JP5023974B2 - Biosensor measuring instrument - Google Patents

Description

  The present invention relates to a biosensor measuring device, and more particularly to a measuring device that automatically identifies a biosensor.

  In recent years, biosensors that enable measurement of in-vivo substances such as blood glucose levels using enzyme reactions and antigen-antibody reactions have been developed. Such biosensors have different sensor sensitivities due to differences in the lots of enzymes used, production lines, detection electrode formation, enzyme application, etc., and the sensor sensitivities are the same among all production lots. Not necessarily. In order to calibrate the difference in sensor sensitivity, for example, the manufacturer adjusts the sensor sensitivity for each production lot and then ships a calibration sensor for adjusting the sensor sensitivity of the measuring instrument for each product package. Or assigning an identification number to each production lot. The user then calibrates the measuring instrument using the calibration sensor in advance, or selects the calibration data stored in the measuring instrument in advance by inputting the identification number and calibrates the measuring instrument. It is carried out. However, in any of the methods, the measurer himself has to calibrate, which not only gives the measurer the trouble of calibrating, but also gives rise to the problem that accurate measurement values cannot be obtained if calibration is forgotten. In addition, if the measuring device measures a plurality of target items, there is a problem that the calibration is not correctly performed due to a mistake in the calibration sensor.

  In order to solve such problems, for example, in Japanese Patent Laid-Open No. 2001-311711 (Patent Document 1), a slit for identifying information for calibration is provided in the output electrode of the biosensor, and the installation of this slit is provided. A method for automatically recognizing calibration data based on a pattern is disclosed.

  In Japanese Patent Laid-Open No. 10-332626 (Patent Document 2), a calibration electrode is provided separately from the output electrode on a substrate on which an output electrode constituting a biosensor is formed, and the output electrode and the calibration electrode are provided. Disclosed is a method for automatically recognizing calibration data selected by a closed circuit formation pattern formed between and.

  International Publication WO2003 / 76918 (Patent Document 3) discloses a biosensor in which a protrusion is provided at the tip of a substrate on which an output electrode constituting the biosensor is formed, or a protrusion is provided on the back surface of the substrate. Is disclosed. Here, the formation position of these protrusions and projections is recognized using the capacitance change of the capacitor formed on the connector for mounting the sensor, and calibration data is automatically recognized from this formation position, or the output electrode An electrode different from the output electrode is provided on the substrate on which the electrode is formed, and the position where this electrode is formed is automatically recognized by using the capacitance change of the capacitor formed between the electrode and the sensor mounting connector. Yes.

  Further, in Patent Document 3, as another method, a through hole is formed at the tip of a substrate on which an output electrode constituting a biosensor is formed, and the position of the through hole is defined as a leaf spring shape passing through the through hole. A method for recognizing using the conduction state of the position detection electrode is disclosed.

JP 2001-311711 A JP-A-10-332626 International Publication No. WO2003 / 76918

  However, in the method of forming a slit in the electrode, a high level of technology is required for forming the slit. In addition, it is conceivable that a slit formation failure or an electrode short-circuit is likely to occur, and a calibration data identification failure is likely to occur. Further, in the method of forming the calibration electrode and the protruding portion or the protruding portion for changing the capacity, it is necessary to form a new electrode or protruding portion after manufacturing, and there is a problem that the manufacturing process of the biosensor becomes complicated. is there.

  Further, in the method of forming the calibration electrode, the counter electrode (connector pin) that forms a closed circuit between the output electrode and the calibration electrode is formed in the connector, and the protrusion or the like is formed to change the capacitance. In the method in which the capacitor forming counter electrode corresponding to the calibration electrode is passed through the through hole and the position detecting electrode is passed through, it is necessary to provide the position detecting electrode on each connector.

  By the way, there are many technical restrictions in providing such a detection means in a connector, and there are restrictions in the number of counter electrodes etc. which can be provided in the connector mounting part of a biosensor. For this reason, it is considered that the number of calibration data to be prepared is limited, and there is a possibility that various biosensors cannot be supported. In addition, the method using a counter electrode and the method using a position detection electrode tend to cause a problem in that automatic identification cannot be performed correctly due to poor contact between the electrodes as the number of times the biosensor is used increases.

  The present invention has been made in view of the above-mentioned problems of the background art, and an object of the present invention is to provide an automatically identifiable biosensor measuring device that avoids identification defects based on technical limitations and contact failures received from connectors. Is to provide.

