WO2013061681A1 - Dispositif de mesure d'un composant et procédé associé - Google Patents

Dispositif de mesure d'un composant et procédé associé Download PDF

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Publication number
WO2013061681A1
WO2013061681A1 PCT/JP2012/071589 JP2012071589W WO2013061681A1 WO 2013061681 A1 WO2013061681 A1 WO 2013061681A1 JP 2012071589 W JP2012071589 W JP 2012071589W WO 2013061681 A1 WO2013061681 A1 WO 2013061681A1
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WIPO (PCT)
Prior art keywords
component
concentration
specimen
test paper
light
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PCT/JP2012/071589
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English (en)
Japanese (ja)
Inventor
秀幸 桃木
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テルモ株式会社
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Publication of WO2013061681A1 publication Critical patent/WO2013061681A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
    • G01N21/78—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator producing a change of colour
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/59—Transmissivity
    • G01N21/5907—Densitometers
    • G01N2021/5915—Processing scan data in densitometry
    • G01N2021/5923—Determining zones of density; quantitating spots

Definitions

  • the present invention relates to a component measuring apparatus and a component measuring method.
  • An apparatus for measuring the concentration of a specific component in body fluid, for example, glucose in blood by a colorimetric method is known.
  • the collected body fluid hereinafter referred to as a specimen
  • the spotted specimen is developed on a test paper and reacts with the reagent to cause a color reaction according to the concentration of the specific component.
  • the colorimetric component measuring apparatus calculates the concentration of the specific component contained in the specimen by optically measuring the color generated by the color reaction.
  • specimen development speed the speed at which a specimen is developed on a test paper
  • factors such as specimen quantity, specimen properties, environmental temperature, and variations in test paper production. If the development speed of the specimen on the test paper changes due to such factors, for example, the specimen does not sufficiently develop on the test paper within the measurement time, or the start of the color reaction is delayed. As a result, it is difficult to correctly calculate the concentration of the specific component in the sample.
  • Patent Document 1 discloses that a color reaction on a test paper is measured by dividing it into a plurality of regions, and a measurement value in a region where the specimen is not sufficiently developed is not used for calculating the component concentration.
  • an object of the present invention is to provide a component measuring apparatus and a component measuring method capable of accurately calculating the concentration of the specific component in the sample even when the developing speed of the sample on the test paper changes.
  • the component measurement apparatus of the present invention is a component measurement apparatus that measures the concentration of a component based on the degree of color development of a reagent that reacts with a component contained in a specimen, and includes an irradiation unit, a detection unit, a component concentration calculation unit, Have The irradiation means irradiates light onto the test piece to which the specimen is attached.
  • the detection means detects the reflected light reflected by a plurality of different regions on the test piece.
  • the component concentration calculation means calculates the concentration of the component contained in the sample based on the intensity of the reflected light at the end time after a predetermined time has elapsed from the start time at which the sample has infiltrated and started coloring in a plurality of different regions.
  • the component measurement method of the present invention is a component measurement method for measuring the concentration of a component based on the degree of color development of a reagent that reacts with a component contained in a sample, and starting irradiation of light on a test piece to which the sample is attached. And a step of starting detection of the reflected light respectively reflected in a plurality of different areas on the test piece, and a reflection of an end time after a predetermined time has elapsed from the start time when the specimen invaded and started coloring in the different areas. Calculating the concentration of the component contained in the specimen based on the light intensity.
  • the present invention it is possible to prevent the change in the development speed from affecting the calculation of the component concentration of the specimen by aligning the coloration start times in a plurality of different regions on the test piece. Therefore, the component concentration of the specimen can be calculated with high accuracy. Further, even if a development failure occurs in a part of the area on the test piece, the measurement can be continued and the measurement value can be calculated.
  • FIG. 3A is a schematic diagram for illustrating the development of blood spotted on a test paper
  • FIG. 3B is a diagram for explaining a reflectance curve in a region A68 of FIG. 3A. It is.
  • FIGS. 7A and 7B are diagrams for explaining a method of setting the upper limit value and the lower limit value of the reflectance. It is a flowchart for demonstrating the procedure which calculates the glucose level contained in the blood in the 2nd Embodiment of this invention. It is a figure explaining the processing content in each step of the flowchart shown in FIG. It is a figure for demonstrating the procedure which calculates the glucose level contained in the blood in the 3rd Embodiment of this invention with the processing content in each step.
