JP6691780B2 - Component measuring device, measuring mode setting method and program for this device - Google Patents

Description

  The present invention relates to a component measuring device for measuring a component in a liquid, a measurement mode setting method for the device, and a program.

  BACKGROUND ART A blood glucose meter that measures a component amount (blood glucose level) of a glucose component in blood is known as one form of a component measuring device that measures a component in a liquid. For example, Patent Document 1 discloses a blood glucose meter that captures blood in a sensor case (chip) and obtains a current value according to a glucose component in blood from an internal reagent layer to calculate a blood glucose level.

  Further, the blood glucose meter disclosed in Patent Document 1 is configured as a medical device for ward examination (POCT: Point Of Care Testing) used in a medical facility. In this case, the blood glucose meter is different from a large-scale analyzer that is installed in a test room and the test process after transporting the test sample is carried out in a separate room, and a series of operations from blood collection, test, and measurement value confirmation are performed near the patient. It can be carried out and reflected in treatment, and contributes to quick examinations in emergency departments, OPE rooms, dialysis rooms, etc. in addition to bedside. Therefore, a blood glucose meter for POCT (POCT device) is required to be as accurate as a large-scale analyzer even if it is a simple type, and even if a quality control such as QC (Quality Control) is performed, accurate measurement is always performed. It is important to be managed to calculate the value.

  Furthermore, the POCT device contributes to the work efficiency of medical staff such as doctors and nurses, and is therefore small in size so as to be easily carried. In addition, it is possible to identify medical staff and patients, and to automatically send measurement values by communicating with a server (electronic medical record) in the hospital. It is required to be able to record and refer. In recent years, the use of such a POCT device has led to an increase in medical efficiency and cost reduction, and it is expected that a wide range of measurable conditions and multi-item measurement will be performed. Further, the POCT device is required to perform highly accurate measurement value calculation even in the low blood glucose range, blood condition, and measurement item, which have been often excluded from measurement targets.

JP 2004-555A

  By the way, of the blood glucose meters, in particular, for patients who perform a treatment in which blood glucose is measured by a self-monitoring blood glucose (SMBG) device, and the dose of insulin injection is determined based on this value, the insulin dose A serious health hazard can be expected due to the incorrect calculation of The blood glucose meter is designed and managed based on a management standard that prevents such an accident. Therefore, high-risk designs such as measurement value calculation errors that may occur depending on the use of multiple chip types are often shunned, which has hindered improvements in accuracy and multi-product measurement functions. .. On the other hand, not only the SMBG device but also the POCT device used in the ward, the blood glucose meter is measured by the combination of the measuring device and the chip, so most users buy only the consumable chip. Therefore, the measuring instrument is often used for a long period of time, and it is required to continuously provide a chip that can be used in the existing measuring instrument. Therefore, even if the measurement accuracy can be greatly improved by the improvement, the chip may not be sold even if it can not be used in the current measuring instrument, and if the risk of misuse is high, sales are shunned. There are many things. In recent years, further improvement in the measurement accuracy of blood glucose meters including SMBG and POCT is expected to be linked to the accuracy of blood glucose control of patients and improve the therapeutic effect in the long term, but the characteristics of the market pose an obstacle. As a result, there has been a problem that a blood glucose meter with high measurement accuracy is not used.

  In addition, since the characteristics of the blood glucose meter change depending on the function of the test strip in the chip, if the type of test strip including the production lot is different, the measurement accuracy of the blood glucose level will decrease and the calculation error will increase. Therefore, safety has been prioritized over measurement accuracy in product design. Even if a significant improvement in chip function performance is achieved through improvement development, it is extremely difficult to completely recover the old specification product. Therefore, within the expiration date, there are two types of products, the old specification product and the improved product. Consumables will be used in the market at the same time.

  In addition, as one of the measures to improve the measurement accuracy, it is conceivable that the blood glucose meter has a plurality of measurement modes according to the type of test paper of the chip and the user resets the measurement mode when the chip is used. .. In this way, when it is necessary to switch the function of the measuring instrument according to the type of consumable item, in addition to the inconvenience that the user forgets or mistakes the setting of the measurement mode, or feels the setting operation troublesome, there is a serious problem due to misuse. The risk of accident increases. Moreover, when the mode is automatically switched, a reliable means for avoiding erroneous calculation is required. Further, in the case of the POCT device, a large number of devices for performing a plurality of measurements may be prepared, and in addition to this, the medical facility will own the improved product chip while leaving a large amount of the old specification chip. In addition to managing a plurality of types of chips, complicated switching during use causes confusion, and medical accidents are likely to occur. Therefore, it is desired that the blood glucose meter can surely distinguish and manage different types of chips for easy storage and use.

  The present invention has been made in view of the above circumstances, by specifying the type of the chip and setting the measurement mode according to the type, the measurement accuracy is improved, and the versatility is further increased. An object of the present invention is to provide a measuring device, a measuring mode setting method for this device, and a program. It is also an object of the present invention to enable a safety measure to prevent a serious accident even if misuse occurs due to a mixture of a plurality of types of chips.

In order to achieve the above-mentioned object, the present invention attaches a chip to an apparatus main body in a detachable manner, detects the component amount of a component in a liquid collected in the chip, and calculates measurement information of the component. A component measuring device, wherein the device body specifies a type of the chip in a mounted state of the chip, and based on the type of the specified chip, a measurement mode for setting a measurement mode for measuring the amount of the component. The chip has a setting section, and the chip has a test paper that can take in the liquid, and the apparatus main body projects measurement light onto the test paper and reflects it when detecting the component amount. Receiving light, outputting a detection value based on the reflected light, and having light emitting means for projecting pre-light of a wavelength different from the wavelength of the measurement light, the measurement mode setting unit, Extract the feature quantity of the chip A characteristic amount extraction unit and a specifying unit that specifies the type of the chip based on the characteristic amount extracted by the characteristic amount extraction unit, and the characteristic amount extracted by the characteristic amount extraction unit is the component amount. Before performing the detection, the device body projects the preliminary light on the test paper and receives the reflected light to calculate the calculated preliminary detection value. As the amount of reflected light, the amount of light is calculated from a range of wavelengths different from the wavelength of the measurement light .

  According to the above, the component measuring device includes the measurement mode setting unit that specifies the type of the chip and sets the measurement mode according to the type, so that the component amount of the component in the liquid is not bothered by the user. Can be accurately measured. That is, normally, although the types of chips are different, measuring the component amounts in the same measurement mode causes a decrease in measurement accuracy. On the other hand, since the component measuring device according to the present invention sets the measurement mode according to the type of chip by the measurement mode setting unit, for example, even if the type of test paper in the chip is different, the component amount is measured with high accuracy. In addition, the labor of the user is reduced, and at the same time, a medical accident based on an incorrect measurement value can be prevented. In addition, even if the chip is changed in specifications, the component measuring device can be used properly between the old type and the improved type, and can be used satisfactorily. Becomes

In addition , since the measurement mode setting unit includes the feature amount extraction unit and the identification unit, the component measurement device can significantly improve the distinguishability by the feature amount and identify the chip type. Further, it becomes possible to set the operating condition in the measurement mode in detail by the characteristic amount, and the component amount can be measured with higher accuracy.

Further , the feature amount extracted by the feature amount extraction unit is calculated from the pre-detection value of the pre-light before the detection of the component amount, so that the type of the test paper can be specified well based on the pre-detection value. Is possible.

Further , by emitting the preliminary light of a wavelength different from the wavelength of the measurement light by the light emitting means, and the feature amount extraction unit calculates the light amount of the reflected light, the test paper in the wavelength range that does not depend on the wavelength of the measurement light. The feature quantity can be extracted. Therefore, for example, when providing a chip with a new specification, by using a test paper that can sufficiently reflect the prior light, the component measuring device can easily carry out the measurement mode according to the chip.

