 4 1 1 2 and the control tank 4 1 1 0.

After the movement is completed, change the direction of rotation over time and mix. In this case, because the mixing tank has a large volume, mixing is possible by simply changing the speed over time or changing the direction of rotation.

After mixing, by reducing the rotation speed, the mixed solution fills the fourth flow path 4 1 2 2 connected to the mixing section 4 1 1 2, and the plasma fills the third flow path 4 1 2 0. .

Again set the rotation speed to 5 0 0 ΓΡΠ! When the pressure is increased to about 100 rpm, the mixed solution is supplied to the second supply channel 4 1 30 and the plasma is supplied to the first supply channel 4 1 1 8. Each metering tank 4 1 1 4 is filled by force. The fixed-quantity supply channel 4 1 1 5 is also filled, but stays on the connection surface with the reagent reaction tank 4 1 1 6.

After each of the quantification tanks 4 1 1 4 and 4 1 1 4 ′ is filled with the mixed solution and the plasma, the surplus portion is stored in the excess diluted mixed solution storage portions 4 1 1 7 a to 4 1 1 7 d. Increase the rotation speed to about 2500 rpm.

Furthermore, since each solution in each quantification tank 4 1 1 4 and 4 1 1 4 ′ is supplied to the reagent reaction tank 4 1 1 6, 4 1 1 6 ′, the number of rotations of the carrier is further increased (5 0 0 0 r pm to 6 0 0 0 r pm).

After the supply is completed, as shown in FIGS. 40A to 40C, the carrier is caused to rotate alternately up to a predetermined number of rotations over time.

This alternating change in acceleration gives the liquid in the reagent reaction tank The body and the reagent are mixed to produce a uniform color reaction.

Next, the primary color light sources 4 1 3 6 a to 4 1 3 6 c irradiate each reagent reaction tank with laser light, and the light receiving elements 4 1 3 7 a to 4 1 3 7 c receive the transmitted light and absorb the absorbance. Is measured electronically and the concentration of blood components is measured.

According to the above description, it is possible to easily measure blood components simply by supplying blood to the central blood reservoir 4 10 1. Industrial applicability

The first invention enables a simpler and quicker apparatus that can perform signal processing, so that a patient or a healthy person can easily diagnose himself / herself in a place close to his / her life such as a lifestyle-related disease. The first invention makes it possible to spread the diagnosis of lifestyle-related diseases that are a problem in modern society. Therefore, even when measuring various multiple components, electrical processing can be performed accurately, and it can be used for automatic measurement of body fluid components that are small and easy to use at home. Contributes greatly to the realization of equipment. ,

In the first invention, when a plurality of biological components are measured on a single carrier, optical measurement can be performed easily and stably, so that an automated body fluid component measuring device can be reduced in size and simplified. A device that can measure the tendency of various diseases such as lifestyle-related diseases at a more familiar place.

In the first invention, since biochemical analyzers such as blood tests and infection tests can eliminate signal drift and other errors, more accurate biochemical information can be obtained quickly. A faster biochemical analyzer can be constructed.

In addition, the second invention is smaller and simpler, but has many items. It is possible to measure information on the components in the body that cross, and to propose a detection device for more familiar in-vivo information.

Furthermore, in the third and fourth inventions, biochemical analyzers such as blood tests and infection tests can quickly obtain more accurate biochemical information. it can.

Claims

The scope of the claims

1. a carrier having a plurality of reaction sites showing a biochemical reaction, a plurality of reading units for reading the biochemical reaction, and the carrier and the reading unit are movable with respect to each other, and on the carrier A biochemical analyzer characterized in that the interval between reaction sites and the interval between the plurality of reading parts are arranged differently.

2. The biochemical analyzer according to claim 1, wherein an interval between the reading units is different from an interval that is an integral multiple of an interval between reaction sites on the carrier.

3. The biochemical analyzer according to claim 1, wherein the reaction site is a site that causes a color reaction of a body fluid such as blood or urine according to a component.

4. The biochemical analysis apparatus according to claim 1, wherein the carrier has a disc shape, and the reaction sites are arranged on the outer periphery at equal intervals.

5. A carrier having a plurality of reaction sites showing a biochemical reaction, biochemical reaction information acquisition means for obtaining biochemical reaction information from a plurality of reaction sites of the carrier, and acquiring the biochemical reaction information at a predetermined time Detecting means for detecting biochemical reaction information obtained from the means, calculating means for calculating a predetermined number of information obtained by the detecting means for a predetermined time, and a part serving as a reference from the signal output from the calculating means A biochemical analyzer characterized by comprising determination means for determining whether or not.

6. A storage unit that temporarily stores information obtained by the biochemical reaction information acquisition unit is provided, and when determining a reference site, data is read from the storage unit for determination. Item 6. The biochemical analyzer according to Item 5.

7. The biochemical analyzer according to claim 5, wherein the reaction site is arranged in a state having an orbit, and a non-light-absorbing region including a slit in a part thereof is used as a reference region. .