  • FIG. 1 is a schematic block diagram for explaining a component measuring apparatus according to the first embodiment of the present invention.
  • the component measuring apparatus of this embodiment arranges the coloration start times in a plurality of different regions on the test piece.
  • the principal part of the component measuring apparatus of this embodiment is demonstrated, and description is abbreviate
  • a colorimetric blood glucose measuring device that measures a blood glucose level based on a color change (coloring) of a reagent that reacts with glucose contained in blood
  • the colorimetric blood glucose measurement device the color of the reagent that reacts with blood by irradiating light on the opposite side of the blood adhering surface of the test paper (test strip) to which blood has adhered and receiving the reflected light from the test paper
  • the concentration of glucose contained in the blood is measured.
  • the test paper contains a reagent that develops color by reacting with glucose in the blood, and the color development of the test paper increases as the glucose concentration increases.
  • the glucose concentration is measured by utilizing the change in the amount of light received due to the difference in the color density.
  • light having a wavelength of 620 to 640 nm red light
  • the hematocrit value for correcting the measured glucose concentration is also measured.
  • the hematocrit value is measured based on the concentration of hemoglobin in the blood.
  • light having a wavelength of 510 to 540 nm (green light) is preferably used.
  • red light and green light are alternately and periodically irradiated on the test paper to measure the glucose concentration and the hematocrit value. That is, in this embodiment, the glucose concentration and the hematocrit value are alternately measured in a time division manner using two wavelengths of light. Since the hematocrit value can be measured in the same manner as when measuring the glucose concentration, the following description focuses on the measurement of the glucose concentration. Further, the method for calculating the glucose concentration and the hematocrit value from the reflectance of light of each wavelength is the same as the conventional method, and thus the description thereof is omitted.
  • the component measurement device 100 includes an attachment unit 110, a light source unit 120, a light emission drive unit 130, a detection unit 140, a signal processing unit 150, an operation unit 160, A display unit 170 and a calculation control unit 180 are included.
  • an attachment unit 110 a light source unit 120, a light emission drive unit 130, a detection unit 140, a signal processing unit 150, an operation unit 160, A display unit 170 and a calculation control unit 180 are included.
  • a light source unit 120 includes a light emission drive unit 130, a detection unit 140, a signal processing unit 150, an operation unit 160,
  • a display unit 170 and a calculation control unit 180 are included.
  • each component shown in FIG. 1 is demonstrated in order.
  • the measurement is started by detecting that blood has infiltrated into the test paper 111 and the reflectance of the test paper 111 has changed significantly, and based on the reflectivity after a predetermined time from the start time.
  • To calculate the blood sugar level Since the test paper 111 before blood is attached is a color close to white, the reflectance is large. On the other hand, the test paper 111 after the blood is adhered develops color and the reflectance decreases as the reaction between glucose and the reagent proceeds. For this reason, as the reflectance when calculating the blood sugar level, it is desirable to adopt the reflectance when the reaction rate between the glucose and the reagent approaches the state where the reaction has been completed and the reduction rate of the reflectance is within a predetermined value.
  • the test paper 111 is detachably attached to the attachment unit 110 after being held in an appropriate case.
  • the mounting unit 110 is provided in a housing (not shown) of the component measuring apparatus 100. Thereby, the positional relationship between the test paper 111, the light source unit 120, and the detection unit 140 is determined.
  • the light source unit 120 is a light source that irradiates light onto the test paper 111 as an irradiation means.
  • the light source unit 120 is attached to the housing of the component measuring apparatus 100 so that the light emitting surface thereof faces the direction of the test paper 111. Irradiation light from the light source unit 120 is collected by a lens (not shown) and irradiates the entire test paper 111.
  • the light source unit 120 includes a light emitting diode (LED) that emits light within a wavelength range of light absorbed by the color of the test paper 111, for example, a wavelength of about 500 to 720 nm.
  • LED light emitting diode
  • the light source unit 120 includes a red light emitting diode and a green light emitting diode.
  • the red light-emitting diode emits red light and is used to measure the blood glucose concentration in accordance with the amount of dye produced by the reaction between glucose and the coloring reagent.
  • the green light emitting diode emits green light and is used to measure the hematocrit value based on the amount of hemoglobin in the blood.
  • the red light emitting diode and the green light emitting diode may be arranged close to each other as separate elements, or may be integrally configured as one element.