  Alternatively, the feature amount extraction unit extracts a change rate of the light amount of the reflected light with respect to a reference light amount as the feature amount, and the specifying unit is configured to specify the type of the chip from the extracted change ratio. May be.

  In this way, the feature amount extraction unit extracts the change rate of the light amount of the reflected light with respect to the reference light amount, so that the distance between the light emitting unit (or the light receiving unit) and the test strip can be estimated, and the change rate can be calculated. It is possible to specify the corresponding chip type.

Further, in order to achieve the above-mentioned object, the measurement mode setting method of this device according to the present invention uses a measurement mode setting unit of the device body in a state in which a chip is detachably attached to the device body of the component measuring device. The step of specifying the type of the chip, and the step of setting the measurement mode when measuring the component amount of the component of the liquid collected in the chip based on the specified type of the chip by the measurement mode setting unit. If, based on the measurement mode set, calculating a measurement information of the component detecting the component amount, only contains the chip are those having a test paper that can capture the liquid, When detecting the component amount, the apparatus main body projects measurement light onto the test paper and receives reflected light thereof, outputs a detection value based on the reflected light, and outputs the measurement light. A light emitting means for projecting pre-light having a wavelength different from the length is provided, and the step of identifying the type of the chip includes a feature amount extracting step of extracting a feature amount of the chip, and a feature amount extracting step. A specific step of identifying the type of the chip based on the extracted characteristic amount, the characteristic amount extracted in the characteristic amount extraction step, the device body before the detection of the component amount, the test It is calculated from the pre-detection value that is output by projecting the preliminary light on paper and receiving the reflected light, and in the feature amount extraction step, as the light amount of the reflected light of the preliminary light, the wavelength of the measurement light is calculated. It is characterized in that the light quantity is calculated from a range of wavelengths different from .

Further, in order to achieve the above-mentioned object, the program according to the present invention, in a component measuring device for measuring the component amount of a component in a liquid, in a state where a chip is detachably attached to the device body of the component measuring device. The step of specifying the type of the chip by the measurement mode setting unit of the apparatus body, and the amount of the component of the liquid collected in the chip based on the specified type of the chip by the measurement mode setting unit A step of setting a measurement mode at the time of measurement, and a step of detecting the component amount and calculating measurement information of the component based on the set measurement mode, a program for executing the chip, The apparatus main body has a test paper capable of taking in the liquid, and the apparatus main body projects measurement light onto the test paper and receives reflected light thereof when detecting the component amount. Then, the detection value based on the reflected light is output, and the light emitting means has a light emitting means for projecting pre-light having a wavelength different from the wavelength of the measurement light. The feature extracting step of extracting a feature amount of a chip, and a specifying step of specifying the type of the chip based on the feature amount extracted in the feature extracting step, wherein the feature extracted in the feature extracting step The amount is calculated from a pre-detection value output by the device body projecting the preliminary light on the test paper and receiving the reflected light before performing the detection of the component amount, and extracting the characteristic amount. In the step, the amount of light of the reflected light of the preliminary light is calculated from a range of wavelengths different from the wavelength of the measurement light .

  According to the present invention, the component measurement device, the measurement mode setting method and program of this device, by specifying the type of chip and setting the measurement mode according to the type, the measurement accuracy is improved, and versatility and The safety can be improved.

It is a perspective view showing the whole blood glucose meter composition concerning a 1st embodiment of the present invention. It is a cross section and a block diagram which show the internal structure of the blood glucose meter of FIG. It is a block diagram which shows the function part which measures a blood glucose level by the control circuit of FIG. It is a graph which shows roughly the light quantity of the reflected light spectrum in the wavelength of the 1st measurement light. FIG. 5A is a schematic explanatory view showing an arrangement state of a predetermined type of test paper, FIG. 5B is a schematic explanatory view showing an arrangement state of a test paper of a type different from the test paper of FIG. 5A, and FIG. FIG. 6 is an explanatory diagram showing a graph of changes in reflected light when the third measurement light is projected. It is a flow chart which shows the processing flow which sets up the measurement mode of the blood glucose meter concerning a 1st embodiment. FIG. 7A is a schematic explanatory view showing a mounted state of a predetermined type of chip in the second embodiment, and FIG. 7B is a schematic explanatory diagram showing a mounted state of a chip of a type different from the chip of FIG. 7A. FIG. 7C is an explanatory diagram showing a graph of the rate of change of reflected light according to the distance when the first or second measurement light is projected. It is a section and a block diagram showing an internal structure of a blood glucose meter concerning a 3rd embodiment. FIG. 9A is a schematic explanatory diagram showing an equivalent circuit of a predetermined type of test paper, and FIG. 9B is a schematic explanatory diagram showing an equivalent circuit of a test paper of a different type from the test paper of FIG. 9A. 10A is a cross-sectional view and a block diagram showing the internal structure of the blood glucose meter according to the fourth embodiment, FIG. 10B is a schematic explanatory view showing an equivalent circuit of a predetermined type of test paper, and FIG. 10C is a view showing FIG. 10B. FIG. 3 is a schematic explanatory diagram showing an equivalent circuit of a test paper of a type different from the test paper of FIG.

  Hereinafter, a component measuring device, a measuring mode setting method and a program of the device according to the present invention will be described in detail with reference to the preferred embodiments (first to fourth embodiments) with reference to the accompanying drawings.

[First Embodiment]
As shown in FIG. 1, the component measuring device 10 according to the first embodiment of the present invention detects a glucose component in blood (liquid) and measures a blood glucose level (component amount of glucose component) based on the detected value. It is configured as a blood glucose meter 10 (hereinafter, also referred to as blood glucose meter 10). The blood glucose meter 10 is mainly configured as a POCT device used by medical staff (users) such as doctors and nurses in a medical facility, and has a function of identifying a medical staff and a patient and an individual patient. It has the function of recording and calling blood glucose level data. Further, the blood glucose meter 10 automatically transfers these recorded data or transfers them by connecting to a server in the hospital, and links the data with the measuring person, the date and time, the treatment action, and the accuracy confirmation record in cooperation with a tool such as an electronic medical record. It may have a management function. The blood glucose meter 10 may be used as an SMBG device that the patient himself / herself measures his / her blood glucose level.

  The blood glucose meter 10 includes a chip 12 that takes in blood, and a device body 14 that detachably mounts the chip 12 to obtain a blood glucose level by optical measurement. The chip 12 is configured as a disposable type that is discarded after each measurement, while the device body 14 is configured as a portable and robust device so that the user can repeat the blood glucose level measurement. .. In addition, a holder such as a strap may be detachably attached to prevent damage due to drop prevention.

  As shown in FIGS. 1 and 2, the tip 12 includes a cylindrical mounting portion 16 that is inserted and fixed in the apparatus body 14, and a nozzle 18 that projects from the mounting portion 16 to the tip. At the center of the nozzle 18, a blood introducing passage 18a is provided which extends linearly from the tip end toward the inside of the mounting portion 16, and the test paper 20 is stored in the mounting portion 16. The chip body 19 including the mounting portion 16 and the nozzle 18 is made of a rigid material having a predetermined rigidity. As such a rigid material, for example, a highly hydrophilic material such as an acrylic resin or various resin materials that have been hydrophilized are preferable, and it is more preferable that a treatment that does not allow ambient light to pass through is performed.

  The test paper 20 is obtained by supporting (impregnating) a reagent (coloring reagent) on a carrier capable of absorbing blood (specimen). This carrier is preferably composed of a porous membrane (sheet-shaped porous substrate). In this case, the porous membrane preferably has a pore size such that red blood cells in blood can be filtered. Examples of the carrier for the test paper 20 include, in addition to the porous film, a sheet-shaped porous substrate such as a nonwoven fabric, a woven fabric, and a stretched sheet.

