JP6675763B2 - Optical semiconductor device used for measuring blood sugar level and apparatus using the same - Google Patents

Description

  The present invention relates to an optical semiconductor device used for measuring a blood glucose level and an apparatus using the same.

  The number of diabetic patients with lifestyle-related diseases is increasing year by year. According to a 2014 survey by the Ministry of Health, Labor and Welfare, the number of diabetic patients in Japan has reached about 3.16 million, and about half of them are being treated. It is said. If the blood sugar level is high, medicine is used to lower the blood sugar level. On the other hand, low blood sugar is extremely dangerous if it is affected by drugs, so that candy and the like are eaten to increase the blood sugar level. For this reason, in the treatment of diabetes, blood is collected from a patient with an injection needle and the blood sugar level is measured. Naturally, blood collection may be painful to the patient and may result in infection after blood collection. In addition, blood collection costs are high.

Therefore, a non-invasive study for measuring a blood glucose level using a near-infrared light beam without collecting blood from a patient with an injection needle has been conventionally performed.
For example, in the blood sugar level measuring device disclosed in Patent Document 1 below, a light source that generates light of at least two different wavelengths, an optical system for irradiating light emitted from the light source to the body surface, And a photodetector for detecting reflected light of the light.
According to Patent Document 2 below, infrared light emitted from the two light emitting elements 122 of the sensor node 1 shown in FIG. 3 is irradiated on a wrist as a measurement site, and a change in intensity of scattered light from a blood vessel is detected by a light receiving element. The light is received at 121, and the pulse and the pulse wave are estimated from the cycle of the intensity change to measure the blood sugar level.
Furthermore, the blood sugar level measuring device according to Patent Document 3 below has a configuration in which a sensor having a light receiving element formed around a light emitting element is incorporated in a wristwatch.

Japanese Patent No. 3884036 (Japanese Patent Application Laid-Open No. 2006-61308) Japanese Patent No. 5090013 (Japanese Unexamined Patent Application Publication No. 2008-206575) JP 2009-109927 A

However, in each of Patent Literature 1 and Patent Literature 2, as shown in FIGS. 4 and 3, it is difficult to finely adjust the optical axis of the light emitting element and the light receiving element, and the near infrared ray that emits light. Since the amount of near-infrared light received with respect to the amount of light is small, there is a problem that the utilization efficiency of near-infrared light is reduced.
Further, in Patent Document 3, as shown in FIG. 55, high accuracy is achieved unless a thick blood vessel of the user is located near the position of the window 1006 of the wristwatch-type blood glucose level measuring device 1000. Measurement is difficult.
The present invention has been made to solve such a conventional problem, and a blood glucose level measuring apparatus capable of performing a stable measurement of blood glucose level without requiring fine optical axis adjustment between a light emitting element and a light receiving element. The purpose is to provide.

      The present invention relates to an optical semiconductor device used for a blood sugar level measuring device having an operation unit, wherein a lens substrate on which a plurality of lens groups for condensing passing light along an optical axis is arranged, and a direction of the optical axis. On one surface of the lens substrate, which is perpendicular to the lens, light of a specific wavelength, which is formed corresponding to each of the plurality of lenses and whose absorptance increases in accordance with the blood glucose level, is input from the operation unit to a predetermined wavelength A plurality of light-emitting elements that sequentially emit light and transmit the corresponding lenses in accordance with the instruction; and an inner edge formed on one surface of the lens substrate corresponding to each of the plurality of lenses and adjacent to an outer edge of the light-emitting element. In a region defined by an inner edge of the light emitting element and an outer edge outside the inner edge of the light emitting element, light of a wavelength incident through the corresponding lens is received, and an electric value indicating the intensity value of the light is received. Generate a signal A plurality of light receiving elements, a storage unit for storing corresponding data indicating a correspondence between an intensity value of light indicated by an electric signal generated by the light receiving elements and a blood sugar level, and a light receiving element surrounding the light emitting elements sequentially emitting light And a calculating unit that calculates a blood glucose level of the measurement target close to the lens substrate based on the light intensity value indicated by the electric signal generated from the optical signal and the blood glucose level of the corresponding data.

  ADVANTAGE OF THE INVENTION According to the blood glucose level measuring apparatus of this invention, the effect that the stable measurement of a blood glucose level is attained without requiring fine optical axis adjustment of a light emitting element and a light receiving element is acquired.