  • the light emission drive unit 130 is a drive circuit that supplies a drive signal to the light source unit 120. More specifically, the light emission driving unit 130 supplies a pulse signal having a predetermined pulse width, intensity, and cycle to the light source unit 120 based on an instruction from the arithmetic control unit 180. The light source unit 120 repeatedly emits light for the duration of this pulse width in accordance with the supplied pulse signal, and turns off until the next pulse signal rises.
  • the pulse width is generally in the range of 10 to 1000 ⁇ s, preferably about 120 ⁇ s.
  • the period is about 1 ms to 10 ms, preferably about 2 ms for each of red and green. Note that red light and green light are preferably emitted alternately.
  • the pulse width, intensity, and period can be appropriately changed according to the design conditions of other components.
  • the detection unit 140 detects, as detection means, the reflected light that is reflected by a plurality of different regions on the test paper 111 and converts it into an electrical signal.
  • the detection unit 140 is attached to the housing of the component measurement apparatus 100 so that the light receiving surface thereof faces the test paper 111.
  • the detection unit 140 includes a plurality of light detection elements (not shown) that detect reflected light corresponding to a plurality of different regions on the test paper 111, respectively.
  • the light detection elements are sensitive to the wavelength of light absorbed by the color reaction of the test paper 111 and are preferably arranged in a line or matrix on the light receiving surface of the detection unit 140.
  • the arrangement form of the light detection elements is not limited to the form arranged in a line or a matrix, and other arrangement forms may be used.
  • Each light detection element includes at least one pixel which is a minimum unit having a function of detecting light. Therefore, in the light detection element having such a configuration, reflected light from a plurality of different regions on the test paper 111 is detected by at least one pixel of the corresponding light detection element.
  • an image sensor is employed as the plurality of light detection elements.
  • the image sensor is, for example, a CCD sensor or a CMOS sensor in which a plurality of pixels are arranged in a matrix.
  • the irradiation range of the light source unit 120 and the field of view (detection range) of the detection unit 140 do not necessarily need to match.
  • the detection unit 140 may be configured to detect reflected light from a specific area on the test paper 111.
  • the plurality of light detection elements of the detection unit 140 detect reflected light corresponding to a plurality of different regions on the test paper 111, respectively. Therefore, the distance that blood is spread on the test paper 111 in one region is shorter than that of the test paper 111 as a whole, and the apparent development speed in the detection range increases. That is, the blood development time is relatively shortened.
  • the signal processing unit 150 performs signal processing on the electrical signal output from the detection unit 140.
  • the signal processing unit 150 includes a sample and hold circuit, an amplifier circuit, and an A / D converter.
  • the electrical signal output from the detection unit 140 is periodically sampled by a sample and hold circuit, amplified to a predetermined signal level by an amplifier circuit, converted from an analog signal to a digital signal by an A / D converter, and used as image data. It is stored in the memory of the arithmetic control unit 180.
  • the operation unit 160 transmits an instruction from the operator to the calculation control unit 180.
  • the operation unit 160 has, for example, a push button switch, and is attached to the casing of the component measuring apparatus 100.
  • the operator gives instructions to start / stop the component measuring apparatus 100 and display the measurement result via the operation unit 160.
  • the display unit 170 displays the blood sugar level calculated by the calculation control unit 180.
  • the display unit 170 has a liquid crystal display panel, for example, and is attached to the housing of the component measuring apparatus 100.
  • the calculation control unit 180 performs overall control of the component measuring apparatus 100 and calculation of blood glucose level. More specifically, the arithmetic control unit 180 includes peripheral circuits including, for example, a CPU, a memory, a communication circuit, and the like, and includes a light source unit 120, a light emission drive unit 130, a detection unit 140, a signal processing unit 150, and an operation unit 160. And the display unit 170 are electrically connected. The arithmetic control unit 180 executes blood glucose level measurement processing according to a predetermined procedure in response to an instruction from the operator input via the operation unit 160.
  • peripheral circuits including, for example, a CPU, a memory, a communication circuit, and the like, and includes a light source unit 120, a light emission drive unit 130, a detection unit 140, a signal processing unit 150, and an operation unit 160.
  • the display unit 170 are electrically connected.
  • the arithmetic control unit 180 executes blood glucose level measurement processing according to a predetermined procedure in response to an instruction from the operator input
  • the arithmetic control unit 180 uses the image data stored in the memory as the component concentration calculation means to calculate the reflectance of the test paper 111 before and after attaching blood to the test paper 111, and for each of the test papers 111.
  • Time measurement is started by detecting that blood has infiltrated the region. After a predetermined time has elapsed, the glucose concentration is calculated using the correspondence between the reflectance and the glucose concentration.