8. The biochemical analyzer according to claim 5, wherein the predetermined time is a predetermined time earlier than a central time.

9. The biochemical analyzer according to claim 5, wherein the read information is an electrical signal related to a color reaction between a reagent and a body fluid.

10. A change amount conversion means for converting a biochemical signal into a signal indicating a change amount, and a measurement range determination means for determining a measurement range from the signal obtained by the change amount conversion means. Biochemical analyzer.

11. The biochemical analyzer according to claim 10, wherein the signal indicating the amount of change is a differential signal.

The biochemical analyzer according to claim 10, wherein the measurement range is between peaks of the signal indicating the amount of change.

1 3. The biochemical signal is a carrier in which a plurality of reagent reaction tanks that perform a color reaction between a reagent and a specimen are arranged at equal intervals, and the reagent reaction tank is irradiated with measurement light from the outside to be reflected or reflected. The biochemical analyzer according to claim 10, wherein the biochemical component is measured by measuring transmitted light.

1 4. A carrier in which a plurality of reagent reaction tanks are arranged on the same orbit, and a measurement unit for optically measuring the components in the reagent reaction tank, and the measurement unit and the carrier move relatively. The biochemical analyzer according to claim 10, wherein the biochemical analyzer is a biochemical analyzer that measures the components in each of the reagent reaction vessels.

1 5. Reagent reaction tank detection means for detecting a part of the reagent reaction tank, and when the interval of the parts detected by the reagent reaction tank detection means is equal to or larger than a predetermined interval, the interval is divided by the predicted interval. When the value is 1 force or more

Reagent reaction tank part determining means for determining a predetermined interval as a reagent reaction tank part The biochemical analyzer according to claim 14, further comprising:

1 6. A carrier consisting of a translucent member provided with a reagent reaction tank, the reagent reaction tank supplied with the sample is irradiated with measurement light from the outside, and the light obtained through the reagent reaction tank is received to receive a sample. In a biochemical analyzer that measures components, a light absorbing member such as a film that absorbs light, a printed surface, or a painted surface is provided in the direction of the irradiation surface that irradiates measurement light to the reagent reaction tank. The biochemical analyzer is characterized in that the area of the measurement window is smaller than the area of the measurement light irradiation surface of the reagent reaction tank. '

17. The area of the measurement window is smaller than the area of the irradiation surface of the reagent reaction tank so that the measurement light can pass only through the central portion of the reaction layer. The described biochemical analyzer.

18. The biochemical analyzer according to claim 16, wherein the measurement window is formed in a concave shape.

1 9. A carrier consisting of a translucent member having a plurality of reagent tanks, and the reagent reaction tank to which the sample is supplied is irradiated with measurement light from the outside by relative movement, and is arranged on the track of the measurement light. A biochemical analyzer that receives light obtained through a reagent reaction tank and measures a sample component, wherein the carrier is provided with a reference site for permeation measurement.

2 0. The reference part is one or more of a black surface, a through-hole, a reference liquid tank, an empty reagent reaction tank, a dilution liquid tank, a measurement sample (plasma, etc.) only, and a sealed tank. The biochemical analyzer according to claim 19, wherein the biochemical analyzer is characterized by the following.

21. The biochemical analyzer according to claim 19, further comprising a calibration means for performing offset calibration based on a light reception signal when the reference site is black.

2 2. Heating means for heating a part of the carrier, temperature measuring means for measuring a part opposite to the part of the heating means, and based on the temperature measured by the temperature measuring means, the heating A biochemical analyzer characterized by comprising control means for adjusting and controlling the heating amount of the temperature means.

23. The biochemical analyzer according to claim 22, wherein an endothermic member is disposed on the other surface of the carrier.

24. The biochemical analyzer according to claim 25, wherein the heating means is a halogen lamp.

25. The biochemical analyzer according to claim 22, wherein the carrier performs regular motion.

26. A heating means for heating a part of the carrier, a temperature measuring means for measuring the surface of the carrier, and a heating amount of the heating means based on the temperature measured by the temperature measuring means A biochemical analysis apparatus comprising a control means for adjusting and controlling the temperature, and performing the heating by the heating means and the temperature measuring means at different timings.

2 7. After supplying the specimen, in a carrier that is processed and arranged in a state for performing a plurality of examinations, a dilution member for diluting the specimen is arranged vertically movable in the carrier, and the dilution member A carrier for a biochemical analyzer, comprising: an opening member for forming an open state in the downward direction of the dilution member when the is moved downward.

28. The biochemical analyzer carrier according to claim 27, wherein the diluting member is accommodated in the carrier via a pressable sheet member such as a bellows.

29. The dilution member has a configuration in which an opening surface of a cup member containing a diluent is covered with a thin film sheet, and the opening member is formed of a puncture device that can puncture the thin film sheet. A carrier for biochemical analyzers.

