JP4581898B2 - Test piece measuring device - Google Patents

Description

  The present invention relates to a test piece measuring apparatus, and more particularly to an apparatus for developing a test solution on a test piece and quantifying the concentration of a specific component in the test solution.

  In the field of clinical diagnosis, the presence or concentration of specific components in test solutions such as blood, plasma, serum, and urine collected from subjects are measured, and doctors make diagnoses based on the results. Is going. For these measurements, there is a large machine used in clinical laboratories and a small machine for so-called POCT (Point of Care Testing) that obtains diagnostic results in the immediate vicinity of the subject, such as a bedside. is there.

  Large machines have high measurement accuracy and reliability, but large hospitals conduct analysis in their clinical laboratories, or small hospitals that do not have clinical laboratories outsource to clinical laboratories for analysis. Therefore, it took time to obtain the analysis results. In addition, the operation of the large machine is complicated, requiring specialized techniques for the preparation and pretreatment of the solution to be inspected, and the inspection cost is high.

  On the other hand, a small machine has excellent portability and portability, and provides an advantage that measurement results can be obtained immediately in the immediate vicinity of the subject and that the inspection cost is relatively low. In addition, it can be measured with simple pretreatment and can be easily operated without requiring specialized knowledge.However, since blood and urine collected directly from fingertips and ear lobes are often used as they are, environmental temperature, humidity There is also a drawback that the state of the solution to be inspected and the like easily affect the measured value.

  As an example of a conventional small machine, there is an apparatus for optically quantifying the degree to which a specific component contained in a test solution stains a reaction zone on the test piece by developing the test solution on a test piece.

  Describing in detail with reference to FIG. 8, the test piece 101 is a strip-shaped PET (polyethylene terephthalate) film 102 on which a porous member such as a nonwoven fabric or a membrane is arranged as a development layer 103. The development layer 103 is provided with reaction zones 104, 105, and 106 in which reagents are immobilized. In addition, a cavity in which a solution to be inspected can be collected by a cover 107 is formed at one end of the test piece 101, and the solution to be inspected is introduced into the cavity from the opening on the end face of the test piece 101.

  When the user adds about 50 μl of the test solution to the test piece 101, the test solution penetrates the development layer 103 using capillary action to develop the test piece 101. The reaction solution passes through the three reaction zones provided in the test piece 101 sequentially from the upstream reaction zone 104 to the reaction zones 105 and 106, thereby reacting by an immunological antigen-antibody reaction. Stain the area.

  In a test piece using such immunochromatography, the color intensity depends on the concentration of a specific component in the test substance contained in the test solution. Therefore, conventionally, the time until the added solution to be inspected has flowed too far downstream of the test piece and the reaction is expected to be completed in the three reaction zones is measured in advance using a number of test pieces. An average value was taken, for example, 5 minutes was set as the timing for measurement.

  In the actual optical concentration measurement, after adding the solution to be inspected, when the timer 116 measures 5 minutes, the control unit 114 drives the test piece drive unit 118 to emit the analysis light emitted from the light emitter 110. The test piece 101 is moved so that 108 scans from the upstream side to the downstream side of the test piece 101. When each reaction zone is scanned, the detection light 109 corresponding to the color density is read by the detector 111, converted to a density by the density calculation unit 119, and each result is stored in the memory 117.

The apparatus changes the sensitivity of each reaction zone to a specific component in order to widen the measurable range, and refers to the concentration of each reaction zone stored in the memory 117 and determines that the concentration of the specific component is low. The result of the reaction zone 104 is converted into the concentration by using the result of the reaction zone 106 when the concentration is high.
International Publication No. 03/014740 Pamphlet

  However, when the present inventors conducted extensive research in the above-described conventional measuring apparatus, the timing at which the measurement is performed is greatly related to the measurement accuracy, and the timing of the measurement is determined after a lapse of a certain time since the solution to be inspected was added. It was found that it was not possible to improve the accuracy of the measured values if they were unified.