  • a timer (not shown) is used for measuring the predetermined time.
  • the correspondence between the reflectance and the glucose concentration is stored in advance in a non-volatile memory such as a ROM as a lookup table, or is calculated from a relational expression between the reflectance and the glucose concentration.
  • the calculated glucose concentration is corrected using the hematocrit value and output to the display unit 170 as a blood glucose level.
  • the measurement processing procedure by which the component measuring apparatus 100 measures the glucose concentration is stored in advance as a program in a nonvolatile memory such as a ROM of the arithmetic control unit 180, and the CPU sequentially executes the program.
  • a nonvolatile memory such as a ROM of the arithmetic control unit 180
  • the arithmetic control unit 180 instructs the light emission driving unit 130 to output a predetermined pulse signal
  • the signal processed by the signal processing unit 150 is used as image data in a RAM or the like. Instructs to store in volatile memory.
  • FIG. 2 is a flowchart for explaining the procedure for measuring the glucose concentration by the component measuring apparatus according to the first embodiment of the present invention.
  • 3A is a schematic diagram for illustrating the development of blood spotted on the test paper
  • FIG. 3B is a diagram for explaining the reflectance curve in the region A68 of FIG. 3A.
  • step S101 light irradiation is started on the test paper 111 (step S101). Specifically, the light source unit 120 emits light in pulses, and irradiation of light onto the test paper 111 is started.
  • the light source unit 120 emits pulses in order to reduce the influence of ambient light incident on the component measuring apparatus 100 by using the difference between the signal level during light emission and the signal level during extinction for measurement. is there. In addition, there is an effect of reducing power consumption by causing the light source unit 120 to emit light intermittently.
  • the arithmetic control unit 180 can calculate the distance between the areas based on the size of the test paper 111 and the number of areas separating the test paper 111. Further, the blood development speed on the test paper 111 can be calculated from the distance between the regions and the difference in the coloration speed. Since the deployment speed depends on the hematocrit value, it can be used as information for estimating the hematocrit value.
  • the detection unit 140 When the component measuring apparatus 100 is activated, upon receiving an instruction from the arithmetic control unit 180, the detection unit 140 starts detecting the reflected light reflected by the areas A1 to A100 on the test paper 111 at time t0. At this time, since blood is not spotted on the test paper 111, the reflected light of the test paper 111 whose surface is white is detected.
  • the reflectance of the test paper 111 is 1. In the present embodiment, the reflectance is calculated based on the intensity of the reflected light at the time t0.
  • test paper 111 Thereafter, blood is spotted on the spotting area X on the test paper 111 at time t1.
  • the spotted blood spreads on the test paper 111 and reaches the development area Y at time t2, and reaches the development area Z at time t3.
  • the size of the test paper 111 is about 2 to 6 mm on a side.
  • the time for the blood to reach differs depending on the position on the test paper 111.
  • the blood development speed varies depending on the temperature and viscosity of the blood, the porosity and hole diameter of the test paper 111, the amount of reagent applied, and the like. These causes lead to a measurement error when the reflected light is detected using the test paper as one region.
  • the color reaction is started after blood arrives, and the reaction rate of the color reaction is considered to be constant under the same conditions. Therefore, it is considered that the temporal change in the reflectance of the test paper 111 detected by the detection unit 140 strongly depends on the blood development speed.
  • the color reaction does not occur because the blood has not yet reached from time t0 to t2. Therefore, as shown in FIG. 3B, the reflectance of the test paper 111 is maintained at about 1 until time t2. On the other hand, after the time t2, the color reaction proceeds because blood develops in A68. Accordingly, the reflectance of the region A68 starts to decrease.
  • a curve showing the temporal change in reflectance as shown in FIG. 3B is referred to as a reflectance curve.
  • the arithmetic control unit 180 calculates the reflectance curve in the areas A1 to A100 based on the image data stored in the RAM.
  • the light detection element of the detection unit 140 includes a plurality of pixels, for example, a value obtained by averaging the data of the plurality of pixels can be used as a representative value to calculate the reflectance curve.
  • the time when the color of the reagent starts to change depends on the blood development speed on the test paper 111. Change.
  • the concentration of glucose contained in the blood is calculated (step S103).
  • the glucose concentration contained in the blood is calculated based on the reflectance at the end time t3 after a predetermined time has elapsed from the start time t2 when the color was detected.
  • the arithmetic control unit 180 calculates the blood glucose level based on the measured glucose concentration, the display unit 170 displays the blood glucose level, and the process is terminated.
  • the reflectance detected before the start time t2 (for example, t1) can be used for correcting the baseline.
  • FIG. 4 is a flowchart for explaining step S103 of the flowchart shown in FIG. 2 in more detail
