JP2007010319A - Biochemical analyzer - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a small-sized simple biochemical analyzer capable of realizing the optical measurement of a plurality of reagent reaction tanks corresponding to a very small amount of body fluids by an accurate, rapid, and more simple measuring circuit and capable of being placed in the vicinity of a patient and a healthy person for the purpose of the diagnosis or the like of living habitual diseases. <P>SOLUTION: The biochemical analyzer includes a carrier having a plurality of reaction regions showing biochemical reaction and a plurality of reading parts for reading the biochemical reaction and constituted so that the carrier and the reading parts have a movable state mutually and are arranged so that the interval between the reaction regions on the carrier is different from the interval between a plurality of the reading parts. Further, an accurate reference point is obtained in the case that specimen components of many items are measured on the one carrier and an accurate specimen position is obtained in the case that the specimen components of items are measured on the one carrier. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to a biochemical analyzer for measuring a carrier having a plurality of sites showing a biochemical reaction.

Recently, diseases related to lifestyle such as diabetes, cancer, cerebral infarction, etc. are deeply related to dietary requirements, stress, etc., so body fluid components such as blood and urine are also used for early detection of these diseases. It is desired that an environment capable of quickly measuring and diagnosing multiple items can be realized in a more familiar place.
A device that analyzes and diagnoses bodily fluids can be used easily at home or in places where there are no facilities, as long as the bodily fluid components are supplied. preferable.
In biological component measurement, irradiate light to a reaction tank in which a body fluid such as blood, urine, sweat, etc., and an enzyme reagent are colored and reacted, receive reflected or transmitted light, and measure the received light. In a component analyzer that optically measures glucose, total cholesterol, creatinine, low-density lipoprotein, and total bilirubin component concentration by determining absorbance, the received light as shown in Japanese Patent Laid-Open No. 05-209836 is converted into RGB Used to obtain the absorbance of each of the three primary colors, or to irradiate the light previously separated into the three primary colors onto the reaction tank described above and obtain the absorbance from the transmitted or reflected light of the three primary colors. It has been.

It has been necessary to consider the following points regarding a device used as diagnostic information by obtaining a plurality of component values by such optical measurement.
(1) The absorbance of each reaction vessel may be output as time-series data while rotating one carrier in which a plurality of reagent reaction vessels are arranged. In this case, in order to specify a plurality of reaction vessels, it is necessary to accurately detect a base point in one round. Conventionally, it has been 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 with a smaller amount of sample and automatically performs from sample supply to optical measurement, the optical measurement can be performed by mixing bubbles in the reagent reaction tank. Destabilization became a problem.

  (3) For 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 measuring a large number of biological components with a small amount of sample, the amount of sample used for measurement of each item becomes smaller, and there is a minute manufacturing error when manufacturing the carrier to be calibrated. The influence of the error caused by the generated burr or the movement error when moving the carrier or the optical measurement head, the light absorption by the material, and the irregular reflection becomes very large.

JP 05-209836 A Japanese National Patent Publication No. 10-510362 Japanese Patent Laid-Open No. 3-25351 JP 2003-207454 A Japanese Patent Laid-Open No. 5-240869

A more specific explanation of the above points will be given below.
After receiving multiple lights from one reaction tank at the same time, or after receiving light and splitting it into three primary colors, photoelectric conversion is performed on each light to form parallel electric signals and these parallel signals are A circuit configuration such as a multiplexer for conversion to a serial signal string is required.
When a plurality of lights pass 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 part is required, which is expensive and complicated. It comes with it.
The use of a multiplexer that requires a timing signal obtained by using a clock signal, etc., cannot be switched at an optimal time, resulting in delays and distortion in the waveform, when the reaction of the reaction vessel is fast. In some cases, it is not possible to detect all of the spectral signals required at the same time.

  Moreover, 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.

In Japanese National Publication No. 10-510362, a reference substance such as water is placed in a reaction tank for blood and a reagent as a reference tank, and the reagent is transmitted through the reagent reaction tank based on the wavelength of light transmitted through the reference tank. The calibration of the light obtained in this way is described.
The use of the reference substance disclosed in JP-T-10-510362 must be capable of being detected reliably within a range that does not hinder the measurement of the color reaction between the body fluid and the reagent, and is also storable. Often there is also a need to pay attention.

  Japanese Patent Application Laid-Open No. 3-25351 discloses that light that has passed through detection of bubbles mixed in a nozzle-shaped reagent reaction tank is photoelectrically converted and then differentially detected. In the optical detection in a reagent reaction tank having a structure that moves instantaneously, there is no disclosure of a method for determining a necessary measurement region.

Japanese Patent Application Laid-Open No. 2003-207454 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 having absorptivity is disclosed, but in fact, leakage from the light source at the boundary between the transmitted light measurement part and the black part is disclosed. Is a problem.

Also, errors contained in the received light signal prevent accurate component analysis and reduce the analysis capability of the entire apparatus.

In view of the above, the present invention
(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, on the carrier By adopting a combined configuration in which the interval between reaction sites and the interval between the plurality of reading units are different, the configuration is simple and the measurement process is improved.

  (2) Furthermore, the present invention defines 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 separately providing the base point detection means, and ensures that Provides an algorithm for extracting into. That is, 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 information obtained by the detecting means for a predetermined time, A combination of a calculation means for calculating a predetermined number and a determination means for determining a reference portion from a signal output from the calculation means provides a more reliable reference position without being confused with optical information in the reagent reaction tank. It is possible to detect.

  (3) Further, according to the present invention, a combination of a change amount conversion unit that converts a biochemical signal into a signal indicating a change amount, and a measurement range determination unit that determines a measurement range from the signal obtained by the change amount conversion unit. When multiple reagent reaction tanks move at a predetermined speed and multiple reagent reaction tanks are measured at regular intervals, the effective measurement area can be determined instantly and efficient component measurement is possible It becomes.

  (4) Further, the present invention is directed to light obtained through a reagent reaction tank by irradiating measurement light from the outside to the reagent reaction tank supplied with a carrier and a sample made of a translucent member having a reagent reaction tank. In the biochemical analyzer that receives the light and measures the sample component, an absorption member that absorbs the light provided with the measurement window is disposed in the direction of the irradiation surface that irradiates the measurement light to the reagent reaction tank, and the area of the measurement window However, by making it smaller than the area of the measurement light irradiation surface of the reagent reaction tank, it is possible to prevent light from leaking from parts other than the reagent reaction tank and to secure a measurement region with little error.

(5) Further, in the present invention, the light obtained through the reagent reaction tank by irradiating the reagent reaction tank supplied with the carrier and the specimen including the reagent reaction tank with the measurement light from the outside. In the biochemical analyzer that receives the light and measures the analyte component, the carrier is provided with a reference site for permeation measurement, which is caused by an electric circuit mixed in the received light signal or caused by uneven manufacturing of the carrier Signal drift can be eliminated and accurate data can be obtained.

  In the present invention, an input electric signal can be formed only by mixing a color signal obtained spectroscopically without requiring a special circuit configuration, and reading only takes timing from the rotational speed and arrangement position. Since individual spectroscopic data can be obtained, there is an effect that a quick signal processing can be performed with a simpler configuration.

  In the present invention, a predetermined reference position can be set on the carrier simply by providing a through hole having a specific shape in the arrangement of the reagent reaction tanks. Therefore, the carrier for measuring multiple body fluid components can be simplified. And an accurate reference position can be detected.

    In the present invention, when measuring color development reactions in a plurality of reagent reaction vessels optically continuously over time, it is possible to more quickly biochemical over many items by grasping an accurate measurement region based on differential signals. 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.

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, By having a combined configuration in which the interval between the reaction sites on the carrier and the interval between the plurality of reading units are different, a desktop device can be easily realized, and body fluid components can be easily measured at various locations. It becomes possible.
Examples of the biochemical reaction in the present invention include reactions that optically measure components related to a living body, such as a color reaction between a body fluid such as blood, urine, and sweat, and a reagent, and a fluorescence reaction using an immune response.
Examples of reagents used for measuring blood components include enzymes for measuring GPT, albumin, ALP, urea nitrogen (BUN), total protein, total bilirubin, glucose, total cholesterol, GOT, amylase, etc. in body fluid components The kind is shown.

The carrier has a disk shape, a rectangular shape, or a sheet shape, and a reaction tank containing or supplied with a reagent is arranged on the surface thereof at constant and unspecified intervals, and at least from the outside. The thing which provided translucency in the site | part which can measure light is illustrated.
In addition to the blood, there may be a separation unit for separating unnecessary blood cells, a quantitative supply unit for supplying a certain amount of body fluid to the reagent reaction tank, and the like.

The plurality of reading units in the present invention need only be able to measure the coloring information of the colored reagent in the reagent reaction vessel, and includes a light source that outputs visible light, ultraviolet light, infrared light electromagnetic waves, and the like, such as a laser and a light emitting diode. Examples include a light receiving unit that receives various light beams output from the light source and passes through or reflects the reagent reaction tank 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 what color density has been developed and how the color value has changed. Is adjusted as appropriate.

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 development spectrum of the reagent.
In the present invention, the combination configuration in which the interval between the reaction sites on the carrier and the interval between the plurality of reading units are different is, for example, measured by irradiating one reading unit with light from one light source. The other reading units indicate that they are in a position where 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 in a relatively moving relationship, and the carrier is rotating or sliding on the stationary reading unit, or vice versa, and the stationary carrier is In contrast,
A state in which the reading unit is rotating or sliding is shown.