  Examples of the constituent material of the carrier such as the porous membrane include polyesters, polyamides, polyolefins, polysulfones, and celluloses, etc., but they are impregnated with an aqueous solution in which a reagent is dissolved, or blood is absorbed during blood collection. A material having hydrophilicity or a material that has been subjected to a hydrophilic treatment is preferable for rapid development.

  As a reagent for impregnating a carrier (porous membrane), in the case of measuring a blood glucose level, for example, an enzyme reagent such as glucose oxidase (GOD) or peroxidase (POD) and, for example, 4-aminoantipyrine or N-ethyl N- ( Examples thereof include a coloring reagent such as 2-hydroxy-3-sulfopropyl) -m-toluidine, and other substances are appropriately selected according to the measurement components.

  The chip 12 is stored in a state that it is sealed in a dedicated container in order to reduce the change with time of the reagent carried inside the test paper 20.

  When the blood glucose level is measured by the blood glucose meter 10, the user mounts the chip 12 on the device body 14 and then spots the patient's blood on the tip of the nozzle 18. The spotted blood is guided to the test paper 20 via the blood introducing path 18a based on the capillary phenomenon, develops inside the test paper 20, and then reacts with the reagent carried in the test paper 20 to cause coloration. To do. In the color reaction, since the color density changes according to the amount of glucose contained in blood, the change amount of the color density is detected and calculated as a blood glucose level. At this time, a correction calculation is added to the factors that may cause a calculation error, and a correction step is provided so that the calculated value is close to the plasma glucose concentration value. The factors to be corrected include blood concentration (hematocrit value), measurement temperature, test strip lot, and medication taken by the patient.

  The blood glucose meter 10 can measure the blood glucose level by mounting a plurality of types of chips 12 on the device body 14. As the type of the tip 12, for example, when the specifications are changed, when the test strip 20 is different due to a difference in manufacturing raw material or configuration, the shape (for example, axial length) of the tip 12, the test strip structure, and the type of reagent are different. Cases can be given.

  As shown in FIG. 1, the apparatus main body 14 has a housing 22 that forms the outer appearance. The housing 22 is slightly elongated so that the user can easily hold it with one hand, and the tip portion thereof is tapered toward the tip end and slightly bent downward to form a shape that facilitates the spotting operation of blood. ing. A mounted portion 24 to which the chip 12 is mounted and an ejector 26 that removes the chip 12 mounted on the mounted portion 24 are provided on the front end side of the housing 22. A monitor 28 and operation button group 30 are provided on the upper surface of the housing 22, and a bar code reader 32 is provided on the base end surface of the housing 22. The housing 22 may have water resistance when water or a chemical is submerged for cleaning when blood adheres to the housing 22, and may have a structure that is easy to wipe, such as surface processing or eliminating a gap as much as possible.

  The attached portion 24 is formed at the tip of the blood glucose meter 10 and has a cylindrical shape to which the above-described tip 12 can be attached. A cap 24a, which protects the tip portion when carried, and which can be detached at the time of measurement, may be attached to the attached portion 24 together with the fall prevention holder 24b. Inside the mounted portion 24, mounting means for mounting a plurality of types of chips 12 is provided. The mounting means is not particularly limited, but, for example, the chip body 19 is formed of a material that is not easily broken by external pressure, and when the chip body 19 is pressed toward the mounted portion 24, the outer peripheral portion is pushed into the gap with the housing 22. When the chip 12 is pressed toward the mounted part 24, the mounted part 24 is tapered and the diameter of the mounted part 24 is gradually increased from the tip end so that the chip 12 is slidable. Another example is a method in which the mounted portion 24 is naturally enlarged and mounted so that the mounted portion 24 is designed to be closely held. In the blood glucose meter 10 according to the present embodiment, the distal end portion of a block body 42, which will be described later, protruding in the mounted portion 24 is configured by an elastic member 43 having a predetermined thickness. Thereby, even if the tip 12 has a different axial length or a slightly different shape of the mounting portion 16 depending on the type, the elastic member 43 is attached to the mounting portion 16 by inserting the mounting portion 16 into the mounted portion 24. It becomes possible to elastically deform and adhere.

  The ejector 26 is connected to the eject pin 26a in the housing 22, and pushes the tip 12 mounted on the mounted portion 24 forward and separates it in response to a forward pressing operation by the user. As a result, the user can easily remove the chip 12 mounted so as to be in close contact, and further, after the blood glucose level is measured, the chip 12 can be discarded without touching the chip 12 to which blood has adhered. Therefore, the work efficiency of the user can be improved, and at the same time, the risk of infection due to contaminated blood generated in the hospital can be reduced.

  The monitor 28 provided in the device body 14 is composed of a liquid crystal, an organic EL, or the like, and displays information provided to the user in measuring the blood glucose level, such as the blood glucose level, date and time, or other information (for example, error or measurement procedure). indicate.

  As shown in FIG. 1, the operation button group 30 includes a power button 30a, a move button 30b, a selection button 30c, an LED display unit 30d, and a data read button 30e. The move button 30b has a function of moving the selection frame with respect to the item displayed on the monitor 28 or scrolling the screen in accordance with the operation. The selection button 30c has a function of selecting the function of the item in which the selection frame is located on the monitor 28, or canceling the selection and returning to the screen before the selection, according to the pressing operation of the user. The LED display unit 30d lights up or blinks in various colors by LEDs to notify the state of the blood glucose meter 10. The data read button 30e is provided between the monitor 28 and the mounted portion 24, and operates to read the barcode reader 32. It should be noted that the power-on is not limited to the pressing of the power button 30a, and it may be set to change to the power-on state by detecting the mounting of the chip 12, the removal of the cap 24a, etc. It is not limited to the pressing of, and includes a state change due to interruption of signal communication or removal of the chip 12.

  The barcode reader 32 has a function of reading a barcode (not shown) by laser scanning. The barcode to be read is attached or affixed to a patient, a medical staff, or the like in advance, for example. The blood glucose meter 10 obtains the patient identification data and the measurer identification data by reading the respective bar codes, and associates them with the blood glucose measurement value data, the treatment action, and other measurement values, and a predetermined database (not shown). ).

  Further, as shown in FIG. 2, the device body 14 includes a detection unit 34, an A / D converter 36, and a control circuit 40 inside the housing 22. The detection unit 34 is a structural unit that optically detects blood collected in the chip 12. The detection unit 34 includes a block body 42, a lens 44, a substrate 46, a light emitting unit 48, and a light receiving unit 50.

  The block body 42 of the detection unit 34 is fixed inside the tip end side of the housing 22, holds the lens 44 on the tip end side, and holds the substrate 46 on the base end side. The light emitting unit 48 and the light receiving unit 50 mounted on the substrate 46 are inserted and arranged inside the base end side of the block body 42. In addition, in the block body 42, a measurement light optical path 42a that guides the measurement light projected by the light emitting unit 48 to the lens 44, a space 42b from the lens 44 to the test paper 20, and a reflection reflected from the test paper 20. An optical path 42c for reflected light that guides light from the lens 44 to the light receiving unit 50 is provided.