  The biosensor measuring device of the present invention is a biosensor measuring device that measures using a biosensor with a mark that can be identified by optical means, and has the maximum number of marks required for biosensor identification. 1 to the light receiving element that receives light from the light emitting element and the light emitting element, or the light receiving element that has the maximum number of marks necessary for identification of the biosensor, and 1 to the light that emits light to the light receiving element It is characterized by having the maximum number of light emitting elements.

  According to the present invention, the identification mark attached to the biosensor can be read by combining the light emitting element and the light receiving element. Therefore, it can identify in a non-contact state with a biosensor, and the identification failure by the increase in the frequency | count of use can be avoided.

  Hereinafter, the present invention will be specifically described with reference to the accompanying drawings. FIG. 1 is a schematic cross-sectional view of a biosensor measuring device 1 according to the present invention, partly broken, and FIG. However, the embodiment shown below is an exemplification, and the present invention is not limited to the following embodiment, and all the modifications included in the scope of the claims and equivalents thereof are included in the present invention. It is intended to be included.

  The measuring instrument 1 has a circuit board 3 in which a connector 10 for mounting the biosensor 100 and taking out the output of the biosensor 100 is mounted in a housing 2. This measuring instrument 1 is necessary based on identification information composed of a storage unit 20 in which calibration data is stored, a detection unit 30 that detects an identification mark 160 provided on the biosensor 100, and the identification mark 160. A collation unit 40 for collating correct calibration data, a computation unit 50 for computing a test value from the output of the biosensor 100 using the collated calibration data, and a display unit 60 for displaying the result.

  The detection unit 30 includes detection means for detecting an identification mark 160 provided on the biosensor 100. This detection means comprises optical means, and includes a light emitting element 31 such as a light emitting diode and a light receiving element 32 such as a photodiode that receives light emitted from the light emitting element 31 and passing through or passing through the identification mark 160.

  The illustrated measuring instrument 1 has the same number of light emitting elements 31 and 1 as the maximum number of identification marks 160 provided on the biosensor 100, that is, the maximum number of identification marks 160 necessary for identifying the identification information of the biosensor 100. Two light receiving elements are provided. The number of necessary light emitting elements 31 varies depending on the number of calibration data prepared in the measuring instrument 1 in advance. For example, when the identification information of the biosensor 100 is configured by four identification marks 160, four light emitting elements 31 are provided.

  Each light emitting element 31 is mounted on the circuit board 3 disposed in the housing 2 of the measuring instrument 1 corresponding to the position of each identification mark 160, and emits light from below the biosensor 100 toward the identification mark 160. Irradiate. In other words, when the maximum number of identification marks 160 is formed on the biosensor 100, the light emitting elements 31 are mounted so that the light emitting elements 31 and the identification marks 160 have a one-to-one relationship. The detection unit 30 sequentially causes each light emitting element 31 to emit light at a constant light emission interval Δt.

  One light receiving element 32 is mounted on the circuit board 3 on the same surface as the substrate surface on which the light emitting element 31 is mounted, with the light receiving surface facing upward. Above the light emitting element 31, a light receiving portion 33 having a light receiving surface facing downward is disposed. The biosensor 100 is mounted between the light receiving element 32 and the light receiving unit 33. The light receiving unit 33 and the light receiving element 32 are optically connected by a light guide path 34 made of an optical fiber or the like. On the light receiving element 32 side of the light guide path 34, a light leakage prevention cover 35 is press-fitted and fixed to the circuit board 3, and light received by the light receiving portion 33 is reliably received by the light receiving element 32. Thus, the light emitted from the light emitting element 31 and passing through the identification mark 160 is received by the light receiving element 32 through the light guide 34 and converted into an electric signal.

  FIG. 3 is a schematic perspective view showing an example of the biosensor 100 used in the measuring instrument 1, and FIG. 4 is an exploded perspective view of the biosensor 100. In FIG. 4, the adhesive layer 140 is omitted.