  Specifically, for example, when blood is used as a solution to be tested and the concentration of a specific component contained therein is to be measured, even if the concentration of the specific component is the same, the viscosity or non- When the development layer 103 such as a membrane is chromatographed depending on the presence / absence of a coagulant, environmental temperature, humidity, etc., the development speed of each test piece is slightly different. It was found that this slight difference appears as a difference in coloration depending on the density and causes variations in measured values, so that the measurement accuracy cannot be improved.

  The present invention solves the above-mentioned conventional problems, and even if the speed at which the test piece is developed varies depending on the state of the solution to be inspected and the surrounding environment, the measurement result with high accuracy is not affected by it. It aims at providing the test piece measuring apparatus obtained.

  In order to solve the above-described problem, the test piece measuring apparatus of the present invention is arranged in a development layer where the added solution to be inspected is developed, at a plurality of locations from the upstream side to the downstream side of the flow of the solution to be inspected. A test piece that forms a reaction zone that reacts with a specific component in the solution to be inspected to produce an optically detectable result is mounted, and the analysis light and the test piece are combined while irradiating the test light with the analysis light. A test strip measuring device that detects the detection light from the reaction zone by scanning a plurality of reaction zones of the test strip with the analysis light by relatively moving, and quantifies the concentration of the specific component. The solution to be inspected which is developed in order from the first reaction zone located on the most upstream side of the test piece toward the n-th reaction zone on the downstream side thereof reaches the second reaction zone. Previously, the tip position of the flow of the solution to be inspected to unfold the test piece By optically detecting, the development rate of the solution to be inspected is calculated, and the reaction time until the amount of change in the measured value in the first reaction zone falls below a predetermined value is measured. In addition, the measurement timing for performing analysis by irradiating the analysis light in the second reaction zone and the subsequent reaction zones is calculated from the development speed and the reaction time.

  According to the test piece measuring apparatus of the present invention, it is possible to perform measurement at a timing suitable for the developing speed regardless of the speed at which the solution to be inspected develops the test piece. It becomes possible.

  Further, according to the test piece measuring apparatus of the present invention, when optical reading is performed by irradiating the test piece with light and scanning, the number of times of reading can be reduced. For this reason, when the test piece measuring apparatus is configured to be driven by a battery, the battery life can be extended, and portability and portability as a POCT device are improved.

  Embodiments of a test piece measuring apparatus according to the present invention will be described below in detail with reference to the drawings. However, the embodiment described below is an example and does not limit the present invention.

(Embodiment 1)
In the first embodiment, a test piece measuring apparatus for measuring blood CRP concentration (C-reactive protein concentration) using blood as a solution to be tested will be described.

  FIG. 1 is a configuration diagram of a test piece measuring apparatus according to the present embodiment. In FIG. 1, the same reference numerals are given to the same configurations as the conventional one.

  In the figure, a test piece 101 is a strip-shaped thin piece having a length of 30 mm, a width of 6 mm, and a thickness of 0.5 mm, and blood is spotted on the end face on the side where the cover 107 is arranged and introduced into the inside through the opening. Is done. The introduced blood penetrates and spreads on the test piece 101 in the long side direction, passes over all the reaction zones 104, 105, 106, and moves to the opposite end of the test piece 101. The side on which the blood is spotted is called upstream and the opposite side is called downstream.

  The support 102 is a PET film having a thickness of 0.3 mm, which prevents blood leakage and maintains the strength of the test piece 101. In addition to the above, plastics such as acrylic and vinyl chloride, glass, metal, etc. can be used as long as the support 102 is easily processed into a thin piece, is a moisture-impermeable material, and is not easily deformed. .

  The spreading layer 103 uses a thin film of nitrocellulose having a thickness of 0.3 mm. Since the spreading layer 103 is porous, blood develops by capillary action. In addition to the above, a membrane, glass fiber, filter paper, non-woven fabric, cloth, or the like can be used for the spreading layer 103 as long as it is moistened with blood and causes capillary action.