In the present invention, when the carrier is a rotating body, so-called rotor, the arrangement angle from the center of the reagent reaction tank 1φ is θ, n is an arbitrary integer (n = 1, 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
K = θ × n − θ / m
It is represented by According to this equation, the size of the disc-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 is exemplified by visible or invisible color values, absorbance, frequency characteristics, etc. obtained by reacting a body fluid with a reagent. The biochemical reaction information acquisition means includes a reagent reaction tank. Examples include a combination of a light transmitting element and a light receiving element obtained by transmitting or reflecting light, a combination of electromagnetic wave transmission, and receiving means.
The “predetermined time” of the detecting means for detecting the biochemical reaction information obtained from the biochemical reaction information acquiring means at a predetermined time indicates, for example, two times at regular intervals before and after the central time Tn. For example, as shown in FIG. 9C, four time intervals tn1-β, tn1-α, tn1 + α, and tn1 + β are set for the time tn.
The “biochemical reaction information obtained from the biochemical reaction information acquisition means” is, for example, an amplitude value of a signal at a predetermined time, a frequency component, etc. after converting an optical output into an electrical signal, Either digital processing or analog processing may be performed.

The “predetermined time” in the calculating means for calculating the information obtained by the detecting means for a predetermined time and a predetermined number is a time width from tn1−β to tn1 + β in the case of FIG. 9C, for example. The 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 the reference part from the signal output from the calculation means is, for example, outputting a fact that the reference position is at time tn when there is an output of the calculation means at a predetermined time interval. The 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 an electrical signal after converting a biochemical signal into an electrical signal, and examples thereof include a differential, an integral signal, and other secondary differential signals.
The present invention outputs a signal having a high peak 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 peak and the beginning of the last high peak, and during this time, when the peak of a certain amount of height appears, this is a state where unnecessary optical interference such as bubble contamination has occurred. By removing, 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. However, 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, at least the previous The reagent reaction tank part that could not be detected is calculated by calculation based on the signal indicating the position of the reagent reaction tank detected next and the position of the reagent reaction tank that can be detected next, and information on that part is detected. May be.

  If the part of the reagent reaction tank of the chip and the number of rotations of the carrier are known in advance, the prediction range can be found, but since there are variations in the number of rotations of the carrier, all parts are predicted. Will result in a reaction tank that cannot be measured, so it is possible to detect the reagent reaction tank more reliably by obtaining 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. It becomes.

The present invention provides various reference parts on the carrier and uses the reference parts as so-called calibration information or reference information.
Factors that can cause calibration include emission intensity errors of light sources such as laser diodes and LEDs, sensitivity errors of photodiodes, DC offset voltage caused by errors in electrical circuits such as amplifier circuits, unevenness of materials forming the carrier, reagent reaction Processing irregularities at the bottom of the tank, adhesive intervening on the interface between the carrier and the lid, diffuse reflection of light on the adhesive, refraction, absorption, individual differences in body fluid components, component differences in diluents, measurement component errors, etc. Illustrated.

For such error factors,
For example, the light receiving signal can be corrected or calibrated by adding the following configuration to a portion corresponding to the optical measurement portion of the carrier.
1. A black pattern having an area equal to or larger than that of the reagent reaction tank is disposed.
By measuring the black pattern optically, it is possible to measure offset information generated in an amplification circuit, etc., and by removing this offset information from the optical information of the reagent reaction tank actually obtained, Component information is obtained.
2. A through hole equal to or larger than the reagent reaction tank is formed.
By receiving the light output from the light source that has passed through the through hole, the actual intensity, wavelength, and the like can be known, so that the measured color value can be corrected.
The through hole may be used as a reference site.

3. Place the reagent reaction tank empty.
In an empty reagent reaction tank, the state of measurement light due to processing unevenness at the bottom of the tank is measured, and it becomes possible to verify the measurement value that can obtain true optical information.
4). In addition, by filling with high purity water, the bottom surface and the top surface can be removed, and an accurate calibration value such as processing unevenness on the bottom surface of the reagent reaction tank can be obtained.
5. Place the reagent reaction tank filled with the diluent.
The absorbance of the diluted solution is obtained and used to calibrate the actual color value.
6). A reagent reaction tank is simply filled with plasma components. This is preferably the same as the plasma when plasma is supplied to the other reagent reaction vessels.
The optical measurement of only plasma 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 areas are optical measurement results of transmitted light through the reagent reaction tanks containing only the respective media. For example, when expressed in terms of OD value, penetrating light (OD value 0) <air (diluent) <Plasma only <Plasma + reagent reaction <Black (∞)
It is. The measured value of air (diluent) or plasma alone is used to correct the deviation of the light source intensity and the sensitivity of the photoreceptor and the absorbance of the carrier itself. The black (completely light-shielded) part is used to correct the offset value of the photoreceptor and the electrical circuit that amplifies its output (measured output value when there is no incident light). The use of a diluent having the same OD value is preferable because of the cloudiness of the bottom due to the water vapor.

FIG. 1 shows an embodiment of the present invention, and the present invention will be described in detail.
FIG. 1 (a) is a diagram for explaining a combination relationship between the carrier in a state in which the housing of the measuring apparatus is omitted for the sake of explanation and the reading portion, and FIG. 1 (b) shows the carrier 10 from above. FIG.
10 is a carrier, which is made of polyester, PMMA, PC, PS, PET, PDMS, glass or the like, and has a concave portion corresponding to a channel, a reaction tank, etc. formed on the surface, and a sheet lid made of the same material from above Are joined together by pressure-sensitive adhesive, adhesive, or self-adsorption ability.
The carrier 10 is exemplified by a configuration in which the blood supplied to the center is separated, mixed with a diluent, etc., and supplied in a fixed quantity to the reaction tank, depending on the relationship between the centrifugal force generated by the rotation and the capillary force of the flow path. The
In the case of blood, the configuration includes a blood cell separation chamber, a dilution / mixing chamber, a plasma quantification unit, and the like, but since any configuration can be adopted, the detailed configuration is omitted.
Reference numeral 11 denotes a metal plate for joining with the reading device, and is arranged so as to be exposed in a state where it is preferably partially embedded in the back surface of the carrier 10. A concave portion 11 ′ that is inserted into and fixed to a connecting shaft on the reading device at the center is formed so as to penetrate the bonding metal plate 11 from the back surface direction of the carrier 10 and partially penetrate the carrier 10.
Reference numeral 12 is an example of the operation unit, and illustrates a mixing tank or the like for a diluent. The operation unit 12 arbitrarily controls the rotation of the carrier 10 to adjust the capillary force and centrifugal force generated in the flow path and reaction tank in the carrier 10, and the reagent reaction tank row 15 a arranged in the outer peripheral direction of the carrier 10. At ~ 15 h, a conditioned specimen such as plasma separated and quantified is supplied.

Reference numeral 13 denotes a sample supply unit which is a part for supplying body fluid such as blood from the outside, and is composed of a concave liquid tank or flow path, and a supply unit lid is provided so that the sample does not leak to the outside as necessary. It may be provided.
Reference numeral 14 denotes a distribution channel, which is a channel for supplying the adjusted specimen to the individual reagent reaction tanks 15a to 15h. Reference numeral 18 denotes one of supply channels, which is used to connect the distribution channel 14 to each of the reagent reaction tanks 15a to 15h. The supply channel is connected to one reagent reaction tank. On the other hand, a plurality may be provided. Further, the volume of the supply channel 18 may be a quantitative value for the processed specimen.
15a to 15h are an example of a reagent reaction tank, and a target reagent is accommodated in a cylindrical recess in a dry, gel, or liquid state. The size is about 1mm in diameter and 3mm in depth, for example.
Reference numerals 16a to 16c denote light sources that output three primary colors. For example, the light source 16a is a red R laser, the light source 16b is a green G laser, and the light source 16c is a blue B laser.
Reference numerals 17a to 17c denote light receiving bodies, and photodiodes, phototransistors or the like are used.

The distribution flow path 14 and the reagent reaction tanks 15a to 15h are in a state of being covered with a lid portion made of a translucent sheet such as polyacrylic or PET during use.
FIG. 1B is a view of the positional relationship between the reagent reaction tanks 15a to 15g and the light sources 16a to 16c shown in FIG.
The individual reagent reaction tanks are arranged at intervals of 15 degrees from the center O of the carrier 10 around the reagent reaction tank 15a, and the light sources are arranged at intervals of 40 degrees around the light source 16a.
FIG. 4 shows the relationship between the light source, the light receiving unit, and the reagent reaction tank of the carrier. FIG. 4 is a cross-sectional view taken along the line XX ′ in FIG. In FIG. 4, a part of the reading device omitted in FIG. 1 is also shown.
The same components as those in the embodiment shown in FIG. 1 (a) are designated by the same reference numerals and description thereof is omitted. In FIG.
Reference numeral 19 denotes a lid, which is formed so as to cover the flow path or the like of the carrier 10. The lid 19 covers the upper part of the distribution channel 14, the supply channel 18, the reagent reaction tank 15 a and the like shown in FIG. 1 (a), and is a member having translucency for measurement by reflected light or transmitted light. It is formed with.
Reference numeral 20 denotes 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 thereto, and passes between the light source and the reagent reaction tank. It is arranged other than the optical path through the hole.
The passage hole 25 may have an area smaller than the area of the light source 16a, and may suppress reflected light and scattered light generated when light is irradiated from the light source to the reagent reaction tank.