  In the biosensor 100, the cover 120 and the substrate 110 are bonded together with an adhesive layer 140 so as to form a sample space 130 between the cover 120 and the substrate 110, which are insulating plate members, as shown in both drawings. Have a structure. The biosensor 100 has a sample introduction port 101 connected to the sample space 130 at the tip thereof. Further, at the rear end of the sample space 130, vent holes 141 connecting the sample space 130 and the outside of the biosensor 100 are extended on both sides thereof. A pair of electrodes 111 is formed on the substrate 110 so as to face the sample space 130. The connector mounting portion 150 at the end of the substrate opposite to the sample introduction port 101 is formed with a voltage extraction terminal (output electrode) 112 electrically connected to the electrode 111 through the conductor path 113. Yes. The cover 120 is provided with a reagent layer 121 that faces the sample space 130 and reacts with a sample (specifically, a body fluid such as blood). The pair of electrodes 111 and the reagent layer 121 constitute a biosensor. An example of such a biosensor 100 is a chip in which a board member and a cover are produced by bending a plate member as described in, for example, International Publication WO2005 / 10591. However, the biosensor 100 used in the measuring instrument 1 of the present invention is not limited to the illustrated biosensor 100 having the structure shown in International Publication WO2005 / 10591.

  In an area other than the connector mounting portion 150, for example, in the illustrated case, three identification marks 160 including through holes are provided at positions penetrating the conductor path 113. The maximum number of identification marks 160 of the biosensor 100 is 4, and a circle indicated by a broken line indicates a position where one remaining identification mark 160 is to be formed. The formation position of the identification mark 160 may not be a position that penetrates one conductor path 113 as shown unless it is a position that affects the measurement result, for example, a position that does not penetrate the reagent layer 121 or the sample space 130. It does not matter even if the position crosses the two conductor paths 113. Further, from the viewpoint of the strength of the biosensor 100, a position passing through the three layers of the cover 120, the adhesive layer 140, and the substrate 110 is preferable, but the identification mark is formed on the substrate 110 exposed when inserted into the connector (not shown). 160 may be provided. In order to reduce the influence on the measurement value, it is desirable to provide in a non-conductor path forming region such as between the two conductor paths 113.

The presence or absence of the identification mark 160 constitutes identification information (bit pattern) for automatically recognizing calibration data necessary for calibration. That is, an identification mark (bit pattern) in which the presence or absence of the identification mark 160 is indicated by a binary value is formed, and this identification mark determines calibration data used for calibration. In other words, in the identification mark 160 formed of a through hole, the position where the through hole is formed indicates a bit pattern, and necessary calibration data is determined from the bit pattern. The position and number of the identification marks 160 vary depending on the production lot of the biosensor 100, and the identification marks 160 are formed by stamping or drilling after a trial test after production. The maximum number of identification marks 160 differs depending on the number of calibration data prepared in advance in the measuring instrument 1, and for example, if the calibration data prepared in the measuring instrument 1 is 3 (= 2 ² −1) types. For example, a maximum of two identification marks 160 are formed. If 15 (= 2 ⁴ −1) calibration data are prepared, a maximum of four identification marks 160 are formed. Although the diameter of the through-hole as the identification mark 160 varies depending on the performance of the light receiving element 32 to be used, it may be a size that allows light to pass through. For example, the diameter is about 1 to 3 mm.

  When the biosensor 100 is inserted into the socket 10 of the measuring instrument 1 and preparation for measurement is completed, light is sequentially emitted from the light emitting elements 31 at the light emission interval Δt. When the light receiving element 32 receives light, an electric signal is generated. Therefore, if a through hole (identification mark 160) is formed, it can be detected as an ON signal. Therefore, the formation position of the identification mark 160 can be detected by matching the timing at which each light emitting element 31 emits light with the timing at which the light receiving element 32 receives light.

  FIG. 5 is an explanatory diagram showing an example of a method for detecting identification information in the detecting means. FIG. 5 shows a case where identification information is configured from a maximum of four identification marks 160 arranged in series. In the biosensor 100 shown in the figure, among the four identification marks 160, for example, position A, position B, Identification information is constituted by three identification marks 160 (indicated by solid circles) at the position D. Although the identification mark 160 is not formed at the position C, one remaining identification mark 160 (indicated by a broken line) is formed at this position as necessary. Then, four light emitting elements A, B, C, D corresponding to the identification marks 160 are mounted on the circuit board 3 as shown in FIG.