  The first reaction zone 104 is the most upstream reaction zone. In the first reaction zone 104, an antibody immunologically specific to CRP is immobilized in advance. Although not shown, a labeling agent specific to CRP is arranged further upstream of the first reaction zone 104. When blood develops, CRP in the blood is labeled with this labeling agent. . When the labeled CRP reaches the reaction zone 104, the first reaction zone 104 is stained with the red color of the labeling agent by antigen-antibody reaction.

  Here, when the concentration of CRP in the blood is high, more CRP adheres to the reaction zone, so that the reaction zone is stained more clearly. Conversely, when the CRP concentration in the blood is low, it is stained lightly. The density is calculated by optically reading the shade of this color.

  The second reaction zone 105 is a reaction zone that is dyed next to the first reaction zone, and is disposed on the downstream side of the first reaction zone. In the second reaction zone 105, as in the first reaction zone 104, an antibody that specifically binds to CRP is immobilized. The second reaction zone 105 is disposed at a position of 2 mm downstream from the first reaction zone 104. The third reaction zone 106 is the most downstream reaction zone arranged at equal intervals in the downstream direction from the first reaction zone, and is dyed last. In this embodiment, three reaction zones are provided. However, the present invention is not limited to this, and more reaction zones can be provided, or two reaction zones can be provided.

  In the present embodiment, the reaction zones are arranged at an equal interval of 2 mm. However, if the positions of the reaction zones are stored by an apparatus, the reaction zones can be arranged at an arbitrary interval.

  In the present embodiment, the flow path can be easily created by sequentially arranging the reaction zone positions in the direction of blood flow, the amount of blood required for the test can be reduced, and the test piece and the optical Since the relative movement with the system is in one direction, the configuration of the apparatus can be simplified, which is preferable.

  The cover 107 has a function of protecting the above-described labeling agent applied to the spreading layer 103 and limiting the amount of blood to be spotted. The cover 107 has a gap of about 2 mm between the spread layer 103 and about 50 μl of blood is sucked into this gap. The labeling agent applied to the spreading layer 103 under the cover 107 dissolves in the spotted blood and is transferred downstream while labeling the CRP in the blood.

  The light emitter 110 is inexpensive, easy to handle, has a long life, and has a stable output, and therefore uses a laser diode (LD) to generate the analysis light 108. As the analysis light 108, a wavelength having the highest sensitivity in terms of the property of the labeling agent is selected and set to 635 nm. The output is optimally 3 mW from the balance of noise and signal.

  The light emitter 110 only needs to emit an electromagnetic wave to the test piece. In addition to the laser diode (LD), the light emitter 110 can be selected from an LED (light emitting diode), an incandescent lamp, and the wavelength and output can be freely selected. .

  The detection light 109 is reflected and diffused light generated when the test light 101 is irradiated with the analysis light 108, and has information on the CRP concentration in the reaction zone and information on the presence or absence of the solution to be inspected. The detection light 109 may be scattered light having information on the test piece, and may be transmitted light, diffracted light, diffused light, fluorescence excited by irradiation light, or the like.

  The detector 111 uses a photodiode (PD) and converts a change in the amount of the detection light 109 into an electric signal. In order to detect the detection light 109 efficiently, the detector 111 is arranged on an extension line having an angle of 45 degrees with respect to the irradiation angle of the analysis light 108. The detector 111 may be arranged at a position where the detection light 109 can be received. When the detection light 109 is transmitted light, the detector 111 may be arranged on the opposite side of the test piece 101. However, in this case, it is desirable to use a transparent or translucent material for the support 102 of the test piece 101. The detector 111 only needs to replace the change in light with an electric signal. In addition to the above example, a position sensitive device (PSD), a charge coupled device (CCD), or the like can be used.

  The display unit 115 uses an inexpensive, easy-to-handle, long-life, lightweight liquid crystal panel. The display unit 115 may be any means that informs the user of the measurement result and the state of the measuring instrument, and can be selected from general display devices such as a cathode ray tube monitor, a plasma monitor, an organic EL panel, and a printer.