Reference numeral 21 denotes an electric lead wire on the light source side for electrically connecting the light source 16a to the power source and the light source control circuit. The electrical lead wire 21 is connected to, for example, the electrical connection line 326 shown in FIG.
Reference numeral 22 denotes a light receiving side electric lead wire for electrically connecting the light receiving body 17a and the signal processing circuit.
Reference numeral 23 denotes a measuring device lid, which is equipped with a light receiving element 17a and the like, and is, for example, a movable part for taking out the carrier to the outside.
Reference numeral 24 denotes a carrier mounting portion of the measuring apparatus, for example, in which the light source 16a is inscribed so as to come directly under the reagent reaction tank of the carrier, and houses a stationary portion for placing the carrier, a motor for chucking and rotating, and the like. The overall shape of the carrier mounting portion 24 is shown in FIG.

Next, an example of a circuit configuration for processing signals received by the photoreceptors 17a to 17c shown in FIG. 1 will be described with reference to FIG.
In FIG.
310a to 310c are light sources of three primary colors, and correspond to, for example, the light sources 16a to 16c of FIG.
Reference numeral 311 schematically shows a reagent reaction tank on the carrier 10 shown in FIG. The carrier 10 shown in FIG. 1 rotates and each reagent reaction tank is shown passing through between the light source and the light receiving unit.
Reference numerals 312a to 312c denote light receiving units, which indicate a state in which an optical path is formed with each of the three primary color light sources 310a to 310c. The light receiving unit is also a part that converts a light receiving signal into an electric signal. The light receiving sections 312a to 312c correspond to the light receiving bodies 17a to 17c shown in FIG.
Reference numerals 313a to 313c are configured by an amplifier circuit and a filter circuit using an OP amplifier or the like, and are electrically connected to the individual light receiving units 312a to 312c, respectively, and amplify and filter the received light electric signal to electrically It is intended to be ready for processing.
Reference numeral 314 denotes a mixing unit, which mainly includes an adder circuit, and is a part for multiplexing the received light signals individually amplified by the amplification units 313a to 313c into, for example, one signal line.
The mixing unit 314 is configured by an analog adder circuit using an operational amplifier or the like, for example.
Reference numeral 315 denotes a filter for passing a frequency band necessary for measurement in the received light signal and removing aliasing noise due to sampling.

Reference numeral 316 denotes an A / D converter (A / D converter) that includes a sampling circuit, a quantization circuit, and the like, and converts received light electrical signals into digital signals.
Reference numeral 317 denotes a ROM that stores programs, parameters, and the like for operating the CPU 324 and the like.
Reference numeral 318 denotes a RAM, which is a part for storing temporary data and the like during program execution.
A display unit 319 includes a printer interface, RS-232C, a monitor, a speaker, a wireless LAN interface, a wireless output unit such as an infrared ray, a modem, and the like for displaying and transmitting the obtained blood information. Part.
Reference numeral 320 denotes a bus, which is a transmission path for transmitting command signals, data signals, and the like used in the CPU, ROM, RAM, and the like.
Reference numeral 321 denotes a rotation control unit, which is a drive driver for rotating the carrier left and right or in a shifting manner.

Reference numeral 322 denotes a temperature control unit, and blood and reagents operate effectively at around 38 degrees. Therefore, the carrier is heated by controlling a heater such as a halogen heater to generate a constant temperature. It is a circuit to keep.
Reference numeral 323 denotes a drive unit that controls an electrical output for causing the light sources 310a to 310c to emit light. For example, when the measurement is unnecessary, the control is such that the electrical output is stopped with respect to the light source.
Reference numeral 324 denotes a CPU for transmitting control signals to the rotation control unit 321 and the temperature control unit 322 via the bus 320 based on the program stored in the ROM 317 to control the operation of each element. is there.
Reference numeral 325 denotes an electric lead wire, which is formed of a jumper wire, a substrate wiring, or the like, and has a configuration in which the filter 315 and the A / D converter 316 are electrically connected.
Reference numeral 326 denotes an electrical connection line, which has a configuration in which the individual light sources 310a to 310c and the drive unit 323 are electrically connected separately as described above.

Next, the operation of the embodiment shown in FIG. 1 will be described in detail with reference to other drawings.
In FIG.
A lid is provided to supply blood to the specimen supply unit 13 and close the supply port. The lid is provided as necessary, and may not be necessary when the supply portion has a smaller diameter.
The carrier 10 supplied with the specimen is placed on the carrier mounting portion 24 of the measuring apparatus shown in FIG. 7, for example.
In FIG.
Reference numeral 11a denotes a rotating body, which is provided with a rotating shaft 11b at the center, a concentric magnetic member, and a friction member 11d on the outer side.
When the concave portion 11 ′ of the carrier 10 is inserted into the rotating shaft 11b, the metal plate 11 for joining the carrier 10 and the magnetic member 11c attract each other by magnetic force, but the friction member 11d is provided slightly higher than the magnetic member 11c. The rotating body 11a and the carrier 10 are strongly bonded while being in a non-contact state.
The size of the reader shown in FIG. 7 is, for example, about the size of an external or built-in type CD-ROM reader that is an accessory of a personal computer.
Note that a CPU, ROM, RAM, and a liquid crystal display may be directly incorporated in the reading device to be a stand-alone type.
When the measuring device lid portion 23 and the carrier mounting portion 24 are closed, the inside is in a state as shown in FIG. The CPU 324 shown in FIG. 6 outputs control signals to the temperature control unit 322, the rotation control unit 321, and the drive unit 323, and adjusts the rotation of the carrier while maintaining the temperature of the carrier 10 shown in FIG.
The blood supplied to the center moves in a controlled manner 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 a dilution operation with an effective physiological saline.
Further, the plasma obtained by separating blood cells by the action of the centrifugal force generated by the rotation of the carrier 10 shown in FIG. 1 and the capillary force generated by the miniaturization of the flow path is mixed with the centrifugal force by which the diluent is changed.
The diluted plasma is quantitatively supplied to the individual reagent reaction tanks, for example, via the distribution channel 14 and the supply channel 18 shown in FIG.
In each reagent reaction tank, the diluted plasma solution and the reagent are mixed, a color reaction occurs, and measurement of absorbance and the like is started.
In addition, since the color development time varies depending on the reagent, it may be preferable to measure in order of color development.

First, the description starts from the case where the reagent reaction tank 15a is on the measurement optical path formed by the light source 16a and the light receiver 17a shown in FIG.
The CPU 324 illustrated in FIG. 6 drives the driving unit 323, and the light sources 310a to 310c output laser beams by driving the driving unit 323.
Since the light source 16a and the light receiver 17a shown in FIG. 1 coincide with the transmission part of the reagent reaction tank 15a, the light emitted from the light source 16a passes through the reagent reaction tank 15a and is received by the light receiver 17a. For example, an electrical signal as indicated by R1 in FIG. 2 (a) is output from the photoreceptor 17a shown in FIG.
At this time, the light sources 16b and 16c shown in FIG. 1 are shielded from light by the light shielding portion 20 shown in FIG. 4, and the light receivers 17b and 17c are not receiving light.
When the output light of the light source 310a shown in FIG. 6 is received by the light receiving unit 312a via the reagent reaction vessel 311, the light receiving unit 312a converts the received light into an electric signal, and is amplified by the amplification unit 313a. At the connection point 3a, the signal shown in FIG. 2 (a) is output.
At this time, the output light of the light source 310b is blocked by the light shielding unit 20 shown in FIG. 4, and the light receiving unit 312b does not receive the light from the light source 310b, and the connection point 3b is shown in FIG. 2B. Thus, there is no output.
The output light of the light source 310c is also blocked by the light shielding unit 20 shown in FIG. 4, and there is no output at the connection point 3c shown in FIG. 6 as shown in FIG. 2 (c).
The mixing unit 314 shown in FIG. 6 receives the amplification signals of the individual amplification units 313a to 313c, but only the light reception signal R1 from the amplification unit 313b is output as shown in FIG. 2 (d).

Next, when the carrier 10 shown in FIG. 1 (a) rotates clockwise around the center point O,
The red laser light output from the light source 16a shown in FIG. 1 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. 1 passes through the inside of the reagent reaction tank 15e.
By this light transmission, the light receiving body 17b receives the light via the reaction reagent and converts it into an electrical signal, which is then amplified by the amplification section 313b shown in FIG. 6, and the signal amplified by the amplification section 313b is connected to the connection point 3b. Is output to the mixing section 314 as a signal G5 shown in FIG. Since the other light receiving bodies 17a and 17c block the light output from the light sources 16a and 16c, and the light receiving sections 312a and 312c have no output, the output of the mixing section 314 is a signal only for G5.
Next, when the carrier 10 shown in FIG. 1 (a) rotates clockwise around the center point O,
The green laser light output from the light source 16b shown in FIG. 1A and the red laser light output from the light source 16a are blocked by the light shielding unit 20 shown in FIG. 4, and the blue laser light output from the light source 16c shown in FIG. And passes through the inside of the reagent reaction tank 15h.

  The light receiving body 17c receives light via the reaction reagent and converts it into an electrical signal, which is then amplified by the amplifying unit 313c shown in FIG. 6, and the signal appearing at the connection point 3c is the signal B10 shown in FIG. And output to the mixing unit 314. Since the light output from the light sources 16b and 16a is blocked in the same manner as described above, the other light receivers 17b and 17a shown in FIG. 1 (a) have no output in the light receiving portions 312b and 312a shown in FIG. As indicated by 2 (d), the output of the mixing unit 314 is a signal only for B10.