  Now, when the light emitting element A at the position A emits light, the light receiving element 32 receives light, so that the detection unit 30 detects an ON electrical signal. Then, the detection unit 30 recognizes that the identification mark 160 is formed at the position A. Next, when the light emitting element B at the position B emits light, the light receiving element 32 receives light, so that the detection unit 30 detects the electrical signal ON. Then, the detection unit 30 recognizes that the identification mark 160 is formed at the position B. Next, when the light emitting element C at the position C emits light, since the identification mark 160 is not formed at the position C, the detection unit 30 cannot detect the electrical signal ON. Then, the detection unit 30 recognizes that the identification mark 160 is not formed at the position C. Finally, when the light emitting element D at the position D emits light, the light receiving element 32 receives light, so that the detection unit 30 detects the electrical signal ON. Then, the detection unit 30 recognizes that the identification mark 160 is formed at the position D. As a result, the detection unit 30 detects a binary signal corresponding to the bit pattern of ON, ON, OFF, ON at a time interval of Δt, and outputs this binary signal to the verification unit 40. The collation unit 40 retrieves calibration data corresponding to this bit pattern from the storage unit 20 and outputs it to the calculation unit 50. The calculation unit 50 obtains a measurement value from the output voltage output from the biosensor 100 based on the calibration data, and outputs the measurement value to the display unit 60. In this way, the calibration data is automatically recognized, and the display unit 60 displays an accurate measurement value calibrated based on the calibration data.

  Similarly, although not shown, in the biosensor 100 in which the through holes are formed as the identification marks 160 at the positions B and D, the detection unit 30 is OFF, ON, OFF, ON 2 in the same way as described above. A value signal is obtained, and calibration data corresponding to the binary signal is used. Further, the positions of the identification marks 160 do not need to be in series, and can be provided in a matrix of 2 × 2, for example. At this time, the light emitting elements 31 are arranged in a 2 × 2 matrix. When the through hole 160 does not exist at all, the detection unit 30 does not detect the ON signal, and therefore calibration data corresponding to the OFF, OFF, OFF, OFF bit patterns may be used, or calibration is performed. The measured value may be calculated without any change.

  Thus, the measuring instrument 1 can read the identification mark 160 attached to the biosensor 100 by the light emitting element 31 and the light receiving element 32. Therefore, it is possible to identify the biosensor 100 in a non-contact state with the biosensor 100, and it is possible to prevent identification failure due to an increase in the number of uses.

  A light emitting element 31 and a light receiving element 32 are provided in a region other than the connector 10. For this reason, the technical restrictions by the connector 10 decrease. Moreover, since the light receiving unit 33 and the light receiving element 32 that receive the light that has passed through the identification mark 160 are optically connected by the light guide path 34, the light emitting element 31 and the light receiving element 32 can be mounted on the same substrate surface, The complication of the manufacturing process is prevented.

  In the above method, the case where a plurality of light emitting elements 31 and one light receiving element 32 are used is illustrated, but the individual light receiving elements 32 are arranged in a one-to-one relationship with each light emitting element 31, or an array It is also possible to arrange a light receiving array in which the light receiving elements are arranged and the position information received can be detected. In this case, it is not necessary for the light emitting elements 31 to emit light sequentially at a constant time interval Δt, and all the light emitting elements 31 can emit light simultaneously. However, in this case, if the light emitting elements 31 are close to each other, the light receiving element 32 corresponding to the position where the identification mark 160 is not formed may receive light and misidentify the identification information. It is advisable to take preventive measures to avoid misrecognition, such as setting an offset that is detected as ON.

  In addition, the light emission wavelength of the light emitting element 31 and the light receiving wavelength of the light receiving element 32 corresponding to the light emitting element 31 can be made different from each other to prevent misidentification.

  FIG. 6 is a schematic cross-sectional view in which a biosensor measuring instrument 1 according to another embodiment of the present invention is partially broken. The measuring instrument 1 includes one light emitting element 31 and a plurality of light receiving elements 32. The light receiving element 32 is mounted so that the light receiving element 32 and the identification mark 160 have a one-to-one relationship when the maximum number of identification marks 160 is formed on the sensor chip 100. Further, one light emitting unit 36 that emits light toward the maximum number of identification marks 160 is provided. The light emitting unit 36 is optically connected to the light emitting element 31 and the light guide path 34. On the light emitting element 31 side of the light guide path 34, a light leakage preventing cover 35 press-fitted and fixed to the circuit board 3 is provided, and light emitted from the light emitting element 31 is reliably emitted from the light emitting unit 36. Thus, the light emitted from the light emitting element 31 (light emitting unit 36) passes through the identification mark 160, is received by the light receiving element 32, and is converted into an electrical signal. Calibration data necessary for the biosensor 100 can be automatically identified by the measuring instrument 1 having such a configuration.

  FIG. 7 is a schematic cross-sectional view in which a biosensor measuring instrument 1 which is still another embodiment of the present invention is partially broken. The light emitting element 31 and the light receiving unit 33 of the measuring instrument 1 are provided in the connector 10, and the light receiving unit 33 and the light receiving element 32 on the circuit board 3 are optically connected by a light guide path 34.