  In this measuring apparatus, the irradiation position of the analysis light 108 is fixed, and the test piece 101 is moved in parallel by the test piece driving unit 118 for measurement. In the present embodiment, the analysis light may be configured to irradiate and scan all reaction zones. For example, the test piece 101 may be fixed and the irradiation position of the analysis light 108 may be moved.

  Note that specific operations of the reaction time detection unit 120, the development speed calculation unit 121, and the n-th region measurement time calculation unit 122 in FIG. 1 will be described together with the description of the operation of the measurement apparatus described later.

  Next, the operation of the test piece measuring apparatus according to the present embodiment will be described with reference to FIGS. First, the operation | movement which calculates | requires the expansion | deployment speed | velocity | rate of the blood which expand | deploys a test piece is demonstrated using FIG. 2, FIG.

  FIG. 2A is a cross-sectional view showing a state in which blood 200 is spotted on a test piece 101 and analysis light is irradiated by a test piece measuring apparatus immediately after the start of blood development, and FIG. FIG. 2A shows the signal level of detection light obtained by the detector 111 when the analysis light 108 is scanned in the direction of the arrow in FIG. The horizontal axis 201 indicates the moving distance from the end of the test piece 101.

  FIG. 3 shows a case where the blood 200 has been developed and developed to just before the first reaction zone 104. In FIG. 3, the test piece 101 is not moved, and irradiation with the analysis light 108 is performed at a position downstream of the blood tip position detected in FIG. 2 and upstream of the first reaction region. It shows how to continue. In addition, the horizontal axis in the graph of FIG.3 (b) has shown time passage.

  When the test piece 101 spotted with the blood 200 is attached to the test piece measuring apparatus, the test piece 101 is moved while irradiating the test piece 101 with the analysis light 108 from the light emitter 110, and the analysis light 108 is moved downstream of the test piece 101. Scan from the side edge to the upstream side. The detection light reflected by the surface of the test piece 101 is detected by the detector 111. When there is blood in the detection light, the light is absorbed by the blood, and the signal level from the detector 111 is lowered. Conversely, when there is no blood at the irradiation position of the analysis light, the signal level of the detector 111 is increased.

  Therefore, when the test piece 101 is scanned, the signal shown in FIG. 2B is detected. The position at which the signal level of the detection light has suddenly changed is determined as the tip position of the blood to be developed, and the tip position and the detection time are stored in the memory 117.

  Next, in FIG. 3A, the test piece 101 is stopped at a position where the test piece 101 is moved about 5 mm downstream from the tip position of the blood 200 stored in FIG. Irradiate intermittently. When the blood 200 arrives at the position of the analysis light 108, the signal level received by the detector 111 changes as shown in FIG. With this sudden change point, it is determined that blood has arrived, and the detected detection time is stored in the memory 117.

  Here, the deployment speed calculation unit 121 shown in FIG. 1 calculates the difference between the detection time detected in FIG. 2 and the time detected in FIG. 3, and the time required for the blood 200 to expand 5 mm. By dividing, the development speed of the blood 200 is obtained and stored in the memory 117.

  The method of obtaining the development speed is not limited to the above method, and after waiting for a predetermined time after detecting the tip position in FIG. 2, the downstream side is further scanned with the analysis light, and again, By detecting the tip of the flow, the development speed calculation unit 121 may perform a process for calculating the development speed from the distance of blood to be developed at a predetermined time.

  In the description of FIG. 2 and FIG. 3 described above, the blood development speed is detected at a position upstream of the first reaction zone 104 for the following reason. By detecting the development speed of the specimen at the upstream position, the reaction time after the second reaction zone 105 can be predicted and measured, and the reaction zone intervals can be narrowed.

  After obtaining the development speed as described above, the optimum measurement timing for reading the color reaction in the first reaction zone is subsequently obtained, and the measurement value in the first reaction zone is read at that timing.

  FIG. 4A shows that the test piece 101 is driven to a position where the analysis light 108 irradiates the first reaction zone 104 in order to detect the color reaction in the first reaction zone 104 and intermittently. FIG. 4B shows a change in the signal level of the obtained detection light. FIG. 4B shows how the analysis light 108 is irradiated. In FIG. 4B, the vertical axis 203 indicates the signal level obtained by the detector 111, and the horizontal axis 204 indicates time.