By repeating the rotation of the carrier as described above, the output of the mixing unit 314 appearing at the connection point 3d becomes a single signal sequence as shown in FIG.
The output of the mixing unit 314 shown in FIG. 6 is extracted by the single filter 315 only in the frequency band necessary for analysis and input to the A / D converter 316.
The A / D converter 316 temporarily stores the output signal of the mixing unit 314 converted into a digital signal by performing an A / D conversion operation according to a control signal from the CPU 324 transmitted via the bus 320 in the RAM 318 or the like. .
FIG. 3 is a signal output diagram when twelve types of coloring reagents are used. FIG. 2 is an enlarged view of a part of the signal train of FIG.
The output waveform of the amplifier 313a appearing at the output terminal 3a in FIG. 6 is shown in FIG. 3 (a), for example, indicating a red laser light reception signal sequence, and the numbers are numbers assigned to the reagent reaction vessels.
FIG. 3A shows a signal that appears at the connection point 3a, and is a signal sequence obtained by measuring light with a red laser from the first number arbitrarily determined in the reagent reaction tank.
The output waveform of the amplifier 313b shown at the connection point 3b in FIG. 6 shows the green laser light reception signal sequence shown in FIG. 3B, and the numbers in the figure are numbers assigned to the reagent reaction tanks.

FIG. 3 (b) shows that, for example, photometry is performed with a green laser from No. 5 in the reagent reaction tank.
The output waveform of the amplifier 313c represented by the connection point 3c shown in FIG. 6 is shown in FIG. 3 (c), indicating a blue laser light receiving signal sequence, and the numbers in the figure are numbers assigned to the reagent reaction tanks.
Fig. 3 (c) shows that photometry is performed from the 5th reagent reaction tank using a green laser.
The output of the mixing unit 314 appearing at the connection point 3d shown in FIG. 6 is a composite signal sequence as shown in FIG. 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 obtained by performing electrical processing such as picking up pulse signals R1, G1, and B1 from the signal sequence at a predetermined timing and superimposing them.
Since the rotation of the carrier is constant, R1 can be detected at a constant timing. Therefore, the red light reception data R2 and R3 of other reagent reaction tanks can be picked up at a constant timing.
In the case of the green laser light receiving signal, for example, in the case of FIG. 1 (b), it is the fourth reagent reaction tank from the beginning, and the green signals of the other reagent reaction tanks with respect to the green lasers at regular intervals with reference to this first signal. Light reception data can be obtained.
In the case of a blue laser light reception signal, for example, in the case of FIG. 1 (b), it starts from the 7th reagent reaction tank from the beginning, and the data is picked up at regular time intervals based on this first signal. The light reception data for the blue laser in the reagent reaction tank can be obtained.
In this way, the CPU 324 shown in FIG. 6 has only to process one signal sequence shown in FIG. 3 (d). As shown in FIGS. 3 (a), (b), and (c), the pulse interval is Since it corresponds to the distance between the reagent reaction tanks and is constant and the same, in FIG. 3 (d), with reference to the first pulse obtained from each light receiving unit, if a pulse at every predetermined interval is picked up, Again, it is possible to easily obtain the light reception pulse for each spectral light source shown in FIGS. 3 (a), (b), and (c).
A reference tank for obtaining a specific light receiving pulse may be provided in the row of reagent reaction tanks, and the light receiving pulse indicating the reference tank may be the first pulse.
In the processing of the signal sequence shown in FIG. 3, data may be temporarily stored in a storage medium such as a memory or a heart disk every rotation or every several rotations, and read and processed at a timing required for processing. However, sequential processing may be performed.

Another embodiment will be described with reference to FIG.
Fig. 1 shows a disk-shaped carrier, which is rotated to perform sample mixing, quantification, etc., and component measurement is performed, whereas in Fig. 5, the measurement device and carrier are slid relative to each other. Shows the configuration to measure. The sliding may be repeated left and right.
As described above, the carrier 210 is made of light-transmitting polyacryl, PET, or the like, has a rod shape or a rectangular parallelepiped shape, and the reading device side also has a shape and driving configuration that matches the shape of the carrier 210.
Reference numeral 219 denotes a lid, which has translucency, and is coupled to the carrier 210 by an adhesive, an adhesive, a self-adsorption ability, and the like.
Reference numerals 215a to 215h denote reagent reaction tanks, in which a reagent is enclosed in advance, and a color reaction is performed when a sample such as blood is quantitatively supplied from the outside.
Reference numeral 220 denotes a light-shielding portion, which is colored with black and has a sheet, and light-transmitting holes 225a to 225h are formed only at portions located at the bottom of each reagent reaction tank.
Reference numerals 221a to 221c denote electrical connection lines, for example, corresponding to the electrical connection line 326 of FIG.
Reference numerals 222a to 222c denote electrical connection lines, which correspond to, for example, portions that electrically connect the light receiving unit 312a and the amplification unit 313a of FIG.
Reference numerals 216a to 216c denote light sources, for example, lasers and LEDs that emit light of individual colors of RGB.
Reference numerals 217a to 217c denote light receiving bodies, which include, for example, phototransistors and CDS.

In this embodiment, the carrier 210 is placed on the carrier mounting portion 224, and the reader lid portion 223 is closed.
When the light source 216a and the light receiving body 217a are arranged with respect to the first reagent reaction tank 215a, the light source 216b and the light receiving body 217b and the light source 216c and the light receiving body 217c are shifted from each other directly below the reagent reaction tank. The state is the same as the state shown in FIG.
By sliding the carrier 210 at a constant speed, one signal train shown in FIG. 3 (d) can be formed.
If measurement is possible with a single slide, the configuration may be simpler than the rotational configuration.

Another embodiment of the present invention will be described in detail with reference to FIG.
In FIG.
Reference numeral 101 denotes a photoelectric conversion means, which is composed of a combination of a laser light source and a light receiving semiconductor, etc., and is a means for receiving a transmitted color and a reflected light, which is a mixed color of a reagent and a sample, and converting it into an electrical signal. .
Reference numeral 102 denotes an amplifying means, which is composed of a combination of an amplifying circuit, a filter, and the like for filtering noise from an electric signal obtained by photoelectric conversion and amplifying a necessary frequency band.
Reference numeral 103 denotes an A / D converter, which is a circuit for converting the obtained electrical signal into a digital signal for digital processing, and is mainly composed of an A / D converter.

A control unit 104 controls other output signals such as the storage unit 105 and the read signal output unit 106, and includes a CPU or the like.
Reference numeral 105 denotes a storage unit, which is mainly composed of a storage medium such as a RAM, DVD-R, RW, CD-R, RW, and SD card, and is preferably a RAM because it is often stored temporarily.
Reference numeral 106 denotes a read signal output unit, which includes a clock oscillation unit and other time-adjusted pulse output units. The read signal output unit 106 is a signal output unit for sequentially reading data stored in the storage unit. This signal is necessary for setting a time width for determining whether or not.
Reference numeral 107a denotes a first detection unit that detects optical data at a timing of -β time as a digital signal or a quantized signal with respect to the reading time tn.
Reference numeral 107b denotes a second detection unit that detects optical data at a timing of -α time as a digital signal having a predetermined time width or a quantized signal having a predetermined time width with respect to the reading time tn.

Reference numeral 107c denotes a third detection unit which detects optical data at a timing of + α time with respect to the reading time tn as a digital signal or a quantized signal.
Reference numeral 107d denotes a fourth detection unit that detects optical data at a timing of + β time with respect to the reading time tn as a digital signal or a quantized signal.
Reference numeral 108 denotes a multiplication unit, which is a part for multiplying the signal obtained by the first detection unit 107a to the fourth detection unit 107d in the previous stage. For example, the first detection unit 107a to the fourth detection unit 107d When the output signal is a digital signal, a combination of logic such as an AND gate may be sufficient.
Reference numeral 109 denotes a time width setting unit, which outputs a time width signal from + β to −β with a waveform as shown in FIG. 9 (e) for the signal tn output from the read signal output unit 106, for example. It is a part for.
Reference numeral 110 denotes a determination unit which determines a reference signal from the multiplication signal obtained by the previous multiplication unit 108 and the previous time width setting unit 109 and outputs a determination signal.
The output signal of the determination unit 110 appearing at the output terminal 10g is used for reagent reaction tank recognition and the like.
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 embodiment, in order to explain only the operation for detecting the reference site, the carrier in a state where 10 or more reagent reaction vessels are arranged at equal intervals on the circumference is illustrated. Shown in 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. 1 (a), it is formed in an arc shape and is a reagent reaction tank. Are formed as part of the column.
FIG. 9B shows a cross section of FIG. In FIG. 9 (a), the lid 117 is shown in a omitted state.

In FIG. 9 (a), 111a and 111b are reagent reaction tanks, which are formed by forming recesses on a substrate 116 such as polycarbonate, and the reagents are accommodated therein. The reagent reaction tank is connected to a supply channel 112a, 112b such as a flow channel for supplying a sample from the outside and a capillary tube. The supply path may be unnecessary depending on the type of specimen or reagent and the supply form.
Reference numeral 113 denotes a slit, which is formed of at least a non-translucent member. The thickness of the slit 113 is not particularly limited as long as a non-light-transmitting portion is formed. The slit 113 may be formed integrally with the base material 116 or may be joined separately.
Reference numeral 114 denotes a gap, which is formed in the same size on both sides across the slit 113. The gap 114 is preferably set to be larger by one or two times than the reagent reaction tanks 111a and 111b in terms of measurement, but at least large enough to detect at least two pulses at the distance of the slit. That's fine.