  The light emitting unit 48 is a light source that irradiates the test paper 20 with light as an irradiation unit. The light emitting surface is adjusted so as to face the test paper 20, and the light emitting surface is attached to the housing 22. The lens 44 collects and irradiates the light. The wavelength range used for the measurement is selected according to the wavelength characteristics of the measurement reagent, and is set in a range that is not affected by the wavelength range of the inhibiting factor. Therefore, the wavelength range is set to, for example, about 500 to 720 nm. In the present embodiment, since light having different wavelengths are emitted, the light emitting element is configured by three light emitting elements (first light emitting element 48a, second light emitting element 48b, third light emitting element 48c). The first light emitting element 48a emits the first measurement light L1 at a wavelength (for example, 620 to 640 nm) that detects the color density of the reagent according to the amount of glucose component. The second light emitting element 48b emits the second measurement light L2 at a wavelength (for example, 510 to 540 nm) that detects the concentration of red blood cells in blood. The third light emitting element 48c is an element for discriminating the type of the test paper 20 in the chip 12, and has a wavelength deviated from the detection wavelength range of the first and second measurement lights L1 and L2 (for example, 400 to 500 nm or The third measurement light L3 is emitted at 800 to 900 nm). As the first to third light emitting elements 48a, 48b, 48c, for example, an LED element, an organic EL element, an inorganic EL element, an LD element or the like can be used.

  The light receiving unit 50 is configured by one or a plurality of light receiving elements 50a that receive the reflected light reflected by the test paper 20 and output a current (corresponding to the reflected light intensity) related to the reflected light. As the light receiving element 50a, for example, a PD element, a CCD element, a CMOS element or the like can be used.

  The A / D converter 36 is electrically connected to the substrate 46 of the detection unit 34 and appropriately amplifies the current signal (analog signal) output from the light receiving unit 50 and converts it into a voltage signal (digital signal). , And output as detected value d (current information).

  The control circuit 40 is configured as a computer (control unit) having an input / output I / F 52, a processor 54, a memory 56, and the like, and has a function of controlling the operation of the blood glucose meter 10 as a whole. For example, the control circuit 40 controls the drive of the detection unit 34, receives the detection value d detected by the detection unit 34 and converted by the A / D converter 36, and measures the blood glucose level. Further, the control circuit 40 stores the measured blood glucose level in the database in association with the patient identification data and causes the monitor 28 to display the blood glucose level.

  The control circuit 40 constructs the measurement processing unit 58 for measuring the blood glucose level as shown in FIG. 3 by the processor 54 reading and executing the component measurement program 56a stored in the memory 56. The measurement processing unit 58 is configured to include a detection unit driving unit 60, a detection value acquisition unit 62, a blood glucose level calculation unit 64, and a measurement mode setting unit 66.

  The detection section drive section 60 is activated by a signal from the control circuit 40 and emits pulsed light at predetermined time intervals. The period of this pulsed light is about 0.5 to 3.0 msec, and the irradiation time of one pulse is about 0.05 to 0.3 msec. In the present embodiment, three different wavelengths are used to measure the glucose concentration, the hematocrit value for correction, and the type of the chip 12 are discriminated. Therefore, three different wavelengths are switched in order after the power is turned on. Start continuous irradiation.

  The detection value acquisition unit 62 receives the detection value d transmitted from the detection unit 34 via the A / D converter 36, and temporarily stores it in the memory 56. The detection value acquisition unit 62 is activated immediately after the power is turned on or the measurement mode is switched, and automatically records the amount of reflected light from the surface of the test paper 20 for each irradiation wavelength. The recording time is determined in consideration of the amount of data that can be stored in the memory 56, but it is desirable that the recording time be performed a plurality of times per second. In addition, the number of times may be changed according to the amount of change in the amount of reflected light measured, and as the amount of change increases, the number of measurement points per unit time can be increased to ensure calculation accuracy and save the number of memories used. it can.

  The blood glucose level calculating unit 64 is a functional unit that calculates the blood glucose level based on the detection value d (current value) acquired by the detection value acquiring unit 62 and displays it on the monitor 28. The blood glucose level calculator 64 first calculates the absorbance from the detected value d, then calculates the provisional blood glucose level from the absorbance, and further performs hematocrit correction on the provisional blood glucose level to obtain the blood glucose level as the measurement result. ing. Further, the blood glucose level calculating unit 64 generates the blood glucose level which is the calculated measurement information in the display information and transmits the display information to the monitor 28 to display the blood glucose level of the patient in an appropriate display form. Further, the blood glucose level calculating unit 64 stores the blood glucose level in the memory 56 in association with the patient identification data and the measurer identification data. Thereby, the blood glucose meter 10 can read and display the past blood glucose level for each patient. Alternatively, the blood glucose meter 10 transmits these data automatically (or in response to a user's operation) to a server having an electronic medical record in the hospital.

  On the other hand, the measurement mode setting unit 66 has a function of setting the measurement mode when measuring the blood glucose level according to the type of the chip 12. As described above, the blood glucose meter 10 can be equipped with a plurality of types of chips 12, and in this case, in order to measure the same blood glucose level even if the types of the chips 12 are different, it is possible to change the type depending on the type of the chips 12. Therefore, it becomes necessary to change the measurement mode. For example, in the measurement mode, the light amount of the measurement light emitted from the light emitting unit 48, the amplification amount of the current (detection value d) that the light receiving unit 50 receives and outputs the reflected light, and the detection value of the blood glucose level calculating unit 64. It is possible to adjust the correction amount or the like for d and the calculated value. Each of the above amounts in the measurement mode may be adjusted alone or in combination.

  The measurement mode setting unit 66 performs a measurement mode setting method that is a process of setting the measurement mode after the chip 12 is attached to the device body 14 and before the blood glucose level is measured. At this time, the measurement mode setting unit 66 drives the detection unit driving unit 60 to irradiate the test paper 20 before collecting blood (blank) with the third measurement light L3 as the preliminary light. Then, the measurement mode setting unit 66 sets a detection value based on the reflected light of the third measurement light L3 reflected by the test paper 20 (hereinafter referred to as a pre-detection value pd to distinguish it from the detection value d at the time of measuring the blood glucose level). , From the light receiving unit 50 via the A / D converter 36 and the detection value acquisition unit 62. The irradiation of the third measurement light L3 for calculating the characteristic amount may be performed simultaneously with the blank measurement of the first and second measurement lights L1 and L2 for blood glucose measurement, or at intervals of several seconds or less.

  In addition, the measurement mode setting unit 66 internally includes a feature amount calculation unit 68, a specification unit 70, and a mode selection unit 72 as a functional unit that sets the measurement mode.

  The characteristic amount calculation unit 68 calculates the characteristic amount of the test paper 20 contained in the chip 12 based on the pre-detection value pd acquired by the detection value acquisition unit 62. The characteristic amount of the test paper 20 is not particularly limited, and in the first embodiment, the light amount when the third measurement light L3 having a predetermined wavelength is reflected is used.

  The identifying unit 70 determines the type of the test paper 20 based on the feature amount calculated by the feature amount calculating unit 68. For example, the identifying unit 70 has one or more discrimination thresholds corresponding to the plurality of types of chips 12, and identifies the type of the test paper 20 by comparing the received feature amount with the discrimination threshold.

  Hereinafter, the principle of calculating the characteristic amount of the test strip 20 according to the first embodiment and the method of determining the type of the test strip 20 based on the characteristic amount will be described more specifically with reference to FIGS. 4 to 5C. To go.

  When measuring the blood glucose level, the test paper 20 (chip 12) reflects the reflected light having the reflected light spectrum as shown in FIG. 4 by being irradiated with the first measurement light L1 from the first light emitting element 48a. The waveform shown by the solid line in FIG. 4 is the reflected light reflected by the blank test paper 20. On the other hand, the waveform indicated by the alternate long and short dash line in FIG. 4 is a reflection that is reflected by the test paper 20 that is colored by a glucose component having a certain component amount (for example, a blood glucose level of 100 [mg / dL]) when blood is collected. Light.

  That is, since the test paper 20 is projected with the first measurement light L1 having a wavelength of 620 to 640 nm, the test paper 20 reflects reflected light having a peak at 620 to 640 nm at the time of blanking and measuring the blood glucose level. It can be said that the blood glucose meter 10 is configured to calculate the blood glucose level based on the reduction rate (absorbance) of the light quantity of the reflected light around the peak that shows a large change in the reflected light. The hematocrit value in blood is calculated by projecting the second measurement light L2 of 510 to 540 nm onto the test paper 20 and detecting the reflected light.