2A and 2B show optical components used for blood glucose measurement according to the first embodiment, wherein FIG. 1A is a plan view of a lens, FIG. 1B is a cross-sectional view taken along line XX of FIG. 1A, and FIG. It is. 2A and 2B show a basic structure of a light emitting element and a light receiving element according to the first embodiment, wherein FIG. 2A is a sectional view of the light emitting element, FIG. 2B is a sectional view of the light receiving element, and FIG. . FIG. 6 is a cross-sectional view of a lens having curved surfaces on both sides, showing another optical component of the first embodiment. It is a figure showing the wristwatch type blood glucose level measuring device of a 1st embodiment. 1A shows an electronic circuit, FIG. 1B shows a light receiving circuit, and FIG. 1C shows a data configuration of an SRAM according to the first embodiment. 5A is a flowchart of a blood sugar level measurement process, and FIG. 5B is a flowchart of a timer interrupt. It is a flowchart which shows the blood glucose level measurement process of FIG. It is a flowchart following FIG. It is a flowchart following FIG. FIG. 4 shows a menu screen in the first embodiment, in which (A) is a blood glucose level measurement screen, (B) is a meal start screen, and (C) is a communication setting screen. It is a figure showing arrangement of 721 optical units in a 1st embodiment. FIG. 4 is a diagram illustrating a data array before estimating a blood vessel position in the first embodiment. It is a figure showing the position of the blood vessel before presumption in a 1st embodiment. FIG. 4 is a diagram showing a data array after estimating a blood vessel position in the first embodiment. FIG. 4A is a diagram illustrating a position of a blood vessel in the first embodiment, FIG. 4A is a diagram illustrating a position of a blood vessel after estimation, and FIG. It is a figure showing blood glucose level data in a 1st embodiment. It is a figure showing the example of a display of the blood collection result in a 1st embodiment. FIG. 7 is a diagram illustrating a display example of a result of simultaneous blood collection and measurement in the first embodiment. FIG. 5 is a diagram illustrating a display example of data input according to the first embodiment. FIG. 2 is a perspective view illustrating data communication according to the first embodiment. FIG. 2 is a plan view of the optical semiconductor device according to the first embodiment. FIG. 22 is a cross-sectional view of the optical semiconductor device including the main body taken along line XX of FIG. 21. 23 is an equivalent circuit of a switch including the connector shown in FIG. 22. 4A and 4B are diagrams illustrating a tightening state of a band according to the first embodiment, in which FIG. 4A is a side view of the apparatus, and FIG. 4B is a diagram illustrating a display example of a message. FIG. 6 shows a floating origin system according to a second embodiment, in which (A) shows a configuration of converted honeycomb coordinates, (B) shows a configuration of an interchangeable lens, and (C) shows a configuration of a circuit of the system. FIG. 9A is a plan view of the case of the mobile terminal according to the third embodiment, and FIG. 9B is a cross-sectional view taken along line YY of FIG. FIG. 9 shows a mobile terminal according to a third embodiment, in which (A) is a plan view and (B) is a rear view.

  Hereinafter, a first embodiment of a blood sugar level measuring device according to the present invention will be described with reference to FIGS. The blood sugar level data includes an instantaneous blood sugar level (unit: mg / dL) and hemoglobin (Hb) A1C (unit:%) which is a cumulative value of the blood sugar level.

  When a light beam of a specific wavelength of near infrared rays (for example, 500 nm to 1200 nm) is irradiated on human skin and the reflected light is received, a part of the irradiated light beam is absorbed by sugar in blood. Therefore, the blood sugar level can be indirectly measured by measuring the intensity of the reflected light. In addition, HbA1C can be measured based on the cumulative value of blood sugar levels for several tens of days.

  FIG. 1 is a diagram illustrating optical components used in the blood sugar level measuring device according to the first embodiment. FIG. 1A is a plan view of a regular hexagonal lens 1 constituting a part of a lens substrate formed using a transparent glass substrate. FIG. 1B is a cross-sectional view of a part including the lens 1 of the lens substrate taken along line XX of FIG. 1A. The material of this glass substrate is lead glass containing silicic acid, calcium carbonate, and lead oxide and having high transparency and a high refractive index, or lead-free glass containing no lead oxide. Among them, Tritan Crystal (registered trademark) developed by Zwiesel Crystal Glass Co. of Germany and the like is preferable. Alternatively, a transparent plastic made of polyethylene terephthalate, polyether sulfone, or the like may be used.

  1A and 1B, the lens 1 has a convex portion on one surface (the right side of FIG. 1B) of the lens substrate and the other surface (the left side of FIG. 1B) It has a flat shape. The light emitting element 2 and the light receiving element 3 are formed on this flat surface as shown in FIGS. 1 (A) and 1 (B). A part of the light beam emitted from the light emitting element 2 to the blood vessel 400 is absorbed by the blood in the blood vessel 400, a part of the light beam passes, and the rest is reflected and received by the light receiving element 3.