In FIG. 9A, the reference portion 115 is formed by combining the slit 113 and the gap portion 114.
Reference numeral 117 shown in FIG. 9B denotes a lid, which may be formed of the same material as that of the base material 116 and has a light-transmitting property as a whole. The lid 117 and the base material 116 are preferably joined by, for example, an adhesive, a pressure-sensitive adhesive, or a self-adsorption ability.
Reference numeral 118 denotes a non-translucent member which is black or has a color scheme corresponding to it and does not transmit light. The non-translucent member 118 is, for example, in a seal shape or a thin plate shape, and is preferably 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 vessels 111a and 111b via the supply passages 112a and 112b is mixed with the reagent previously stored in the reagent reaction vessel to cause a color reaction. When the reaction is stabilized, each reagent reaction tank is irradiated with laser light, other visible light, or the like. The optical signal reflected or transmitted through the reaction liquid in the reagent reaction tank is received by the photoelectric conversion means 101 shown in FIG. The photoelectric conversion unit 101 converts the received optical signal into an electric signal, and then amplifies and filters the signal by the amplification unit 102, and supplies the amplified and filtered signal to the A / D conversion unit 103. The signal output to the connection point 10a in FIG. 8 is output as shown in FIG. 9C, for example.
The A / D conversion unit 103 illustrated in FIG. 8 converts the input analog signal into a digital signal, and then outputs the digital signal to the storage unit 105.
The storage unit 105 temporarily or continuously records data that makes a round of the trajectory of the reagent reaction tank row shown in FIG.
Control unit 104 causes read signal output unit 106 to start outputting a read signal.

The control unit 104 controls the time signal tn output from the read signal output unit 106 so that the respective detection units 107a to 107d detect digital data when the ± α and ± β times have elapsed.
The time signal tn is output continuously according to the clock, the first detection unit 107a detects the digital light reception waveform at the time signal tn-β, and the second detection unit 107b detects the time signal tn-α. The third detection unit 107c detects the digital light reception waveform at the time signal tn + α, and the fourth detection unit 107d detects the digital light reception waveform at the time signal tn + β.
The received light waveform is digital data, and the quantized data is shown in FIG. 9 (d). Each detection unit does not necessarily need to be restored until quantization, and is a signal that can be multiplied by the multiplication unit, and may be a code signal if the signal is not noise but an actual received light signal. .

For example, each detection unit may convert the digital value output from the storage unit 105 illustrated in FIG. 8 and output a pulse as a light reception signal when a predetermined threshold value is exceeded.
The tn1, 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 with time in the time axis direction. At the same time, the detection unit detects the received light signal stored in the storage unit every time of ± α, ± β.
For example, when the read signal output unit 106 shown in FIG. 8 outputs the time tn1 signal to the storage unit 105, the first detection unit 107a shown in FIG. The light reception signal value at 120a of c) is detected, and the output shown in FIG. 9D is performed at the connection point 10b in FIG. The first detection unit 107b shown in FIG. 8 detects the light reception signal value at the time 120b in FIG. 9C among the light reception signals read from the storage unit 105, and the connection point 10c in FIG. The output shown in (d) is performed. The first detection unit 107c shown in FIG. 8 detects the light reception signal value at the time 120c in FIG. 9C among the light reception signals read from the storage unit 105, and the connection point 10d in FIG. The output shown in (d) is performed. The first detection unit 107d shown in FIG. 8 detects the light reception signal value at the time 120d in FIG. 9C among the light reception signals read from the storage unit 105, and the connection point 10e in FIG. The output shown in (d) is performed.

These four signals are input to the multiplication unit 108 shown in FIG. 8, and the multiplication unit 108 performs logical multiplication. In the case of the first received light pulse in FIG. 9C, the outputs of the third detection unit 107c and the fourth detection unit 107d shown in FIG.
The time width setting unit 109 determines a time width signal having a pulse width of tn ± β as shown in FIG. 9C from the output signal of the read signal detection unit 106 via the connection point 10f shown in FIG. To 110.

The determination unit 110 checks the presence / absence of an output from the multiplication unit 108 based on the time width signal from the time width setting unit 109. Since the output of the multiplication unit 108 at time tn1 is 0, the determination unit 110 It is determined that this is not the reference part, and a signal to that effect is output to the output terminal 10g.
Next, when tn2 of the time signals sequentially output from the read signal output unit 106 shown in FIG. 8, the first detection unit 107a receives light at the time position indicated by 121a of the light reception signals read from the storage unit 105. The signal is detected and output to the connection point 10b shown in FIG.
The first detection unit 107b detects the light reception signal at the time position indicated by 121b in FIG. 9C among the light reception signals read from the storage unit 105, and outputs it to the connection point 10c shown in FIG.
The first detection unit 107c detects the light reception signal at the time position indicated by 121c in FIG. 9C among the light reception signals read from the storage unit 105, and outputs it to the connection point 10d shown in FIG. The first detection unit 107d detects the light reception signal at the time position indicated by 121d in FIG. 9C among the light reception signals read from the storage unit 105, and outputs it to the terminal 10e shown in FIG.
The output signals indicated by the connection points 10b to 10e are input to the multiplication unit 108 and multiplied. At this time, since all correspond to 1, the output is 1.
When the output 1 of the multiplication unit 108 is input to the determination unit, the determination unit 110 detects tn2 from the time width signal input from the time width setting unit 109, and as shown in FIG. To output a pulse indicating the reference position.

Next, in the case of the time tn3 shown in FIG. 9C among the time signals tn output from the read signal output unit 106 shown in FIG. 8, the first detection unit 107a shown in FIG. Among the received light reception signals, the light reception signal at the time position indicated by 122a in FIG. 9C is detected and output to the connection point 10b shown in FIG.
The first detection unit 107b detects the light reception signal at the time position indicated by 122b in FIG. 9C among the light reception signals read from the storage unit 105, and outputs it to the connection point 10c shown in FIG.
The first detection unit 107c detects the light reception signal at the time position indicated by 122c in FIG. 9C among the light reception signals read from the storage unit 105, and outputs it to the connection point 10d shown in FIG.
The first detection unit 107d detects the light reception signal at the time position indicated by 122d in FIG. 9C among the light reception signals read from the storage unit 105, and outputs it to the connection point 10e shown in FIG.
The output signals indicated by the connection points 10b to 10e are input to the multiplication unit 108 and multiplied. At this time, as shown in FIG. 9D, the first detection unit 107a and the second detection unit 107b Since the output is 0, the multiplier 108 shown in FIG. 8 outputs a signal that is 0 as a result of the multiplication.
Since the signal input from the multiplying unit 108 is 0 with a predetermined time width, the determining unit 110 outputs a signal indicating that it is not the reference unit as shown in FIG.
As described above, since the reference portion is detected arithmetically, the accurate reference portion can be electrically confirmed.

An example for obtaining an effective measurement point when measuring a component 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.
Amplifying means 1301 is a means for inputting a biochemical signal subjected to photoelectric conversion from the input terminal 1a, amplifying and filtering.
Reference numeral 1302 denotes a differentiating means for differentiating the amplified biochemical signal.
At least two output terminals of the differentiation unit 1302 are provided, one is connected to a unit for determining a measurement region, and the other is a unit that performs addition averaging, integration restoration, and the like by an averaging unit. Connected.

Reference numeral 1303 denotes full-wave rectification means, which is a circuit for setting the peak of the differential signal to either + − polarity.
Reference numeral 1304 denotes measurement area detection means for inputting a signal indicating the measurement width determined by the measurement width determination means 1306, and for detecting and outputting the measurement area based on the measurement width.
Reference numeral 1305 denotes a peak detection means for detecting the peak value of the input signal, such as a Schmitt trigger circuit that detects a portion exceeding a certain threshold as a peak pulse. Good.
Reference numeral 1306 denotes measurement width determining means that may detect the measurement region from the pulse width and pulse interval of the peak pulse input from the preceding peak detection means 1305.
Note that a threshold of a predetermined height may be further set in order to detect the occurrence of a peak due to mixing of foreign matters such as bubbles.

Reference numeral 1307 denotes an averaging unit that outputs a differential signal output from the measurement region detection unit 1304 as a signal obtained by averaging.
In addition, the averaging means 1307 may be averaging means for converting to an integrated signal.

An example of the structure of the carrier connected to the analysis circuit is shown in FIG. FIG. 11A also shows another example of the configuration for the same part as in FIG.
Reference numeral 401 denotes a carrier, which is made of a translucent plastic material such as PET or polyacryl, a glass material, or the like, and has a disk shape or a sheet shape in which one or more reagent tanks are formed.
Reference numeral 402 denotes a lid, which is made of the same material as the carrier, for example, and is bonded to the carrier by an adhesive, an adhesive, or self-adsorption.
Reference numeral 403 denotes a light-absorbing member, which is formed of black or a gray sheet close to black, and a measurement window 404 formed of a circular through hole is formed immediately below the reagent reaction tank 405.