  FIG. 8 is a perspective view showing an example of a biosensor 100 used in the measuring instrument 1. The biosensor 100 includes an identification mark 160 in a marker forming region 151 between two terminals 112 provided in the connector mounting portion 150. The presence or absence of the identification mark 160 is detected by optical means by using two types of identification marks 160 having different optical characteristics. For example, the illustrated biosensor 100 includes two types of identification marks 160, which are a light-transmitting identification mark 160a and a light-low-transmitting identification mark 160b. In this case, (1) when the transmittance is low, “marked” is determined, and when the transmittance is high, “not marked”, or (2) when the transmittance is high, “marked”, the transmittance is It can be judged that there is no mark when it is low, and the two are distinguished by the difference in transparency. The difference in transparency can be distinguished by the electromotive voltage generated by the light receiving element 32.

  In many cases, the biosensor 100 uses a substrate 110 having high light transmittance. For this purpose, for example, an identification mark 160b having a low light transmission property by application of a material having a low light transmission property, such as a conductive film containing ink, a seal, gold, copper, carbon or the like, preferably a light non-transparent material. Is formed. That is, the low-light-transmitting identification mark 160b is formed by applying such low-light-transmitting ink or the like, and the light-transmitting mark 160a is formed by not performing these coatings. Therefore, if it can be recognized that light is transmitted through the substrate 110 and there is no low light-transmitting identification mark 160b, it can be determined that the light-transmitting mark 160a is formed. The identification information is constituted by the two types of identification marks 160 formed in this way, and the detection unit 30 is a bit that is output ON and OFF from the combination of the light transmissive mark 161a and the light transmissive mark 161b. Get a pattern.

  In the illustrated biosensor 100, the light-transmitting identification mark 160 a is formed by removing a necessary region of the low-light-transmitting film 152 formed in the marker forming region 151 by a method such as peeling, punching, or cutting. Is formed. Then, the region where the low light-transmitting film 152 remains without being deleted is recognized as the low light-transmitting identification mark 160b (indicated by a broken-line square frame in the drawing). In particular, since the terminal 112 is formed on the connector mounting portion 150 of the biosensor 100 by applying a conductive paste or the like, a film 152 having a low light transmittance can be formed simultaneously with the formation of the terminal 112. Further, since the light-transmitting identification mark 160 is provided by removing a predetermined region of the film 152, the process is not complicated, which is very convenient. In addition, since the light transmission property is used, the formation accuracy may be slightly deteriorated.

  However, the light receiving element 32 may also be provided in the connector 10. As described above, the measuring instrument 1 of the present invention can also include the light emitting element 31 and the light receiving element 32 that detect the presence or absence of the identification mark 160 in the connector 10. Since the measuring instrument 1 can recognize the identification information in a non-contact state with the biosensor 100, it is possible to avoid the identification failure accompanying the contact failure.

  FIG. 9 is a schematic cross-sectional view in which a biosensor measuring instrument 1 which is still another embodiment of the present invention is partially broken. The light emitting element 31 and the light receiving element 32 are arranged on the same substrate surface of the circuit board 3. The light emitting element 31 emits light toward the identification mark 160 formed on the back surface of the biosensor 100, and the light receiving element 32 receives the light reflected by the identification mark 160.

  FIG. 10 is a rear view of the biosensor 100 used in the measuring instrument 1. In this biosensor 100, an identification mark 160 is formed in a marker forming region 151 provided on the back surface of the substrate 110. The identification mark 160 includes three light-reflecting identification marks 160c having higher light reflectivity and one low-light reflecting identification mark 160d having lower light reflectivity. The light-reflective identification mark 160c can be formed, for example, by applying a light-reflective substance or sticking a seal. The area where the substance is not applied or the sticker is not applied is recognized as a light low-reflectivity mark 161d (indicated by a broken-line square frame in the figure).

  The light emitted from the light emitting element 31 is reflected by the light reflective identification mark 160c, received by the light receiving element 32, and converted into an electrical signal. In this way, the detection unit 30 recognizes the electrical signal output from the light receiving element 32 as a bit pattern and determines necessary calibration data.

  Also in this measuring instrument 1, the same number of light emitting elements 31 and light receiving elements 32 as the maximum number of identification marks 160 are arranged, and the same number of light emitting elements 31 and one light receiving element 32 as the maximum number of identification marks 160 are arranged. Any configuration may be employed such that the light emitting elements 31 are caused to emit light sequentially at time intervals, or the same number of light receiving elements 32 as the maximum number of light emitting elements 31 and identification marks 160 are arranged.