  • FIG. 5 is a diagram for explaining the processing contents in each step of the flowchart of FIG.
  • FIG. 6 is a diagram for explaining that the magnitude of the reflectance varies depending on the region.
  • FIGS. 7A and 7B are diagrams for explaining a method of setting the upper limit value and the lower limit value of the reflectance.
  • the coloration start time is recognized for each region (step S201). Specifically, the color development start time is recognized for the reflectance curves in the regions A1 to A100 (hereinafter referred to as reflectance curves C1 to C100).
  • S1 to S100 indicate the light detection elements of the detection unit 140.
  • the color start times of all areas are aligned (step S202). Specifically, the start time when the coloration of the reflectance curves C1 to C100 is detected is aligned with the reference time.
  • the reference time a predetermined reference time may be set, or the start time of any one of the reflectance curves C1 to C100 may be set.
  • the coloration start times of the reflectance curves C1 to C99 can be aligned with the coloration start time of the reflectance curve C100.
  • coloration in a specific region on the test paper 111 may not be started due to a local abnormality of the test paper 111, a lack of blood volume, or the like.
  • the reflectance curve Cm of the region Am has not started to be colored within the measurement time.
  • the start of coloring may be extremely early or late.
  • the reflectance curve in the region is not used for the subsequent processing. The determination when the start of coloration becomes extremely early or late is made by comparing the start time of coloration with a predetermined first upper limit value and a first lower limit value.
  • the reflectance curve in that area is used for the subsequent processing.
  • the reflectance curve in the region is not used for the subsequent processing.
  • the magnitude of the reflectance after the start of coloring may vary depending on the area on the test paper 111.
  • the reflectance curve Cn ′ is a reflectance curve in the region An ′
  • the reflectance curve Cn ′′ is a reflectance curve in the region An ′′.
  • Factors that cause variations in the magnitude of the reflectance include uneven application of the reagent on the test paper 111, a difference in surface roughness and shape of the test paper 111, and the like.
  • the reflectance increases as in the region An ′, it may be considered that blood has infiltrated only a part of the region An ′.
  • a predetermined second upper limit value and second lower limit value are set for the reflectivity size.
  • the reflectance curve that is set and deviates from the range of the second upper limit value and the second lower limit value is not used for the subsequent processing.
  • the second upper limit value and the second lower limit value are set based on the frequency distribution of the number of pixels with respect to the reflectance at time t3 after the start of coloring.
  • the frequency distribution of the number of pixels with respect to the reflectance usually has a first peak P1 and a second peak P2.
  • the first peak P1 represents the maximum value of the number of pixels in which the reflectance has decreased due to the development of blood on the test paper 111 and the occurrence of coloration.
  • the second peak P2 represents the maximum value of the number of pixels having high reflectivity because blood is not spread on the test paper 111.
  • the reflectance corresponding to a predetermined number of pixels when the number of pixels of the first peak P1 is 100% is set as the second upper limit value and the second lower limit value.
  • the reflectances RU and RL corresponding to 90% of the number of pixels of the first peak P1 are set as the second upper limit value and the second lower limit value, respectively. Can do.
  • the second upper limit value and the second lower limit value are set as described above, only the reflectance curve whose reflectance is within the range between the upper limit value RU and the lower limit value RL is used in the subsequent processing.
  • the second upper limit value (N) is included so that N pixels are included between the reflectances RL ′ and RU ′ around the reflectance corresponding to the first peak P1.
  • RU ′) and the second lower limit (RL ′) may be determined.
  • the reflectance curves of the respective regions are synthesized (step S203).
  • the coloration start time is within the range of the first upper limit value and the first lower limit value
  • the reflectance after the start of coloration is the second upper limit value.
  • the reflectance curves within the range of the second lower limit value are combined at the reference time and synthesized to calculate a synthesized reflectance curve CS. In this way, by combining the results of measuring a plurality of different regions, it becomes difficult to be affected by the amount of reagent applied to the test paper 111 and the variation in the structure of the test paper 111.
  • step S204 the glucose concentration is calculated using the combined reflectance curve CS calculated in step S203.
  • the color change start time of the reflectance curve in a plurality of different regions on the test paper 111 is aligned with the reference time, and then the combined reflectance curve obtained by combining the reflectance curves of the respective regions is used. Based on this, the glucose concentration is calculated.
  • the component measuring apparatus 100 has the following effects.
  • the change in the development speed has an influence on the calculation of the glucose concentration by aligning the start times of coloration in a plurality of different regions on the test paper 111 with the reference time. Can be prevented. Therefore, the glucose concentration can be calculated with high accuracy. Further, even if a development failure occurs in a part of the area on the test paper 111, the measurement can be continued and the measurement value can be calculated.