  From this, the reflected light of the test paper 20 at the time of reflecting the first or second measurement light L1, L2 compares the blank time and the blood glucose level measurement at wavelengths of 500 nm or less and 800 nm or more. Is almost unchanged. That is, when the wavelength of the reflected light is in the range of 400 to 500 nm or 800 to 900 nm, almost the same amount of light is detected. Therefore, the blood glucose meter 10 according to the first embodiment determines the type of the test paper 20 by using the range of 400 to 500 nm or 800 to 900 nm, which is the wavelength of the reflected light that does not significantly contribute to the measurement of the blood glucose level. Has become.

  Specifically, as shown in FIG. 5A, the third measurement light L3 having a predetermined wavelength (for example, having a peak at 450 nm) is projected from the third light emitting element 48c onto the blank test paper 20 and the reflected light thereof is reflected. To detect. As shown in FIG. 5C, this reflected light has a mountain-shaped waveform having a peak at 450 nm, and when the type of chip 12 (test paper 20) is different, it is detected with different peak values (light amount). .. For example, the material of the test paper 20 itself, the coloring, the reflected light amount adjustment by the surface processing structure, the kind of the reagent contained in the test paper 20 and the composition ratio of the reagent, the layered application of the reagent in the thickness direction of the test paper 20, the test The amount of reflected light varies due to surface processing by pressure operation after attaching the test paper 20 to the chip body 19, such as uneven application of a reagent on the surface of the paper 20, or changes over time in the test paper 20.

As an example, the test paper 20 _X1 of the chip 12 _X1 shown in FIG. 5A, the test paper 20 _Y1 chips 12 _Y1 shown in FIG. 5B, the third measuring beam L3 having the same amount of light from the third light emitting element 48c is projected However, the reflected light is reflected at different peaks as shown in FIG. 5C. In FIG. 5C, the waveform indicated by the solid line is the reflected light of the test paper 20 _X1 , and the waveform indicated by the chain double-dashed line is the reflected light of the test paper 20 _Y1 .

Therefore, when the detection value acquisition unit 62 acquires the pre-detection value pd based on the reflected light of the third measurement light L3, the feature amount calculation unit 68 of the measurement mode setting unit 66 performs an operation such as integration on the pre-detection value pd. By performing the calculation, the amount of reflected light (absorbance) is calculated. As a result, when the test paper 20 _X1 is attached to the apparatus body 14, the light amount shown by the solid line in FIG. 5C is calculated, and when the test paper 20 _Y1 is attached, it is indicated by the chain double-dashed line in FIG. 5C. The amount of light shown is calculated.

The specifying unit 70 determines the type of the test paper 20 (test paper 20 _X1 , test paper 20 _Y1 ), in other words, the type of the chip 12 (chip 12 _X1 , chip 12 _Y1 ), based on the light quantity calculated by the feature quantity calculating unit 68. Specify. The specifying unit 70 has a discrimination threshold value corresponding to the light amount calculated by the feature amount calculation unit 68. When the discrimination threshold value is larger than the discrimination threshold value, the test paper 20 _X1 is specified. Identify the paper 20 _Y1 .

Returning to FIG. 3, the mode selection unit 72 sets the measurement mode based on the type of the test strip 20 identified by the identifying unit 70 (test strip 20 _X1 , test strip 20 _Y1 ). For example, in the memory 56, the measurement mode data MD corresponding to the type of the test paper 20 is stored in advance. When the test strip 20 _X1 is specified, the mode selection unit 72 selects the measurement mode data MD1 from the memory 56 and sets the measurement mode. On the other hand, when the test paper 20 _Y1 is specified, the measurement mode data MD2 is selected from the memory 56 to set the measurement mode. The measurement mode setting unit 66 previously holds the reference measurement mode data MD, and corrects the control amount of the reference measurement mode according to the discriminated amount of the test paper 20 to obtain the test paper. You may set the measurement mode according to 20 types.

  Then, the measurement processing unit 58 sets the measurement mode data MD read by the mode selection unit 72, so that the operation corresponding to the measurement mode data MD is detected by the detection unit 34 and the A / D conversion at the time of measuring the blood glucose level thereafter. The device 36, the control circuit 40, or the like is made to perform the operation.

The blood glucose meter 10 according to the first embodiment is basically configured as described above. Hereinafter, a measurement mode setting method (processing flow) performed by the blood glucose meter 10 and its action and effect will be described. .. It should be noted that in the following, a case will be described in which, when measuring a blood glucose level, the user _{attaches one} of the different types of chips 12 _X1 and 12 _Y1 (collectively referred to as the chip 12) to the apparatus main body 14.

  The control circuit 40 of the device body 14 starts driving based on the ON operation of the power button by the user, constructs the functional unit shown in FIG. 3, and detects whether the chip 12 is attached to the attached portion 24. Yes (step S1). The mounting of the chip 12 is detected by the user's operation of the selection button 30c, the detection value of the light receiving unit 50 (for example, whether the detection value is equal to or less than a predetermined value due to the mounting of the chip 12 and shading). To be done.

  At the same time when the power is turned on or after the mounting of the chip 12 is detected (step S1: YES), the detection unit driving unit 60 of the measurement processing unit 58 projects the third measurement light L3 as the preliminary light from the third light emitting element 48c. (Step S2). The detection unit 34 receives the reflected light by the light receiving unit 50 in response to the projection of the third measurement light L3 onto the test paper 20 in the chip 12, and outputs the pre-detection value pd.

  The detection value acquisition unit 62 acquires the pre-detection value pd from the light receiving unit 50 via the A / D converter 36 (step S3), and temporarily stores the pre-detection value pd in the memory 56, and at the same time, the measurement mode setting unit 66. The feature amount calculation unit 68 of the measurement mode setting unit 66 calculates the light amount of the reflected light of the third measurement light L3 based on the provided pre-detection value pd (step S4). The light amount calculated by the characteristic amount calculation unit 68 is provided to the identification unit 70.

Next, the identifying unit 70 compares the provided light amount with the determination threshold value (step S5). Then, when the light amount is larger than the determination threshold value (step S5: YES), it is identified that the test paper 20 of the chip 12 mounted on the apparatus body 14 is the test paper 20 _X1 , and the process proceeds to step S6. On the other hand, when the light amount is smaller than the determination threshold value (step S5: NO), it is identified that the test paper 20 of the chip 12 mounted on the apparatus body 14 is the test paper 20 _Y1 , and the process proceeds to step S7.

The mode selection unit 72 selects the measurement mode data MD1 from the memory 56 in step S6 based on the identification of the test strip 20 _X1 . Accordingly, the measurement mode setting unit 66 sets the measurement mode data MD1 as the blood glucose level measurement mode. On the other hand, in step S7, the mode selection unit 72 selects the measurement mode data MD2 from the memory 56 based on the identification of the test paper 20 _Y1 . As a result, the measurement mode setting unit 66 sets the measurement mode data MD2 as the blood glucose level measurement mode.

  Then, after the measurement mode setting unit 66 sets the measurement mode, the measurement processing unit 58 ends the measurement mode setting method and starts measuring the blood glucose level. In the measurement of the blood glucose level, for example, the detection unit driving unit 60 sets the first and second measurement light beams L1 of the first and second light emitting elements 48a and 48b so that the light amount is in the measurement mode set by the measurement mode setting unit 66. , L2 are controlled. Then, the light receiving unit 50 detects the reflected light that the test paper 20 has reflected the first and second measurement lights L1 and L2, and the detection value d is appropriately corrected according to the measurement mode set by the measurement mode setting unit 66. The blood glucose level is calculated by the calculation process. On the other hand, since the amount of reflected light decreases due to the mounting failure of the chip 12, there is a risk that the mounting failure of the chip 12 in the setting mode in which the received light amount is large is erroneously recognized as a mode in which measurement can be performed in the setting in which the received light amount is small. Be done. As a countermeasure against this, by setting the judgment based on the amount of reflected light at the wavelengths of the first and second light emitting elements 48a and 48b for detection together with the judgment by the third light emitting element 48c for judging the chip 12, It is possible to prevent measurement failure due to erroneous recognition of modes.