30. After supplying the specimen, a part of or all of the side surface, top surface, or bottom surface of the carrier to be processed and processed in a state for performing a plurality of examinations is provided. An annular concavo-convex member formed with continuous concavo-convex portions, and a biochemical analyzer characterized by comprising a vibrating member that comes into contact with the annular concavo-convex member and vibrates a portion requiring stirring of the carrier.

3 1. In a carrier placed in a state for performing a plurality of examinations after being supplied with a specimen, the carrier is placed in the inside of the carrier and needs to be stirred. A biochemical analyzer characterized by comprising a stirring member that deforms into '

3 2. After supplying the specimen, a processing operation is performed to arrange the carrier in a state for performing a plurality of examinations, a rotating body for rotating the carrier, and a portion in contact with the rotating body on the back surface of the carrier. A biochemical analyzer comprising: a disposed metal member; a friction member that forms a contact surface between the rotating body and the carrier; and a magnetic member that provides magnetic coupling to the metal member in a non-contact manner. .

3. The biochemical analyzer according to claim 32, wherein a horizontal contact surface between the carrier and the rotating body is a friction member provided on the rotating body and a bottom surface of the carrier.

34. The biochemical analyzer according to claim 32, wherein the metal member is embedded in a bottom surface of the carrier.

3 5. When mixing two or more different substances in a minute space, the centrifugal force does not occur in a relatively short time, and the rotation speed is increased over time so that the required acceleration can be given for a predetermined time. A liquid mixing method characterized by applying an angular acceleration to increase (positive acceleration) or decrease (negative acceleration).

3 6. When mixing substances with different specific gravity in a minute space, compare Centrifugation does not occur in a short period of time, and the necessary acceleration of the substance is increased over time to a speed that can be given for a predetermined time. In addition, the necessary acceleration for the substance is increased over time up to a rotational speed that can be given for a predetermined time.

The liquid mixing method according to claim 35, wherein this is repeated.

3 7. A carrier having a micro space for mixing two or more different substances, such that centrifugation does not occur in a relatively short time and the necessary acceleration can be given for a predetermined time. A liquid mixing apparatus comprising drive means for applying angular acceleration to the carrier so as to increase or decrease the rotation over time up to the rotation speed.

3 8. A carrier having a mixing part for mixing substances having different specific gravities, and a rotation speed at which the carrier is rotated so that centrifugation does not occur in a relatively short time and a necessary acceleration is given to the substance for a predetermined time. Is increased over time until the number of rotations is increased over time so that the required acceleration can be given to the substance for a predetermined time without centrifugal separation in the opposite direction for a relatively short time. The liquid mixing apparatus according to claim 37, further comprising a rotating means.

39. The liquid mixing method and apparatus according to any one of claims 35 to 38, wherein the number of rotations is 2 00 0 rpm or less.

4. The time from the maximum rotational speed in one direction to the maximum rotational speed in the opposite direction is 0.5 to 2 seconds, 4. Liquid mixing method and apparatus.

4 1. When mixing two or more substances in a minute space in a carrier, the centrifugal separation does not occur in a relatively short time, and the carrier is driven to give the necessary acceleration to the substance for a predetermined time. A biochemical analyzer characterized by having means.

4 2. A measuring unit that mixes substances with different specific gravity arranged in the direction of the outer peripheral edge on the rotating body, measures the reaction state and results such as absorbance, and a quantifying unit for supplying a quantitative sample to the measuring unit A flow path for supplying a sample to the quantification unit, a quantitative supply flow path extending in the circumferential direction, a finite first recovery flow path extending concentrically and another recovery flow path, and the first recovery flow path. A carrier for a biochemical analyzer, comprising a flow path and a connecting flow path connecting the other recovery flow paths and connected to the quantitative supply flow path to recover a surplus specimen.

43. The carrier for a biochemical analyzer according to claim 42, wherein a connecting portion between the first recovery channel and the second recovery channel of the connection channel is formed in an acute angle shape.

44. The carrier for a biochemical analysis device according to claim 42, wherein the measurement unit and the determination unit are connected by a flow path extending in a circumferential direction.

45. The carrier for a biochemical analyzer according to claim 42, wherein an air reservoir is formed in a central direction in the measurement unit.

4 6. With respect to the carrier, the centrifugal separation does not occur in a relatively short time, and the necessary angular acceleration is increased over time up to a given time, and then relatively short in the opposite direction. 4. A rotator is further provided for increasing the number of rotations over time until a required angular acceleration is given for a predetermined time, and repeating this without causing centrifugal separation over time. The carrier for a biochemical analyzer described in 1.

4 7. A flow path having capillary force, and at least from the input port, the output calorie has a linear part parallel to the diameter, and adjusts the rotation speed of the carrier to move and stop the liquid. Carrier for chemical analysis equipment.

4 8. A flow path having a capillary force, in which at least the output calorie extends from the input port in the circumferential direction to adjust the rotation speed of the carrier and adjust the liquid. A carrier for biochemical analyzers that moves and stops the body.