  • the development speed on the test paper 111 can be calculated from the distance between the areas and the difference in the coloration speed.
  • the glucose concentration can be calculated with high accuracy regardless of the region of the test paper 111 where blood development starts or the blood development range is different.
  • the glucose concentration is based on the combined reflectance curve obtained by synthesizing the reflectance curve of each region.
  • the calculation of the above has been described.
  • calculation of the glucose concentration for each region on the test paper and averaging the glucose concentration in each region to calculate the final glucose concentration will be described. In the following description, the description of the same configuration as in the first embodiment is omitted.
  • FIG. 8 is a flowchart for explaining the procedure for calculating the concentration of glucose contained in blood in the second embodiment of the present invention
  • FIG. 9 is a diagram for explaining the processing contents in each step of the flowchart shown in FIG. is there.
  • the coloration start time is recognized for each region (step S301).
  • the start time of coloration is recognized for the reflectance curves C1 to C100 of a plurality of different areas A1 to A100 on the test paper 111.
  • those having an abnormal reflectance curve are not used for the subsequent processing.
  • the glucose concentration is calculated for each region (step S302). Specifically, in a plurality of different regions on the test paper 111, the glucose concentration contained in the blood is calculated based on the reflectance at the end time after a predetermined time has elapsed from the coloration start time recognized in step S301.
  • step S303 the glucose concentration in each region is averaged. Specifically, the final glucose concentration is calculated by averaging the glucose concentration of each region calculated in step S302.
  • the glucose concentration is calculated in each of a plurality of different regions on the test paper 111, and the final glucose concentration is calculated by averaging the glucose concentration in each region.
  • the glucose concentration in the blood is calculated based on the reflectance at the end time after a predetermined time has elapsed from the coloration start time, so the difference in coloration start time between the regions is the calculation of the glucose concentration. It does not affect.
  • the color start times in each region are substantially aligned.
  • the component measuring apparatus 100 has the following effects.
  • the light source unit 120 emits multicolor light (for example, white light).
  • the light source unit 120 includes, for example, a white light emitting diode.
  • the arithmetic control unit 180 instructs the light emission driving unit 130 to output a predetermined pulse signal.
  • the detection unit 140 separates light of a specific wavelength used for measurement with a bandpass filter. Therefore, the arithmetic control unit 180 does not need to perform timing control for irradiating and detecting light of different wavelengths in a time division manner.
  • FIG. 10 is a diagram for explaining the procedure for calculating the glucose concentration contained in blood in the third embodiment of the present invention together with the processing contents at each step.
  • the detection unit 140 includes light detection elements S1R, S1G to S100R, and S100G that detect reflected light from a plurality of different areas A1 to A100 on the test paper 111.
  • the light detection element S1R includes a red band-pass filter that transmits only red light on the pixel, and detects red light in the region A1.
  • the light detection element S1G includes a green band-pass filter that transmits only green light on the pixel, and detects the green light in the region A1.
  • the light detection elements S1R and S1G are configured so that pixels including a red bandpass filter and pixels including a green bandpass filter are arranged in a grid pattern.
  • the coloration start time is first recognized for each region, and then the glucose concentration and the hematocrit value are calculated for each region. Then, the glucose concentration is corrected with the hematocrit value in each region. Then, the final glucose concentration is calculated by averaging the glucose concentration in each region.
  • the component measuring apparatus 100 of the present embodiment described as described above has the following effects.
  • the glucose concentration was calculated based on the reflectance calculated from the intensity of the reflected light reflected from the test piece.
  • this invention can also be set as the structure which calculates glucose concentration based on the transmitted light which permeate
  • the present invention can be suitably used to calculate a blood glucose level, but it can of course be widely used in the field of measuring the component concentration of a specimen by quantitatively measuring the amount of transmitted light or reflected light. It is.
  • the present invention can also be configured to measure the concentration of specific components in body fluids, such as cholesterol in blood, uric acid, glucose in urine, hemoglobin, and the like.
  • 100 component measuring device 110 wearing part, 111 test paper (test piece), 120 light source part (irradiation means), 130 light emission drive unit, 140 detector (detector), 150 signal processing unit, 160 operation unit, 170 display unit, 180 Calculation control unit (component concentration calculation means).