  As described above, the blood glucose meter 10 (component measurement program 56a) and the measurement mode setting method according to the first embodiment specify the type of the chip 12 (test paper 20) and set the measurement mode according to the type. Therefore, the blood glucose level can be measured accurately. That is, normally, although the types of the chips 12 are different, the component amounts are measured in the same measurement mode, which leads to a decrease in measurement accuracy. On the other hand, the blood glucose meter 10 measures the blood glucose level by specifying the type of the chip 12 even if the type of the chip 12 is different, so the measurement accuracy is improved. Moreover, since the user can reduce the time and effort of setting, quick measurement can be performed as a result, and the troublesomeness is reduced. Further, in the blood glucose meter 10, even if similar products are mixed in the market after the specifications of the test paper 20 and the chip 12 are changed, accidents due to confusion between the old specifications and the improved products can be prevented. Therefore, the old equipment can be used continuously as long as the consumables can be used, and the equipment is versatile and convenient for the user.

  In this case, the measurement mode setting unit 66 of the blood glucose meter 10 includes the feature amount calculation unit 68 (feature amount extraction unit) and the identification unit 70, and thus the extracted light amount (feature amount) of the third measurement light L3 is reflected. Thereby, the type of the test paper 20 can be specified by greatly improving the distinguishability. Further, since the characteristic amount extracted by the characteristic amount calculation unit 68 is the light amount calculated from the pre-detection value pd of the third measurement light L3 before the blood glucose level is detected, the test paper 20 corresponding to this light amount is detected. It is possible to specify the type well. In addition to this, since the third measurement light L3 is projected from the third light emitting element 48c and the feature quantity calculation unit 68 calculates the quantity of the reflected light, the wavelengths of the first and second measurement lights L1 and L2 are set. The characteristic amount of the test paper 20 can be extracted in the wavelength range that does not depend on it. Therefore, for example, when providing the chip 12 with a new specification, by adopting the test paper 20 that can sufficiently reflect the third measurement light L3, the blood glucose meter 10 can change the measurement mode according to the test paper 20. It can be implemented easily.

In addition, in the said 1st Embodiment, although the case where two types of test strips 20 _X1 and 20 _Y1 were specified was demonstrated, it is needless to say that the blood glucose meter 10 can specify three or more types of test strips 20. For example, by dividing the light quantity of the reflected light of the third measurement light L3 calculated from the pre-detection value pd into three or more stages, it is possible to specify three or more types of test papers 20. The wavelength of the third measurement light L3 projected by the third light emitting element 48c is not limited to the above, and may have a peak in the range of 800 to 900 nm, 400 nm or less, or 900 nm or more, for example. Further, in the above-described embodiment, the case where the characteristic amount irradiation site by the third light emitting element 48c is in substantially the same range as the reagent reaction site used for blood glucose measurement has been described, but the irradiation site may be shifted for the characteristic amount determination. Good. In this case, a local change such as changing the color of the test paper or changing the structure can be given only to the irradiation portion for the feature amount discrimination, and the test paper 20 can be more reliably specified.

  Further, the blood glucose meter 10 controls the measurement mode based on the light quantity (feature quantity) of the reflected light of the third measurement light L3 (light quantity emitted by the light emitting section 48, amplification quantity of detection value, or blood sugar level calculating section). The correction amount of the calculated value in 64) may be adjusted in detail. Thereby, the blood glucose level can be measured with higher accuracy.

  It should be noted that the blood glucose meter 10 (component measuring device 10) according to the present invention is not limited to the above embodiment, and some embodiments will be described below. In the following description, the same configurations or configurations having the same functions as those of the first embodiment are designated by the same reference numerals, and detailed description thereof will be omitted.

[Second Embodiment]
The blood glucose meter 10A according to the second embodiment sets the measurement mode by specifying that the distance between the light emitting unit 48 (or the light receiving unit 50) and the test paper 20 is different as the type of the chip 12, and It is different from the blood glucose meter 10 according to one embodiment. The structure other than the measurement processing unit 58A of the blood glucose meter 10A may basically have the same configuration as the blood glucose meter 10 (see FIGS. 2 and 3), but the third light emitting element 48c of the light emitting unit 48 is provided. You don't have to.

For example, in the blood glucose meter 10A, the length of the tip 12 in the axial direction changes as shown in FIGS. 7A and 7B due to a change in specifications and the like, so that the light emitting section 48 and the test paper 20 are attached to the device body 14 when mounted. The distance between may differ. FIG. 7A shows the chip 12 _{X2 in} which the distance A between the light emitting unit 48 and the test paper 20 _X2 is a reference, and FIG. 7B shows the chip 12 in which the distance B between the light emitting unit 48 and the test paper 20 _Y2 is longer than the distance A. _It shows _Y2 .

  Thus, when the distances A and B between the light emitting unit 48 and the test paper 20 are different, the light amount of the reflected light reflected from the test paper 20 varies as shown in FIG. 7C. In FIG. 7C, the change rate of the light amount shown by the solid line is the case where the first measurement light L1 is reflected, and the change rate of the light amount shown by the alternate long and short dash line is the case where the second measurement light L2 is reflected. .. As shown in the figure, since the first measurement light L1 has a larger change rate according to the distance, the case where the first measurement light L1 is projected as the preliminary light will be described below.

Specifically, in the case of the chip 12 _{X2 with} the distance A shown in FIG. 7A, the light amount close to the reference light amount defined in advance is reflected. On the other hand, the blood glucose meter 10A reduces the light amount with respect to the reference light amount as the test paper 20 becomes farther from the reference. For example, the distance between the test paper 20 and the light emitting unit 48 is 0. The light amount decreases at a rate of change of about 10% even if the distance is only 0.3 mm. In the case of the chip 12 _{Y2 at} the distance B shown in FIG. 7B, the reflected light is reflected with a light amount reduced by 10 to 20% with respect to the reference light amount.

  Therefore, the measurement processing unit 58A of the blood glucose meter 10A causes the first light emitting element 48a to project a predetermined amount of the first measurement light L1 onto the test paper 20 and reflects the first measurement light L1 reflected by the test paper 20. Light is received by the light receiving unit 50 to obtain the pre-detection value pd. Also, the measurement processing unit 58A constructs a measurement mode setting unit 66A including a feature amount calculation unit 68A, a specification unit 70A, and a mode selection unit 72, as shown in FIG.

  The characteristic amount calculation unit 68A has reference light amount data for use in the measurement mode setting method. Then, the characteristic amount calculation unit 68A calculates the light amount of the reflected light from the pre-detection value pd acquired by the detection value acquisition unit 62, and further calculates the change rate C of the light amount of the reflected light of the pre-light with respect to the reference light amount, The rate of change C is output to the identifying unit 70A as the characteristic amount of the chip 12 (test paper 20).

The specifying unit 70A has a map (for example, a graph as shown in FIG. 7C) for specifying the plurality of types of chips 12 according to the change rate C in advance. Then, when the change rate C calculated by the feature amount calculation unit 68A is received, the type of the chip 12 is specified by referring to the map. For example, as shown in FIG. 7C, when the change rate C is in the range of 0 to −10%, the chip 12 _X2 (test paper 20 _X2 ) shown in FIG. 7A is specified. Further, for example, as shown in FIG. 7C, when the change rate C is in the range of −10 to −20%, the chip 12 _Y2 (test paper 20Y ₂ ) shown in FIG. 7B is specified.