The light absorbing member 403 may be disposed at least near the reagent reaction tank 405. Reference numeral 404 denotes a measurement window. The measurement window 404 preferably has an area slightly smaller than the measurement area of the reagent reaction tank 405, for example. This is because if the area is the same as the area of the measurement surface of the reagent reaction tank 405, light leaking to the side surface of the reagent reaction tank may reach the light receiving element.
Reference numeral 405 denotes a reagent reaction tank, which is a portion that is filled with a solid or liquid reagent in advance and that reacts with a body fluid supplied from the outside, such as a supply channel, to develop a color.
A light source 406 includes a laser light source, an LED, a UV light source, and the like. Reference numeral 407 denotes a first lens body, which is formed in a normal lens, spherical shape, and has an arrangement shape for condensing mainly in the reagent reaction tank 405, and a shape and arrangement for forming parallel rays. Has been.
Reference numeral 408 denotes a second lens body for condensing or collimating the diffused light beam into a light beam suitable for light reception by the light receiving element 409.
One or both of the first lens body 407 and the second lens body 408 may be unnecessary depending on the performance and shape of the light source 406 and the light receiving element 409.

Reference numeral 409 denotes a light receiving element that converts an optical signal into an electric signal, and is made of a semiconductor such as a CDS, a phototransistor, or a diode.
Reference numeral 410 denotes a supply channel port, which is a connection part with a channel for supplying a liquid specimen to the reagent reaction tank 405, preferably quantitatively.
Reference numeral 411 denotes a light source electric lead, which is a supply path for supplying electric energy for driving the light source 406.
Reference numeral 412 denotes a light receiving side electric lead wire, which is a light receiving element for supplying a photoelectrically converted signal to the input terminal 1a in FIG.
For example, the carriers 401 may be arranged at equal intervals on the outer periphery of a disk-shaped carrier as shown in FIG.

Next, the operation of the embodiment shown in FIGS. 10 and 11A will be described in detail with reference to FIG.
A carrier 401 shown in FIG. 11 (a) is a rotating body, and a quantitative sample is supplied from the supply channel 410 to the reagent reaction tank 405, and after stirring and mixing operation, rotates at a speed of, for example, about 600 rpm while coloring. is doing. When the reagent reaction tank 405 comes directly below the light source 406, the measurement light output from the light source 406 passes through the first lens body 407, and from the measurement window 404, the carrier 401, the reagent reaction tank 405, and the lid 402. , The second lens body 408 is converted into parallel light and condensed light for the light receiving element 409 and received by the light receiving element 409. Reference numeral 413 denotes an example of an optical path.
The light receiving element 409 inputs the photoelectrically converted signal to the input terminal 1 a shown in FIG. 10 via the light receiving electrical lead 412.
In FIG.
The electric signal input to the input terminal is amplified and filtered by the amplifying unit 1301 and input to the differentiating unit 1302 as a signal shown in FIG.
31a shown in FIG. 12 (a) is an example of a peak generated when bubbles are present in the reagent reaction tank.
Differentiating means 1302 outputs a differential signal shown in FIG. 12B, and this differential signal is inputted to full-wave rectifying means 1303 and measurement region detecting means 1304 shown in FIG.

The differential signal is full-wave rectified by the full-wave rectifying means 1303 and then supplied to the peak detecting means 1305 as a full-wave rectified signal shown in FIG.
The peak detection means 1305 sets the threshold value REF1, converts the portion exceeding the threshold REF1 into a pulse having a constant amplitude as shown in FIG. 12 (d), and measures the measurement width via the connection point 1e shown in FIG. 1306 is output.
The measurement width determining means 1306 outputs the pulse shown in FIG. 12 (e) to the connection point 1f from the falling edge of the first pulse as a region width stable in measurement analysis from the falling edge of the first pulse.
When determining the width of the measurement region, the detection range from the fall of the pulse to the rise of the pulse is a temporary range determined based on the rotation speed of the carrier and a predetermined timing of the reagent reaction tank. It is preferable that the calculated value is included in the range.

The measurement area detection means 1304 passes the output of the differentiation means between the measurement width pulses obtained by the measurement width determination means shown in FIG. 12 (e), and causes the averaging means 1307 to input the passage amount.
The averaging means 1307 integrates and averages the passages and outputs the true measurement regions (31b, 31c) as shown in FIG. 12 (f) to the output terminal 1g.

FIG. 11B shows an embodiment in which the part corresponding to the optical path is protected and the optical measurement state is further improved in handling.
In FIG. 11 (b), the same components as those in FIG. 11 (a) are designated by the same reference numerals and description thereof is omitted.
Reference numeral 414 denotes a concave portion formed on a bottom surface of the carrier 401 and corresponding to a portion immediately below the reagent reaction tank 405. The area of the recess 414 preferably corresponds to at least the width of light passing through the light source 406 and the first lens body 407.
The height of the concave portion 414 may be selected as long as the concave portion 414 prevents the adhesion of fingerprints when the carrier 401 is handled by the user, and is appropriately selected within the range. For example, the height is about 0.5 mm to 1 mm. The
Reference numeral 415 denotes a light-shielding printing surface, which is formed by a screen printing method or the like.
The light-shielding printing surface 415 may be other colors having a density that does not transmit light at least in addition to black printing.
Reference numeral 416 denotes an adhesive tape, which is a transparent tape having a pressure-sensitive adhesive formed on one side and a double-sided adhesive tape, and is formed of a translucent tape with the pressure-sensitive adhesive exposed on only one side.
Reference numeral 417 denotes a fitting lid, which is made of the same member as the carrier 401 and has a thickness of about 1 mm and may or may not have translucency.
Reference numeral 418 denotes a hole, which is formed by a through-hole having a sufficient area to allow light that has passed through the reagent reaction tank 405 to pass therethrough.
Reference numeral 419 denotes a fitting hole, which is formed in the carrier 401 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 420 denotes a fitting projection, which is integrally formed with the fitting lid 415, and the tip portion forms a fitting tip portion 421 that can be contracted laterally.

In the embodiment shown in FIG. 11 (b), an adhesive tape 416 is attached on the carrier 401, and the fitting lid 417 is further covered thereon, and the fitting protrusion 420 is inserted into the fitting hole 419 on the carrier 401. Thus, the fitting lid 417 and the carrier 401 are mechanically coupled with each other by opening the fitting tip 421 outward at the tip of the fitting hole 419.
In the vertical direction of the reagent reaction tank 405, the portion corresponding to the optical path is not lost by the user's fingertip by the concave portion 414 and the hole portion 418, and the loss of transmitted light due to dirt or fingerprints. Is reduced.
The light output from the light source 406 is collected by the first lens body 407, passes through the reagent reaction tank 405 from the recess 414, and is received by the light receiving element 409 through the hole 418 and the second lens body 408. The The second lens body is not required and may not be necessary.
Since the light-shielding printing surface 415 is a thin film and does not allow light to pass therethrough, it is possible to prevent mixing of irregularly reflected light and the like with transmitted light.

Next, another embodiment will be described with reference to FIG.
FIG. 13 shows that the result of the reaction in the reagent reaction tank is too deep in the configuration shown in FIG. 10, so that even when the amount of received light is small, such as when the light transmission is insufficient and the amplitude of the electrical signal is small, It is the Example which added the structure for enabling the detection of optical information.
Reference numeral 1327 denotes a peak interval detection means for detecting the interval time of the peak signal output from the preceding peak detection means 1305.
Reference numeral 1328 denotes comparison means, which compares the peak interval signal output from the peak interval detection means 1327 with a preset interval signal, and outputs a mismatch signal if they do not substantially match.
Reference numeral 1306 denotes a measurement width determining unit. In addition to the function described with reference to FIG. 10, in the output signal from the comparison circuit 1328, the peak interval signal output from the peak interval detecting unit 1327 is longer than the preset interval signal. In the case of a non-coincidence signal, a value obtained by dividing the length by a preset interval signal minus -1 (where n ≧ 1) is a combination of a preset peak interval and a signal having a preset measurement width. Output.
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 unit 1301 shown in FIG. 13 is amplified and filtered to output the signal shown in FIG.
Reference numerals 30a and 30b denote transmitted light generated through the periphery without passing through the inside of the reaction tank, and are noise.
30c is noise generated by bubbles generated in the reagent reaction vessel.
The signal output from the amplifying unit 1301 is differentiated by the differentiating unit, and the differential waveform shown in FIG. 14B is output to the connection point 1c.
Thereafter, full-wave rectification is performed by the full-wave rectification means 1303, and a waveform as shown in FIG. 14C is output to the connection point 1d.
The peak detection means 1305 shown in FIG. 13 outputs a pulse at a portion exceeding the threshold value REF2 shown in FIG.
The peak interval detection means 1327 shown in FIG. 13 stores this pulse, and when the next peak is inputted, for example, the peak interval l1 shown in FIG. 14 is detected on the basis of the rise of the pulse, and the comparison shown in FIG. Output to means 1328.
The comparison means 1328 shown in FIG. 13 compares the peak interval l1 shown in FIG. 14 with the previously estimated reagent reaction vessel interval l2, and when n = l1 / l2-1 is 0 ≦ n <1, A signal indicating that there is an undetected portion in the reagent reaction tank is output when the interval between the reagent reaction tanks is 1 or more.

The measurement width determination unit 1306 receives the signal output from the comparison unit 1328, and outputs a preset width l3 for each preset interval l2 by the number n.
In the case shown in FIG. 14, since n = 1, a signal having a measurement width of a predetermined time width l3 obtained from the moving speed of the carrier and the diameter of the measurement surface of the reagent reaction tank after a preset interval l2 is used. Is output (FIG. 14 (f)).
For example, when n is 2, the measurement region l3 is set after a predetermined time interval l2, and then the measurement region l3 is set after a predetermined time interval l2.
The measurement area detection unit 1304 passes the differential signal by the preset time width l3, and the averaging unit 1307 performs averaging with higher sensitivity than other parts.
In FIG. 14, the portion that becomes the measurement range is indicated by a dotted square. 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 transmitted light cannot be obtained.