Abstract

Cette invention concerne un dispositif de mesure d'un composant capable de calculer avec précision la concentration d'un composant spécifique dans un spécimen, même quand la vitesse de révélation du spécimen sur une bandelette réactive change. Le dispositif de mesure d'un composant (100) selon l'invention est un dispositif de mesure d'un composant qui, sur la base du degré de révélation couleur d'un réactif qui réagit avec un composant contenu dans un spécimen, mesure la concentration du composant, et comprend un moyen d'application (120), un moyen de détection (140), et un moyen de calcul de concentration de composant (180). Le moyen d'application (120) applique une lumière sur la bandelette réactive (111) à laquelle le spécimen adhère. Le moyen de détection (140) détecte la lumière réfléchie, réfléchie par chaque région d'une pluralité de régions différentes sur la bandelette réactive (111). Le moyen de calcul de concentration de composant (180) calcule la concentration du composant contenu dans le spécimen sur la base de l'intensité de la lumière réfléchie à une heure de fin marquant l'écoulement d'un temps prédéfini à partir de l'heure de départ à laquelle le spécimen a été infiltré et à laquelle la révélation couleur a commencé dans chaque région de ladite pluralité de régions différentes.
PCT/JP2012/071589 2011-10-18 2012-08-27 Dispositif de mesure d'un composant et procédé associé WO2013061681A1 (fr)

Applications Claiming Priority (2)

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JP2011228956A JP2015004510A (ja) 2011-10-18 2011-10-18 成分測定装置および成分測定方法
JP2011-228956 2011-10-18

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Publication number Priority date Publication date Assignee Title
TWI577982B (zh) * 2015-11-19 2017-04-11 光寶電子（廣州）有限公司 生化檢測裝置及方法
WO2018093573A1 (fr) * 2016-11-18 2018-05-24 Siemens Healthcare Diagnostics Inc. Mesure de longueur d'onde séquentielle multiple d'un dosage liquide

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS61254836A (ja) * 1985-05-07 1986-11-12 Omron Tateisi Electronics Co 生化学測定装置
JPS6426160A (en) * 1987-04-07 1989-01-27 Kyoto Daiichi Kagaku Kk Method and apparatus for analyzing specific multiple components in liquid
JPH0580048A (ja) * 1991-09-20 1993-03-30 Terumo Corp 血液測定方法および測定装置
JP2004144750A (ja) * 2002-10-21 2004-05-20 Lifescan Inc 終点型反応プロフィールの分析時間を短縮するための方法
JP2009109384A (ja) * 2007-10-31 2009-05-21 Arkray Inc 試験片およびイムノクロマトグラフィ装置
WO2010058472A1 (fr) * 2008-11-20 2010-05-27 アークレイ株式会社 Dispositif de mesure optique

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS61254836A (ja) * 1985-05-07 1986-11-12 Omron Tateisi Electronics Co 生化学測定装置
JPS6426160A (en) * 1987-04-07 1989-01-27 Kyoto Daiichi Kagaku Kk Method and apparatus for analyzing specific multiple components in liquid
JPH0580048A (ja) * 1991-09-20 1993-03-30 Terumo Corp 血液測定方法および測定装置
JP2004144750A (ja) * 2002-10-21 2004-05-20 Lifescan Inc 終点型反応プロフィールの分析時間を短縮するための方法
JP2009109384A (ja) * 2007-10-31 2009-05-21 Arkray Inc 試験片およびイムノクロマトグラフィ装置
WO2010058472A1 (fr) * 2008-11-20 2010-05-27 アークレイ株式会社 Dispositif de mesure optique

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JP2015004510A (ja) 2015-01-08

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