  The mode selection unit 72 selects the measurement mode data MD corresponding to the type of the chip 12 from the plurality of measurement mode data MD stored in the memory 56 based on the type of the chip 12 identified by the identification unit 70A. .. Then, the measurement mode setting unit 66A sets the measurement mode data MD selected by the mode selection unit 72 and causes the blood glucose level to be measured according to the measurement mode.

  As described above, also in the blood glucose meter 10A according to the second embodiment, similar to the blood glucose meter 10, the blood glucose level measurement mode can be set according to different types of chips 12 (test paper 20). Therefore, it becomes possible to measure the blood glucose level with high accuracy. Further, the blood glucose meter 10A estimates the distance between the light emitting unit 48 (or the light receiving unit 50) and the test strip 20 by the feature amount calculating unit 68A extracting the change rate C of the light amount of the reflected light with respect to the reference light amount. It is possible to easily specify the chips 12 having different positions of the test paper 20.

  The blood glucose meter 10A projects the second measurement light L2 as the preliminary light, obtains the preliminary detection value pd from the reflected light, extracts the change rate C of the light amount of the reflected light, and identifies the type of the chip 12. It may be configured. In this case, the blood glucose meter 10A alternately projects the first measurement light L1 and the second measurement light L2, and identifies the type of the chip 12 based on the respective pre-detection values pd to identify the type of the chip 12. The accuracy can be further improved. In addition, the light emitting section 48 includes a light emitting element different from the first and second light emitting elements 48a and 48b, extracts the change rate C of the reflected light projected by the light emitting element, and specifies the type of the chip 12. But it's okay. At this time, a means for improving the recognition performance can be added by installing a recognition probe such as an electrode in the chip body 19 in order to distinguish the mounting failure of the chip 12.

  Further, the blood glucose meter 10, 10A projects the first or second measurement light L1, L2 as the preliminary light, specifies the distance of the test paper 20 based on the change rate of the light amount of the reflected light, and further the third measurement light. The configuration may be such that L3 is projected and the type of the test paper 20 is specified based on the amount of reflected light.

[Third Embodiment]
Unlike the blood glucose meters 10 and 10A according to the first and second embodiments, the blood glucose meter 10B according to the third embodiment is configured as an apparatus for performing the enzyme electrode method, as shown in FIG. Therefore, the detection unit 80 of the apparatus main body 14 has a pair of electrodes 80a and 80b that are in contact with the test strip 20 in the mounted state of the chip 12, and the glucose component in the blood collected on the test strip 20 reacts with the reagent. The electron (current) generated by doing is obtained.

  The pair of electrodes 80a and 80b are connected to the battery 82 and the ammeter 84, and use the power supplied from the battery 82 as a bias to output a detection value d proportional to the amount of glucose component. On the other hand, as shown in FIGS. 9A and 9B, the test paper 20 of the chip 12 is provided with a pair of terminals 21 for electrically contacting the pair of electrodes 80a and 80b. At this time, with respect to the cylindrical chip 12, it is preferable that a guide or a mark for specifying the mounting direction is attached, or the terminal 21 is set in a circumferential shape. 9A and 9B, the test paper 20 is formed in a circular shape in a plan view, but the shape of the test paper 20 is not particularly limited. A rectangular test paper 20 may be used.

  Returning to FIG. 8, the blood glucose meter 10B measures the detected current with the ammeter 84 and outputs the value (detection value) to the control circuit 40. Thereby, the detection value acquisition unit 62 illustrated in FIG. 3 acquires the detection value d, and the blood glucose level calculation unit 64 of the measurement processing unit 58B performs an appropriate process (calculation process of the enzyme electrode method) on the acquired detection value d. By executing the calculation, the blood glucose level is calculated and displayed on the monitor 28.

  The measurement processing unit 58B according to the third embodiment also includes a measurement mode setting unit 66B that specifies the type of the chip 12 (test paper 20) and sets the measurement mode. That is, even when the enzyme electrode method is performed, if the type of the test strip 20 or the chip 12 is different, it is necessary to change the measurement mode. Therefore, the blood glucose meter 10B is configured to perform the measurement mode setting method.

Specifically, as shown in FIGS. 9A and 9B, the type of the test paper 20 (including the change of the reagent) may be changed due to the specification change or the like. In this case, the internal resistance R of the test paper 20 itself changes as a characteristic amount of the test paper 20. For example, FIG. 9A shows a test strip 20 _X3 (chip 12 _X3 ) having a small internal resistance R1, and FIG. 9B shows a test strip 20 _Y3 (chip 12 _Y3 ) having a large internal resistance R2. When the internal resistance R of the test strip 20 changes in this way, the current amount of the test strip 20 changes when the blood glucose level is detected.

  Therefore, the measurement mode setting unit 66B drives the detection unit driving unit 60 to supply predetermined power (current and voltage) from the battery 82 to the test paper 20 before measuring the blood glucose level. This causes the test paper 20 to flow a current according to the internal resistance R, and the detection value acquisition unit 62 acquires the pre-detection value pd (pre-current value) from the test paper 20.

  In addition, the measurement mode setting unit 66B of the blood glucose meter 10B includes a feature amount calculating unit 68B, a specifying unit 70B, and a mode selecting unit 72, as shown in FIG. The characteristic amount calculation unit 68B calculates the resistance value of the internal resistance R as the characteristic amount of the test paper 20 from the acquired pre-detection value pd. The identifying unit 70B has a discrimination threshold value corresponding to the internal resistance R, or a map in which the resistance value and the type of the test paper 20 are associated with each other, and based on the feature amount calculated by the feature amount calculating unit 68B, the test is performed. The type of paper 20 is specified. Further, the mode selection unit 72 selects the measurement mode data MD corresponding to the specified type of test strip 20 as in the first and second embodiments.

  Thereby, the measurement mode setting unit 66B sets the measurement mode data MD selected by the mode selection unit 72, and causes the measurement mode data MD to be measured according to the measurement mode when the blood glucose level is measured. For example, the blood glucose meter 10B adjusts the power supplied from the battery 82 to the test paper 20 according to the measurement mode when measuring the blood glucose level, adjusts the amount of amplification of the current when the detection unit 80 detects the blood glucose, Processing such as adjusting the correction amount in the process of calculating the value is performed.

  As described above, also in the blood glucose meter 10B according to the third embodiment, similar to the blood glucose meters 10 and 10A, the blood glucose level measurement mode can be set according to different types of chips 12 (test paper 20). Therefore, it becomes possible to measure the blood glucose level with high accuracy. Further, since the pre-detection value pd extracted by the feature amount calculation unit 68B varies depending on the internal resistance R of the test paper 20, the specifying unit 70B satisfactorily specifies the type of the test paper 20 corresponding to the internal resistance R. be able to.

[Fourth Embodiment]
The blood glucose meter 10C according to the fourth embodiment performs the enzyme electrode method similarly to the blood glucose meter 10B, but as shown in FIG. 10A, a pair of electrodes for the detection unit 90 of the device body 14 to detect the blood glucose level. The blood glucose meter 10B differs from the blood glucose meter 10B in that it has the type specifying electrodes 92a and 92b different from the electrodes 90a and 90b. That is, the type specifying electrodes 92a and 92b are provided as a configuration for specifying the type of the test paper 20 (chip 12).

The device main body 14 of the blood glucose meter 10C has a battery 94 that supplies electric power from the pair of electrodes 90a and 90b to the test paper 20, and also has an ammeter 96 that detects a current flowing through the pair of electrodes 90a and 90b. .. The pair of type specifying electrodes 92a and 92b also have an ammeter 98 for detecting a current. On the other hand, as different types of chips 12, in addition to the terminals 21, chips 12 _X4 having identification terminals 93a and 93b capable of contacting the type identification electrodes 92a and 92b as shown in FIGS. 10B and 10C, and this identification There is a chip 12 _Y4 which does not include the terminals 93a and 93b.