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 FIGS. FIG. 16 is a cross section taken along line XX ′ of FIG.
Reference numeral 401 denotes a carrier, which is made of a translucent plastic material such as PET or polyacryl, a glass material, or the like, and has a disk shape or a sheet shape in which one or more reagent tanks are formed.
Reference numeral 402 denotes a lid, which is made of the same material as the carrier, for example, and is bonded to the carrier by an adhesive, an adhesive, or self-adsorption.
Reference numeral 403 denotes a light-absorbing member, which is formed of black or a gray sheet close to black, and a measurement window 404 formed of a circular through hole is formed immediately below the reagent reaction tank 405.
Reference numeral 405 denotes a reagent reaction tank, which is formed on the carrier 401 as a cylindrical shape.
Reference numeral 410 denotes a supply channel, which is formed in a concave shape on the carrier 401, and is used for supplying a sample from the outside for a fixed amount.
Reference numeral 422 denotes a distribution channel for supplying a specimen to each reagent reaction tank.

The diameter of the bottom surface 30g of the reagent reaction tank shown in FIG. 16 is about 1.5 mm, whereas the diameter 30f of the measurement window 404 is about 1 mm.
In such a state, when the measurement light is transmitted from below into the reagent reaction tank described above, the whiskers 30a and 30b shown in FIG. 14A do not occur, and a stable waveform can be obtained.

Next, another embodiment of the present invention for removing unnecessary signals caused by the circuit, the shape of the carrier, and the processing state will be described in detail with reference to FIG.
Reference numeral 501 denotes 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, an LED light source, and a light receiving element.
Reference numeral 502 denotes an amplifying unit, for example, for amplifying an input photoelectric conversion signal in an analog manner, filtering it, and outputting it.
Reference numeral 503 denotes an offset value correcting means, which performs an operation such as removing the input offset signal from the signal related to the transmitted light transmitted through the reagent reaction tank, and outputs the calibrated signal to the connection point 5c. It is means to do.
The calculation for the calibration is, for example, a method of calculating after a digital signal is once converted or an analog calculation method, and is appropriately selected according to the size and speed of the apparatus.
Reference numeral 504 denotes 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 the offset signal to the offset value correcting means 503.
Reference numeral 505 denotes a timing signal forming means for detecting a timing at which the measuring unit and the reagent reaction tank coincide with each other in synchronization with a state in which the carrier and the measuring unit are moving relatively, and outputting a coincidence signal. It is.

Reference numeral 506 denotes reference data forming means, for example, means for temporarily storing the result of optical measurement using transmitted light in a reagent reaction tank containing a diluent, pure water or the like.
In some cases, it may be preferable to store a value obtained by performing the same measurement a plurality of times and performing addition averaging.
In addition, the value of the optical measurement result of only plasma may be stored.
Such memory is stored as an OD value, and that value is used as the reference value for OD = 0.
Reference numeral 507 denotes calibration means, which is corrected by subtracting the stored value from the optical measurement result of each reaction tank. The calibration includes meanings such as correction and correction.
The timing signal may be a signal that is preferentially oscillated from the rotational speed and a fixed arrangement angle of the reagent reaction tank after detecting the reference portion of the carrier. If the position of the reagent reaction tank is detected from the amplitude value, etc., and the color density is lost during the process, the detected position signal of the reagent reaction tank and the predetermined distance of the reagent reaction tank and the arrangement distance (angle) ) May be obtained predictively.
Further, when the stage subsequent to the amplification means is used as a means for digital processing, an A / D converter or the like may be newly added and executed by a single microcomputer storing a program.

An example of the carrier is shown in FIG. FIG. 19 shows only parts that are considered necessary for the explanation, and other parts such as a part where blood and a diluent are mixed, a part for quantification, a blood inlet, and the like are omitted.
The carrier 500 is formed of a translucent member such as polyacrylic or PET,
50a is a red light receiver, and 50b is a red light source. 51a is a green light receiver, and 51b is a green light source. 52a is a blue light receiver, and 52b is a blue light source.
Examples of the light source include lasers and LEDs, and examples of the photoreceptor include CDs and phototransistors.
53a to 53h are 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 tank is filled with a different reagent 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 track.
Reference numeral 54 denotes a calibration area provided for calibration and correction.
In the calibration region 54, 54a and 54b are calibration medium storage units, for example, provided with a reagent reaction tank in a diluted state, only plasma, pure water, and an 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 accommodating portion is also an example, and the ones accommodating other calibration media may be arranged at equal intervals.

Reference numeral 54c denotes a black region, which is black with an area that is equal to or larger than that of the reagent reaction tank.
Reference numeral 54d denotes a reference region, which is a hole that vertically penetrates, and is slit in the diameter direction. The reference area 54d is a part serving as various reference points such as a starting point, an ending point, a position recognition point for measurement in the reagent reaction tank, and a point that is a penetrating light. A reference value for measuring the maximum amount of received light may be obtained.
55a is a distribution channel, and 55b is a supply channel having quantitativeness.
Reference numeral 56 denotes, for example, two chucking holes for coupling with the reading device. Reference numeral 57 denotes 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 micropipette or a dropper.
In the configuration from the body fluid supply port 57 to various reagent reaction tanks, a part for mixing the body fluid and the diluent and separating unnecessary blood cells from the body fluid are formed, but this part is omitted.

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. Diluted mixed plasma fluid is supplied and mixed. These actions are preferably performed by rotation and capillary force.
Quantitative mixture fluid is supplied to each of the reagent reaction tanks 53a to 53h and any of the calibration regions 54 that require dilution fluid and body fluid for measurement via the distribution channel 55a and the supply channel 55b. Mixing with liquid and particulate reagents in the reaction tank to cause color reaction.
The carrier 500 rotates 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 taken along the line XX ′ in FIG. FIG. 18 (a) shows an arrangement in which the carrier 500 is actually mounted in the reading apparatus and the light receiver 50a and the light source 50b have reached the vertical direction of the reagent reaction tank 53a. For example, FIG. The structure similar to is shown.
In FIG. 18 (a), reference numeral 501a denotes an upper part of the reading device, to which a photoreceptor 50a is attached. An electrical lead wire 50c for transmitting an electrical signal to the outside is connected to the photoreceptor 50a. Reference numeral 501b denotes a lower part of the reading device, and a light source 50b is disposed in a portion corresponding to a portion immediately below the light receiving body 50a.
An electric lead wire 50d for supplying electric energy is connected to the light source 50b.
The reagent reaction tank 53a is filled with a plasma component / reagent mixed solution 501c.
In the carrier 500, various channels are formed by forming a reagent reaction tank as a recess, and the lid 500b is connected by an adhesive, a pressure-sensitive adhesive, and a self-adsorption ability.
Further, in order to efficiently obtain transmitted light, a light absorbing member 500c 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 500 is further rotated and the calibration medium storage portion 54a is placed between the red light source 50b and the red light receiver 50a. The diluent 52a is contained inside. The supply channel is not connected because it is pre-injected, but when supplying blood and developing the diluted solution, it is possible to supply only the diluted solution to the calibration medium storage portion 54a. good.
FIG. 18C shows a state where the black region 54c is placed between the red light source 50b and the red light receiver 50a.
The black region 54c is not necessarily required to have a reagent reaction tank, and it is preferable that a light absorbing member 500c is disposed at the bottom of the carrier 500 as shown in FIG.

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 through the supply channel.
The quantitative sample is agitated by a change in rotation or the like in the reagent reaction tank, and reacts with the reagent.
At the timing when the color development measurement is possible, the carrier 500 is rotated at a rotational speed of about 600 rpm, and the reference region 54d on the carrier 500 is on the optical path of the red light source 50b and the red light receiver 50a, and the green light source 51b and the green light receiver 51a. When the light passes through the light path and the light paths of the blue light source 52b and the blue light receiver 52a, the light reception measurement is performed. FIG. 21 shows a light receiving waveform of one of the three light receiving units.
In FIG. 21, reference numeral 510S denotes a waveform when the reference area 54d shown in FIG. 19 is received, and shows a double signal by the central slit.
The reference signal 510S is converted into an electric signal by the photoelectric conversion unit 501 shown in FIG. 17 and then input to the timing signal forming unit 505. 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 one of the combination of the red light source 50b and the red light receiver 50a, the combination of the green light source 51b and the green light receiver 51a, and the combination of the blue light source 52b and the blue light receiver 52a shown in FIG. The electric signal sequence obtained from one combination is shown. Voff is an offset voltage, which is a voltage generated from the characteristics of the element.
The timing signal forming means 505 outputs a free-running pulse as shown in (b), for example, to the connection point 5b with reference to 510S shown in FIG. 21 (a).
The pulse interval corresponds to the distance between the reagent reaction vessels arranged at equal intervals, and the pulse width corresponds to the area in the optical path represented by the reagent reaction vessel.