  In FIG. 4B, 205 indicates the time when blood reaches the first reaction zone 104, and the color reaction in the first reaction zone 104 starts at this time point. In the initial stage of the color reaction immediately after the blood 200 arrives, since a lot of blood 200 passes through the first reaction zone 104, the amount of change in the measured value with respect to time is large, and then the flow rate decreases. The amount of change decreases rapidly, and the color reaction is stabilized. Furthermore, when the solution 202 to be inspected stops flowing, the measured value decreases due to factors such as drying.

  Therefore, the optimum timing for obtaining the measurement value of the color reaction in the first reaction zone is preferably performed during a period when the reaction is stable. For example, it is preferable to detect the value at the time point 206 when the reaction enters the stable period. .

  The optimum measurement timing is obtained by the reaction time detection unit 120 in FIG. 1, and as a method for obtaining the optimum measurement timing, for example, the acceleration of the change in the signal level of the detection light is obtained, and the acceleration falls below a predetermined value. It can be determined that the stable period has been reached. Although the method for obtaining the acceleration of the change in the signal level is not described in detail, it can be obtained by obtaining the change rate of the signal level of the detection light at a predetermined time interval and further obtaining the change rate. When determining the acceleration, the period during which the amount of change is large is irradiated with the analysis light at intervals of, for example, about 5 seconds, and the analysis light is irradiated at intervals of about 1 second as the amount of change decreases. By changing the time interval, it is possible to reduce the calculation load of the measuring apparatus and to reduce power consumption when the battery is driven.

  This time interval may be set in two stages as described above. However, the time interval can be set flexibly according to the degree of progress of the reaction that changes every moment by multiplying the ratio of the obtained change by a predetermined coefficient. It can also be set, and further, the setting value can be changed by dividing into more stages depending on the rate of change.

  As described above, the reaction time detection unit 120 obtains the optimum measurement timing of the color reaction in which the reaction is always stable even if the signal level change timing in the first reaction zone changes depending on the environmental conditions. Then, the reaction time detection unit 120 further calculates the time from the time 205 when the blood tip reaches the first reaction zone to the optimum measurement timing 206 as the reaction time.

  As described above, the reaction time from when blood reaches the first reaction zone 104 until the reaction is stabilized is obtained, and at the optimum timing, the detection light in the first reaction zone 104 is read, The concentration in the reaction zone is calculated by the concentration calculation unit 119 and this value is stored in the memory 117.

  Subsequently, the color reaction in the second reaction zone 105 is read. This reading timing is determined by the n-th region measurement time calculator 122 in FIG. 1 from the blood development speed and the reaction time obtained as described above. Ask.

  Here, the operation in the n-th region measurement time calculation unit 122 that calculates the measurement time (measurement timing) in the second reaction zone 105 will be described in detail with reference to FIG. 501 in FIG. 5 is an estimation of a change in the signal level of the detection light that may be obtained in the second reaction zone 105. In the graph, the vertical axis 502 is the detection light signal level in the second reaction zone 105, the horizontal axis 503 is time, 504 is the optimum measurement timing in the second reaction zone 105, and 505 is the first reaction zone 104 to the second. 506 is the time it will take for blood to develop to the reaction zone 105, and 506 is the time it will take for the reaction in the second reaction zone to stabilize after the blood reaches the second reaction zone. Respectively.

  First, in order to calculate the time 505 required for blood to develop from the first reaction zone 104 to the second reaction zone 105, the first reaction zone 104 and the second reaction zone 104 are calculated at the blood development speed obtained above. The distance from the reaction zone 105 is divided.

Next, an interval is determined from the time at which blood is estimated to have reached the second reaction zone to the time at which the reaction in the second reaction zone will stabilize. This is the same as the reaction time obtained in the first reaction zone 104 . That is, the measurement timing in the second reaction zone 105 is the time obtained by dividing the distance between the first reaction zone 104 and the second reaction zone 105 by the development speed obtained from reaching the first reaction zone 104. To the reaction time obtained in the first reaction zone 104.