The measurement processing unit 58C (see FIG. 3) of the control circuit 40 detects the current value output from the electrodes 90a and 90b as the detection value d, and energizes the type specifying electrodes 92a and 92b and the specifying terminals 93a and 93b. The type of the chip 12 is determined based on whether or not For example, if the pre-detection value pd output by the ammeter 98 is equal to or greater than the predetermined value, the measurement mode setting unit 66C identifies the test paper 20 _X4 (chip 12 _X4 ) that conducts the current shown in FIG. 10B. That is, it is determined that the type specifying electrodes 92a and 92b and the specifying terminals 93a and 93b are energized. On the other hand, if the pre-detection value pd is 0 or near 0, the measurement mode setting unit 66C determines that the test paper 20 _Y4 (chip 12 _Y4 ) is not energized as shown in FIG. 10C. Specify.

  As described above, the blood glucose meter 10C can specify the type of the test strip 20 only by determining whether or not the test strip 20 is energized. Therefore, similar to the blood glucose meters 10, 10A, and 10B, the blood glucose meter 10C can set the blood glucose level measurement mode according to the different types of chips 12 (test paper 20) to accurately measure the blood glucose level. It will be possible. In particular, the blood glucose meter 10C has the type specifying electrodes 92a and 92b, which are structures for exclusively specifying the type of the test strip 20, so that the blood glucose meter 10C can have a function specialized for specifying the type. Become.

  The structure for specifying the type of the chip 12 or the test paper 20 is not limited to the above. For example, the blood glucose meter 10, 10A to 10C is configured such that a chip having a predetermined structure and a chip having no predetermined structure can be attached to the device body 14, and the control circuit 40 of the device body 14 is configured to have a predetermined structure. The type of the chip 12 can be specified by detecting the presence or absence of the structure portion.

  Although the present invention has been described centering on a POCT device, particularly a device for measuring glucose concentration in blood, the present invention is not limited to the above-described embodiments, and various modifications can be made without departing from the scope of the present invention. Not to mention possible. As a sample solution for medical purposes, blood, urine, interstitial fluid, saliva, and other sample solutions obtained from living organisms are suitable. It may be a product. As the measurement target, sugars, lactic acid, various cholesterols, nucleic acids, antibodies, antigens, proteins, hormones, bacteria, enzymes, drugs, constituents, medical products, tissue markers, metabolites, chemical substances, etc. , Can be applied to quantitative determination. The component measuring device 10 is not limited to a POCT device of which only one type is measured, but a POCT device capable of simultaneously measuring other items, a large-scale inspection device, or a component measurement for measuring components such as drainage and industrial samples. It can also be applied to a device. Further, as the simplified measuring device, it is possible to apply not only to an SMBG device for measuring self-blood glucose for measuring the amount of glucose component in blood, but also to various devices for measuring the amount of predetermined component in liquid. it can. For example, you may apply to the component measuring device which measures the component (ketone body etc.) of urine.

10, 10A to 10C ... Component measuring device (blood glucose meter)
12, 12 _X1 , 12 _X2 , 12 _X3 , 12 _X4 , 12 _Y1 , 12 _Y2 , 12 _Y3 , 12 _Y4 ... Chip 14 ... Device main body 20, 20 _X1 , 20 _X2 , 20 _X3 , 20 _X4 , 20 _Y1 , 20 _Y2 , 20 _Y3 , 20 _Y4 ... Test paper 34, 80, 90 ... Detection unit 40 ... Control circuit 62 ... Detected value acquisition unit 64 ... Blood glucose level calculation unit 66, 66A to 66C ... Measurement mode setting unit 68, 68A, 68B ... Features Quantity calculation unit 70, 70A, 70B ... Specification unit 72 ... Mode selection unit

Claims (4)

A component measuring device that detachably mounts a chip on a device main body, detects the component amount of a component in a liquid collected in the chip, and calculates measurement information of the component,
The apparatus body includes a measurement mode setting unit that specifies the type of the chip in a mounted state of the chip, and sets a measurement mode when measuring the component amount based on the specified type of the chip ,
The chip has a test paper that can take in the liquid,
When detecting the amount of the component, the apparatus body projects the measurement light on the test paper and receives the reflected light, and outputs a detection value based on the reflected light, and the wavelength of the measurement light. Which has a light emitting means for projecting pre-light of a different wavelength from
The measurement mode setting unit,
A feature quantity extraction unit for extracting the feature quantity of the chip,
A specifying unit that specifies the type of the chip based on the characteristic amount extracted by the characteristic amount extracting unit,
The feature amount extracted by the feature amount extraction unit is output before the device body projects the preliminary light on the test paper and receives the reflected light before performing the detection of the component amount. Calculated from the detected value,
The component measurement device, wherein the feature quantity extraction unit calculates a light quantity from a range of wavelengths different from the wavelength of the measurement light as the light quantity of the reflected light of the preliminary light . The component measuring device according to claim 1 ,
The feature amount extraction unit extracts a change rate of the light amount of the reflected light with respect to a reference light amount as the feature amount,
The component measuring device, wherein the specifying unit specifies the type of the chip from the extracted change rate. A step of specifying the type of the chip by a measurement mode setting unit of the apparatus body, with the chip being removably attached to the apparatus body of the component measuring apparatus,
By the measurement mode setting unit, based on the type of the identified chip, the step of setting the measurement mode when measuring the component amount of the component of the liquid collected in the chip,
Based on the set the measurement mode, you see contains the steps of: detecting the component quantity to calculate the measurement information of the component,
The chip has a test paper that can take in the liquid,
When detecting the amount of the component, the apparatus body projects the measurement light on the test paper and receives the reflected light, and outputs a detection value based on the reflected light, and the wavelength of the measurement light. Which has a light emitting means for projecting pre-light of a different wavelength from
The step of identifying the type of chip includes
A feature amount extraction step of extracting a feature amount of the chip,
A specifying step of specifying the type of the chip based on the characteristic amount extracted in the characteristic amount extracting step,
The feature quantity extracted in the feature quantity extraction step is the output value obtained by the apparatus body projecting the preliminary light on the test paper and receiving the reflected light before the detection of the component quantity. Calculated from the detected value,
In the feature quantity extraction step, the light quantity is calculated from a range of wavelengths different from the wavelength of the measurement light as the light quantity of the reflected light of the preliminary light . In a component measuring device that measures the amount of components in liquid,
A step of specifying the type of the chip by a measurement mode setting unit of the apparatus body while the chip is detachably attached to the apparatus body of the component measuring apparatus;
By the measurement mode setting unit, based on the type of the identified chip, the step of setting the measurement mode when measuring the component amount of the component of the liquid collected in the chip,
A program for executing the step of detecting the component amount and calculating the measurement information of the component based on the set measurement mode ,
The chip has a test paper that can take in the liquid,
When detecting the amount of the component, the apparatus body projects the measurement light on the test paper and receives the reflected light, and outputs a detection value based on the reflected light, and the wavelength of the measurement light. Which has a light emitting means for projecting pre-light of a different wavelength from
The step of identifying the type of chip includes
A feature amount extraction step of extracting a feature amount of the chip,
A specifying step of specifying the type of the chip based on the characteristic amount extracted in the characteristic amount extracting step,
The feature quantity extracted in the feature quantity extraction step is the output value obtained by the apparatus body projecting the preliminary light on the test paper and receiving the reflected light before the detection of the component quantity. Calculated from the detected value,
In the characteristic amount extraction step, a light amount is calculated from a range of wavelengths different from the wavelength of the measurement light as the light amount of the reflected light of the preliminary light .

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