FIG. 21A shows an output signal sequence when the reagent reaction vessels 511a to 511e are measured at regular time intervals with 510S as a reference site. 21A to 511e of the signal sequence shown in FIG. 21A is a signal sequence after photoelectric conversion by receiving the transmitted light that has passed through the colored state in the reagent reaction tank containing the actual reagent.
Further, when the light source / photoreceptor unit reaches the black area 54c shown in FIG. 19, only the offset voltage Voff signal shown in FIG. 20 is received.
This offset voltage is, for example, a voltage specific to an electronic circuit such as a phototransistor configured as a light receiver, an amplifier circuit, and the like, and indicates a voltage generated on an electric circuit.
In FIG. 17, the photoelectric conversion means 511 receives the black region and converts it into an electric signal, and then amplifies and filters by the amplification means 502. The output signal of the amplifying means 502 is indicated by 512a, 512b and 512c in FIG.
These output signal voltage values are added and averaged by the offset value determining means 504, and temporarily stored or set as one offset voltage value.
Next, when the reagent reaction tank 53a shown in FIG. 19 passes the photoelectric conversion means 501 shown in FIG. 17 (for example, between the light source 50b and the light receiving element 50a in FIG. 19), the color reaction data obtained by the light receiving element 50a is amplified. The signal is amplified by the means 502 and input to the offset value correcting means 503.
The offset value correcting means 503 subtracts the offset voltage Voff input from the offset value determining means 504 from the amplified color reaction data, thereby obtaining data with a smaller error (for example, V511 shown in FIG. 21). Are output to the connection point 5c and also output to the correction means 507 and the reference data forming means 506.
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. 17, the reference data forming means 506 uses an offset value correcting means 503 to pass a reagent reaction tank filled with only water and diluent through the photoelectric conversion means 501 according to the timing signal from the timing signal forming means 505. It is detected that it has been output to the connection point 5c as calibrated calibration data, and the value is temporarily stored (for example, all of 513a to 513c shown in FIG. 21).
Further, optical data of only the diluted solution adjacent to each other is stored for each rotation, averaged, and attenuation data due to reflection and scattered light generated by the carrier is stored. Preferably, it is converted into Vt) 21 and stored.
Also, the reference data forming means 506 shown in FIG. 17 stores the optical data OD value of the penetrating light from the reference region 54d shown in FIG. 19 in the same manner as described above, and stores the reference storage OD value (for example, Vmax shown in FIG. 21). Value).
The OD value is indicated by, for example, log ₁₀ (Vin / Vout).
The carrier attenuation OD value Vg (Vmax−Vt) is obtained by subtracting the optical data (OD value Vt) of only the diluent from the optical data related to the penetrating light (510S shown in FIG. 21) (OD value Vmax). This is temporarily stored.
When the light reception signal V511 shown in FIG. 21 relating to the transmitted light of the reagent reaction tank 53a shown in FIG. 19 is input to the correction means 507 via the photoelectric conversion means 501 and the offset value correction means 503 shown in FIG. The forming unit 506 outputs the carrier attenuation data Vg shown in FIG. 21 to the correcting unit 507 shown in FIG.
The correction means 507 converts the optical data relating to the reagent into an OD value, and adds the carrier attenuation data Vg shown in FIG. 21, so that the value V511 + Vg caused by the loss of the carrier can be compensated to obtain more true color development data. It becomes.

  In addition to the dilution liquid data, the optical data of only the sample filled in the reaction tank not containing the reagent (for example, only plasma) is converted into an OD value as reference data (adding the carrier attenuation value Vg), By calculating, it is possible to obtain a more accurate color reaction value.

  The present invention enables a simpler and quicker device capable of performing signal processing, and thus allows a patient or a healthy person to easily diagnose himself / herself in a place close to life such as lifestyle-related diseases. To enable the spread of diagnosis of lifestyle-related diseases that are a problem in modern society.

  In addition, the present invention can propose a configuration capable of accurately recognizing a reference site when automatically measuring components over multiple items of body fluid, for example, even when measuring various components. Can be processed accurately, and contributes greatly to the realization of a small, simple and home-use device for automatic measurement of body fluid components.

  In addition, the present invention can easily and stably perform optical measurement when measuring a plurality of biological components on a single carrier, so that an automated body fluid component measuring device can be reduced in size and simplified. By the way, the apparatus which can measure the tendency of various diseases, such as lifestyle-related disease, is enabled.

  In addition, the present invention eliminates signal drift and other errors in a biochemical analyzer such as a blood test and an infection test, and more accurate biochemical information can be obtained quickly. The device can be configured.

It is a figure which shows one Example of this invention. It is a figure which shows the waveform for demonstrating operation | movement of one Example of this invention. It is a figure which shows the waveform for demonstrating operation | movement of one Example of this invention. It is a figure for demonstrating one Example of this invention. It is a figure which shows the other Example of this invention. It is a circuit diagram for demonstrating operation | movement of one Example of this invention. It is a figure which shows an example of the whole this invention. It is a figure which shows the other Example of this invention. It is a figure which shows the waveform for demonstrating operation | movement of the other Example of this invention. It is a figure which shows the other Example of this invention. It is a figure which shows the other Example of this invention. It is a figure which shows the waveform for demonstrating operation | movement of the Example shown in FIG. 10 of this invention. It is a figure which shows the other Example of this invention. It is a figure which shows the waveform for demonstrating operation | movement of the Example shown in FIG. 14 of this invention. The figure for demonstrating the other Example of this invention. The figure for demonstrating the other Example of this invention. The figure which shows the other Example of this invention. The figure for demonstrating the other Example of this invention. The figure for demonstrating the other Example of this invention. The figure for demonstrating the other Example of this invention. The figure for demonstrating the other Example of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Support | carrier 11 Bonding hole 12 Operation part 13 Specimen supply part 14 Distribution flow path 15a-15h Reagent reaction tank 16a-16c (R, G, B) Light source 17a-17c Photoreceptor 18 Supply flow path 101 Photoelectric conversion means 102 Amplification means DESCRIPTION OF SYMBOLS 103 A / D conversion part 104 Control part 105 Memory | storage part 106 Read signal output part 107a-107d 1st detection part-4th detection part 108 Multiplication part 109 Time width setting part
110 judgment part

Claims (21)

  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 between the reaction sites on the carrier The biochemical analyzer is arranged so that the interval between the plurality of reading units is different from the interval between the plurality of reading units.   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.   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.   The biochemical analyzer according to claim 1, wherein the carrier has a disk shape, and the reaction sites are arranged at equal intervals on the outer periphery.   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, obtained from the biochemical reaction information acquisition means at a predetermined time Detecting means for detecting the biochemical reaction information obtained, calculating means for calculating a predetermined number of pieces of information obtained by the detecting means for a predetermined time, and determining means for determining a reference site from a signal output from the calculating means A biochemical analyzer.   The biochemistry according to claim 5, further comprising a storage unit that temporarily stores information obtained by the biochemical reaction information acquisition unit, and determining data by reading data from the storage unit when determining a reference site. Analysis equipment.   The biochemical analyzer according to claim 5, wherein the reaction sites are arranged in a state having orbits, and a non-light-absorbing region including a slit in a part thereof is used as a reference region.   The biochemical analyzer according to claim 5, wherein the predetermined time is a predetermined time ahead of the central time.   6. The biochemical analyzer according to claim 5, wherein the read information is an electrical signal relating to a color reaction between a reagent and a body fluid. A biochemical analysis apparatus comprising: a change amount conversion unit that converts a biochemical signal into a signal indicating a change amount; and a measurement range determination unit that determines a measurement range from the signal obtained by the change amount conversion unit. The biochemical analyzer according to claim 10, wherein the signal indicating the amount of change is a differential signal. The biochemical analysis means according to claim 10, wherein the measurement range is between peaks of a signal indicating the change amount. 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. The reagent reaction tank is irradiated with measurement light from the outside, and reflected or transmitted light is emitted. The biochemical analyzer according to claim 10, wherein the biochemical component is measured to measure a biochemical component. A plurality of reagent reaction vessels arranged on the same track, and a measurement unit that optically measures the components with respect to the reagent reaction vessel. The biochemical analyzer according to claim 10, which is a biochemical analyzer that measures components in a reaction tank. Reagent reaction tank detection means for detecting a part of the reagent reaction tank, and when the interval between the parts detected by the reagent reaction tank detection means is a predetermined interval or more, a value −1 obtained by dividing the interval by the prediction interval is 1 15. The biochemical analyzer according to claim 14, further comprising reagent reaction tank part determining means for determining a predetermined interval as a part of the reagent reaction tank in the above case. A carrier composed of a translucent member provided with a reagent reaction tank, and the reagent reaction tank to which the sample is supplied are irradiated with measurement light from the outside, and the light obtained through the reagent reaction tank is received to measure the sample components In the biochemical analyzer, a light absorbing member such as a film that absorbs light, a printed surface, and a painted surface is disposed in the direction of the irradiation surface that irradiates the measurement light to the reagent reaction tank, and the measurement window A biochemical analyzer having an area smaller than that of the measuring light irradiation surface of the reagent reaction vessel. 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. The biochemical analyzer according to claim 16, wherein the measurement window is formed in a concave shape. A reagent reaction tank arranged on the trajectory of the measurement light by irradiating the measurement reaction light from the outside with a relative movement to the reagent reaction tank supplied with the sample and the carrier composed of a translucent member having a plurality of reagent reaction tanks In the biochemical analyzer that receives the light obtained through the measurement and measures the analyte component, the biochemical analyzer is provided with a reference site for permeation measurement on the carrier. 20. The reference part is any one or more of a black surface, a through-hole, a reference liquid tank, an empty reagent reaction tank, a diluent tank, a measurement sample (plasma, etc.), and a sealed tank. Biochemical analysis equipment.   The biochemical analyzer according to claim 19, further comprising a calibration unit that performs offset calibration based on a light reception signal when the reference portion is black.

Images