  The timing of measurement in the third reaction zone 106 is also calculated in the same manner as in the second reaction zone, and then the concentration in the third reaction zone 106 is obtained. The respective concentrations of the first, second, and third reaction zones obtained as described above are mutually calculated, and the final CRP concentration is obtained by the concentration calculation unit 119 and displayed on the display unit 115.

  As described above, in the first embodiment, the analysis light is actually irradiated in each of the second and third reaction zones to detect that the blood has reached, or in the second and third reaction zones. Rather than obtaining the optimal measurement timing, the measurement timing in the second and third reaction zones is estimated from the development speed obtained in the upstream region in advance and the optimal measurement timing in the first reaction zone. Like to do.

  In addition, regardless of the measurement method according to the present embodiment, the color change in each reaction zone can be measured individually, but in that case, in order to obtain the maximum value of the change in the measured value individually. , You will have to continue to measure changes in the reaction zone for a longer time. Therefore, it is necessary to widen the interval between the reaction zones on the test piece, and as a result, the measurement time becomes longer. Further, since the interval between the reaction zones is widened, the amount of the specimen and the antigen reaching the reaction zone on the downstream side are reduced, and the reaction becomes insensitive. From these facts, the method according to the present embodiment can measure the change with high accuracy in a short time as compared with the case where the change is obtained by actually measuring each one individually. In addition, since it is not necessary to continuously measure the reaction zones after the second reaction zone, the laser irradiation time can be reduced, battery-driven measurement can be performed, and the life of the equipment can be extended. it can.

(Embodiment 2)
In the second embodiment, a test piece measuring apparatus that uses a test piece different from that in the first embodiment will be described.

  FIG. 6 is a configuration diagram of a test piece in the present embodiment. In the figure, the difference from Embodiment 1 is that the flow path of blood is divided into two along the flow direction, and reaction zones having different sensitivities are alternately arranged on the respective flow paths.

  When blood is spotted on the cover 107 at the tip of the test piece 601, the blood penetrates the two flow paths 601 and 602 almost simultaneously. When a test piece on which blood is spotted is inserted into the instrument, the test piece is irradiated with light, and the tip of the blood flow on each flow path is detected. Further, the time during which the blood flows is measured while moving further downstream and intermittently irradiating light, and the blood deployment speed is calculated. Thereafter, the position information of the reaction zone stored in advance is read, and the measurement timing of the reaction zone is estimated. At this time, if the reaction zones on the two flow paths react at the same time, the optimal timing may overlap and it may not be possible to detect with one light, so the reaction zones need to be arranged alternately.

  As described above, by arranging reaction zones with different sensitivities and predicting the optimal measurement time, it is possible to arrange more reaction zones and expand the range of concentrations that can be measured. Since the sensitivity of the reagent to be immobilized on can be increased, it can be determined with high accuracy. However, in such an arrangement, it is necessary to drive the test piece drive unit not only in the direction of the flow path but also in the direction perpendicular to the flow path.

(Embodiment 3)
In the third embodiment, a test piece measuring apparatus that uses a test piece different from that in the first embodiment will be described.

  FIG. 7 is a configuration diagram of a test piece in the present embodiment. In the figure, the difference from the first embodiment is that the flow path for blood flow is formed in a spiral shape, and different types of reaction zones are radially arranged on the flow path.

  When blood is spotted on the cover 107 at the tip of the test piece 701, the blood expands spirally on the flow path shown in the figure. A plurality of reaction zones are arranged on the flow path, and are applied with reagents having different sensitivities and reagents that react with different blood components. When the test piece is inserted into the device, light scans along the flow path and detects the tip of the deposited blood. Furthermore, it moves downstream along the flow path, detects the tip of the blood to be developed while intermittently irradiating light, and calculates the blood deployment speed from the amount and time of blood movement. Based on the calculated development speed and the position information of the reaction zone stored in advance, the measurement timing is predicted and the reaction zone is measured.