  The light-emitting element 2 emits light having a wavelength in a specific range, specifically, light having a wavelength λ of near-infrared rays. As shown in FIG. 1A, the light receiving element 3 surrounds the light emitting element 2 by an inner edge close to the outer edge of the light emitting element 2, and is defined by an inner edge thereof and an outer edge outside the inner edge (that is, an area defined by the outer edge). , A doughnut-shaped region), receives light having a wavelength λ that is transmitted through the lens 1 and generates an electric signal indicating the intensity value of the light. The center of the lens 1, the center of the light emitting element 2, and the center of the light receiving element 3 have the same optical axis 5 represented by a dashed line.

  As shown in FIG. 1C, a plurality of optical units of a lens 1, a light-emitting element 2, and a light-receiving element 3 are formed on the lens substrate in units of a regular hexagonal plane. That is, an array of microlenses having a honeycomb structure is realized by a plurality of regular hexagonal regions. This honeycomb structure allows a wide variety of variations. This variation will be further described later.

In FIG. 1C, a plurality of optical units are arranged around a lens 1 (0) on which a light emitting element 2 and a light receiving element 3 are formed, and around the lens 1 (0), a lens 1 (2) and a lens 1 (1). (3) are formed. Note that the plurality of optical units and a semiconductor circuit described below constitute an optical semiconductor device which is the most important component in the first embodiment.
Assuming that the number of optical units on the lens substrate is Xi, Xi is represented by Xi = 6i (i is an integer of 1 or more). X0 in the case of i = 0 is one optical unit located at the center of the lens substrate.

  When i = 1, 2, 3, 4,..., 16, the number of optical units surrounding the central optical unit (X0) is 6, 12, 18, 24,. That is, the number of optical units is an arithmetic progression of six. Then, the total number of optical units other than one at the center is 720 (the number of optical units is 721 when one at the center is added). In the case of the present embodiment, the diameter of the sensor in the optical semiconductor device is a substantially circular shape of about 30 mm. The blood sugar level measuring device 11 in the present embodiment is a substantially square of 40 mm × 40 mm or more, and can sufficiently accommodate this optical semiconductor device.

FIG. 2 is a diagram showing a principle structure of the light emitting element 2 and the light receiving element 3 in the first embodiment, and a thin film transistor which is a semiconductor circuit including the light emitting element 2, the light receiving element 3, the driving circuit, the light receiving circuit and the like.
FIG. 2A is a cross-sectional view of the light-emitting element 2. The light emitting element 2 is configured by a PN junction light emitting diode. The light emitting element 2 includes a p-type semiconductor 2a, an n-type semiconductor 2b, an anode electrode 2c made of a transparent electrode, and a cathode electrode 2d. The light-emitting element 2 emits near-infrared light having a specific wavelength λ according to a forward current that is a driving signal from a thin film transistor described later.

  FIG. 2B is a cross-sectional view of the light receiving element 3. The light receiving element 3 is formed on the surface of the n-type semiconductor 3a, the p-type semiconductor 3b formed on the surface of the n-type semiconductor 3a, the n-type semiconductor 3c formed on the surface of the p-type semiconductor 3b, and the surface of the p-type semiconductor 3b. It comprises a transparent gate electrode 3d, a transparent source electrode 3e formed on the surface of the n-type semiconductor 3c, and a transparent drain electrode 3f formed on the surface (the lower surface in the figure) of the n-type semiconductor 3a.

  FIG. 2C is a cross-sectional view of the optical semiconductor device. The transparent electrode layer 7 and the electrode layer 8 formed on the surface 1a of the lens 1 so as to sandwich the semiconductor layer 6 and other semiconductor layers and electrode layers (not shown). In addition, a thin film transistor (TFT) including a driving circuit of the light emitting element 2 and an amplifying circuit of the light receiving element 3 and a storage circuit and the like described later are formed. The method of manufacturing a TFT follows a conventional technique, and for example, refer to the detailed description of Japanese Patent Application Laid-Open No. 2008-288424 and FIGS.

  FIG. 3 is a cross-sectional view of the lens 1 having both surfaces formed of curved surfaces. As in the case of FIG. 1B, the light emitting element 2 and the light receiving element 3 are formed on one surface. Although not shown, a TFT including the light emitting element 2 and the light receiving element 3 is formed. Forming the light emitting element 2, the light receiving element 3, and the TFT on such a curved surface requires higher technology and cost than forming the light emitting element 2, the light receiving element 3, and the TFT, but has an advantage that the refractive index of light can be increased. Also in this case, a part of the light beam emitted from the light emitting element 2 to the blood vessel 400 is absorbed by the blood in the blood vessel 400, a part of the light beam passes, and the rest is reflected and received by the light receiving element 3.