  Further, although not shown in the figure, like the biosensor 100 shown in FIG. 8, a label formation region 151 made of a light-reflective film is prepared on the back surface of the biosensor 100, and a predetermined region of the region 151 is deleted. By doing so, the low-light reflective identification mark 150b may be formed.

  As described above, the measuring instrument 1 of the present invention can detect the presence or absence of the identification mark 160 using light reflectivity and identify data necessary for calibration. In particular, the cover 120 region of the biosensor 100 can hardly be expected to be transmissive because the conductor path 113 is present, but is wider than the connector mounting portion 150. Accordingly, identification marks 160 made up of a large number of through-holes and light-reflecting identification marks 160a can be formed in this region, and more calibration data can be handled.

It is the schematic sectional drawing which fractured partially the biosensor measuring device of the present invention. It is a block diagram which shows the structure of the measuring device of FIG. It is a schematic perspective view which shows an example of the biosensor used for the measuring device of FIG. FIG. 4 is an exploded perspective view of the biosensor of FIG. 3. It is explanatory drawing which shows the detection method of the identification mark of a biosensor, Comprising: (a) is a figure which shows the position of an identification mark, (b) is a figure which shows the light emission timing of a light emitting element, and the light reception timing of a light receiving element. It is the schematic sectional drawing which fractured | ruptured partially the biosensor measuring device which is another embodiment of this invention. It is the schematic sectional drawing which fractured | ruptured partially the biosensor measuring device which is another embodiment of this invention. It is a schematic perspective view which shows an example of the biosensor used for the measuring device of FIG. It is the schematic sectional drawing which fractured | ruptured partially the biosensor measuring device which is another embodiment of this invention. It is a rear view which shows an example of the biosensor used for the measuring device same as the above.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Measuring instrument 2 Housing | casing 3 Circuit board 10 Connector 30 Detection part 31 Light emitting element 32 Light receiving element 40 Collation part 50 Operation part 100 Biosensor 110 Board | substrate 112 Terminal 113 Conductor path 120 Cover 150 Connector mounting part 160 Identification mark 160a Identification mark 160b Light-low transmission identification mark 160c Light-reflection identification mark 160d Light-low-reflection identification mark

Claims (8)

A biosensor measuring device that enables identification of the biosensor from the number of through-holes and the position of the biosensor,
1 to the maximum number of light receiving elements for receiving light from the maximum number of the light emitting element and the light-emitting element of the through-holes required to identify, or to the maximum number of light receiving elements and the light receiving element of the through-holes necessary for identification 1 to the maximum number of light emitting elements for emitting light,
A mounting substrate on which the light emitting element and the light receiving element are mounted on the same surface;
A light receiving portion disposed so as to be able to receive light that has passed through the through hole;
A biosensor measuring device comprising a light guide for guiding light received by the light receiving unit to the light receiving element. A biosensor measuring device that enables identification of the biosensor from the number of through-holes and the position of the biosensor,
For the maximum number of light-emitting elements necessary for identification and 1 to the maximum number of light-receiving elements for receiving light from the light-emitting elements, or for the maximum number of light-receiving elements required for identification and the light-receiving elements 1 to the maximum number of light emitting elements for emitting light,
A mounting substrate on which the light emitting element and the light receiving element are mounted on the same surface;
A light emitting unit for irradiating the light emitted from the light emitting element toward the through hole;
A biosensor measuring instrument comprising a light guide for guiding light emitted from the light emitting element to a light emitting section.   The biosensor measuring device according to claim 1, wherein the light emitting element and the light receiving element are arranged in a one-to-multiple or plural-to-one relationship. A single light receiving unit that receives light from the plurality of light emitting elements;
One light receiving element;
The biosensor measuring device according to claim 1 , further comprising one light guide path. One light emitting element;
One light emitting unit;
The biosensor measuring device according to claim 2 , comprising one light guide path. The biosensor measuring device according to claim 1 , wherein the light emitting wavelengths of the plurality of light emitting elements are different from each other.

The biosensor measuring device according to claim 6 , further comprising a control unit that causes the light emitting element to emit light at regular time intervals. A light receiving element or a light receiving portion that receives light emitted from the light emitting element and the light emitting element, or a connector forming region in which a light emitting element or light emitting portion that emits light toward the light receiving element and the light receiving element is attached to a biosensor. The biosensor measuring device according to claim 1 , wherein the biosensor measuring device is provided in addition to the above.

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