  As described above, in the third embodiment, a spiral flow path is formed in a test piece, a reaction zone is arranged on the flow path, a blood development time is calculated, and a reaction time of each reaction zone is predicted. As a result, a large number of reaction zones can be arranged on a single test piece, and measurement can be performed accurately and with high sensitivity. In addition, by replacing the reagent to be immobilized in the reaction zone with a different type, it becomes possible to carry out various inspection items at once.

  The test piece measuring apparatus according to the present invention is not limited to blood, and can measure with higher accuracy when the solution to be tested is measured on a test piece having a plurality of reaction zones. In addition, since the life of the battery is extended and the portability and portability are increased, it is useful for POCT equipment.

The block diagram of the test piece measuring apparatus in one embodiment of this invention Side view and signal waveform diagram explaining operation of the device Side view and signal waveform diagram explaining operation of the device Side view and signal waveform diagram explaining operation of the device Signal waveform diagram explaining the operation of the device The top view which shows the test piece used for other embodiment of this invention The top view which shows the test piece used for other embodiment of this invention Configuration of a conventional test piece measuring device

Explanation of symbols

DESCRIPTION OF SYMBOLS 101 Test piece 102 Support body 103 Expanding layer 104 1st reaction zone 105 2nd reaction zone 106 nth reaction zone 107 Cover 108 Analysis light 109 Detection light 110 Light emitter 111 Light reception part 114 Control part 115 Display part 116 Timer 117 Memory 118 Test piece drive unit 119 Concentration calculation unit 120 Reaction time detection unit 121 Deployment speed calculation unit 122 Reaction region measurement time calculation unit 200 Blood

Claims (3)

It is possible to detect optically by reacting with a specific component in the test solution at a plurality of locations from the upstream side to the downstream side of the flow of the test solution on the development layer where the added test solution is developed. A test piece that forms a reaction zone that produces a result is mounted, and while the test piece is irradiated with analysis light, the analysis light and the test piece are moved relative to each other, and a plurality of reaction zones of the test piece are used with the analysis light. By detecting the detection light from the reaction zone, and quantifying the concentration of the specific component,
Before the solution to be inspected which is developed in order from the first reaction zone located on the most upstream side of the test piece to the nth reaction zone on the downstream side reaches the second reaction zone, By optically detecting the tip position of the flow of the solution to be inspected to develop the test piece, the development speed of the solution to be inspected is calculated,
Measuring the reaction time until the amount of change in the measured value in the first reaction zone falls below a predetermined value,
A test piece measuring apparatus characterized in that a measurement timing for performing analysis by irradiating analysis light in the second reaction zone and the subsequent reaction zones is calculated from the development speed and the reaction time. It is possible to detect optically by reacting with a specific component in the test solution at a plurality of locations from the upstream side to the downstream side of the flow of the test solution on the development layer where the added test solution is developed. A light emitter that emits analytical light to a test piece that forms a reaction zone that produces a result;
A detector for receiving detection light from the test piece irradiated with the analysis light;
A driving unit for relatively moving the analysis light and the test piece so that a plurality of reaction zones of the test piece are scanned with the analysis light;
Before the solution to be inspected which is developed in order from the first reaction zone located on the most upstream side of the test piece to the nth reaction zone on the downstream side reaches the second reaction zone, A development speed calculation unit that calculates a development speed of the test solution by optically detecting a tip position of a flow of the test solution that develops the test piece;
A reaction time detector for measuring a reaction time until a change amount of a measured value in the first reaction zone falls below a predetermined value,
An n-th region measurement time calculation unit for calculating a measurement timing in the n-th reaction zone from the development rate and the reaction time obtained by the development rate calculation unit and the reaction time detection unit;
From the detection light detected by the detector in the first reaction zone and the detection light in the nth region detected at the measurement timing calculated in the nth region measurement time calculation unit, A concentration calculator for calculating the concentration of the specific component;
A test piece measuring apparatus comprising: 3. The test piece measuring apparatus according to claim 1, wherein a reaction time until an acceleration of a change in the measured value in the first reaction zone falls below a predetermined value is measured. .

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