Next, a blood glucose level measuring apparatus using an optical semiconductor device composed of 721 optical units (lens 1, light emitting element 2, light receiving element 3, and semiconductor circuit) will be described.
FIG. 4 is a diagram showing a wristwatch-type blood sugar level measuring device 11 according to the first embodiment. In FIG. 4A, a display unit 13 provided on one surface of a main body 12 of the blood sugar level measuring device 11, and an analog clock 14 displayed on the display unit 13 (this is a “touch switch”, which will be described later). ), A belt 15, a stretchable belt member 16, and hook switches 12 g (1) and hinges 12 (2) provided at both ends of the main body 12 (these will also be described later). Note that the entire belt 15 may be made of a stretchable material.

  As shown in FIG. 4B, an optical semiconductor device 12a including a measurement surface (that is, the lens 1 in FIG. 1) is formed on the back surface of the main body 12 opposite to the display unit 13. However, a protective layer is formed on the surface of the lens 1 with a transparent plate. Hereinafter, the outer surface of the lens 1 including the protective layer is also referred to as a measurement surface 1.

  FIG. 5 is a diagram showing a configuration of an electronic circuit housed in the main body 12b and the optical semiconductor device 12a of the blood sugar level measuring device 11. In FIG. 5A, the main body 12b includes a display unit 13, an operation unit 14 including a touch switch, and a clock unit 31. The optical semiconductor device 12a includes the measuring unit 1, the control unit 30, the communication unit 32, and a BATT (battery) 35a. The measurement unit 1 includes a light emitting element 2 and a light receiving element 3 and performs signal processing such as amplification processing by converting a light signal received by the driving circuit 33 and the light receiving element 3 that drive the light emitting element 2 into an electric signal. The receiving circuit 34 is connected. The light receiving circuit 34 of each optical unit further includes an amplification circuit 341 and an A / D conversion circuit 342 that converts an analog signal into a digital signal, as shown in FIG.

  The drive circuit 33 causes the 721 light emitting elements 2 to emit light sequentially or selectively according to a control signal from the control unit 30. In the present embodiment, 721 light emitting elements 2 and light receiving elements 3 may be classified into groups. Each group may emit and receive near infrared rays of different wavelengths. In the embodiment of the present invention, a single wavelength λ is applied.

  The communication unit 32 uses Bluetooth (registered trademark), which is a short-distance communication that is widely used for personal computers, mobile terminals (smartphones, etc.), home electric appliances, and the like, and communicates information on blood glucose measurement with the personal computers and mobile terminals. Send and receive between Details will be described later.

  The control circuit 30 has a CPU 301 for controlling the whole blood glucose level measuring device 11, an SRAM 302 backed up by an internal battery (not shown), a rewritable nonvolatile EEPROM 303, and an internal bus connecting these. Although not shown, a memory (for example, a cache memory in the CPU) for temporarily storing data to be processed is provided inside the CPU 301.

  Although details will be described later, in FIG. 5A, the optical semiconductor device 12a is detachably attached to the main body 12 by a hook (12g (1) in FIG. 4) and a hinge (12g (2) in FIG. 4). ing. Therefore, both are connected by the connector. The power of the battery 35a is supplied to the main body 12b by the connector, but the main body 12b may be provided with the battery 35b.

  FIG. 5C is a diagram showing the internal configuration of the SRAM 302. The storage area of the SRAM 302 includes a first storage area 302a, a second storage area 302b, and other storage areas.

  The first storage area stores an array C {p, q}, an array E {j, k}, and blood sugar level data. Each array will be described later.

  The second storage area 302b stores correspondence data between the intensity of the electric signal obtained from the light receiving circuit 34 and the blood glucose level. The correspondence data is written in the EEPROM 303 in advance when the blood sugar level measuring device 11 is manufactured.

  In the manufacture of the blood sugar level measuring device 11, the corresponding data analyzed by various studies and clinical trials is written into the EEPROM 303. Therefore, the correspondence between the intensity of the electric signal obtained from the light receiving circuit 34 and the blood sugar level is highly accurate. However, this does not guarantee the correspondence among all persons, so that in the process of using the blood sugar level measuring device 11, each person can be appropriately corrected in accordance with his or her individuality. This will be further described below.

  The CPU 301 loads the control program from the EEPROM 303 into the internal cache memory and loads the corresponding data into the second storage area 302b of the SRAM 302 at the initialization when the power is turned on. When the corresponding data in the SRAM 302 is corrected, the corresponding data in the EEPROM 303 is appropriately rewritten with the corrected data.

  Next, the operation and operation of the blood sugar level measuring device 11 will be described with reference to FIGS. The CPU 301 of the control unit 30 detects an ON operation of the touch switch 14 of the display unit 13 according to the control program loaded from the EEPRM 302, and executes a process according to the operation.

  Although details will be described later, the CPU 301 includes at least one of an estimating unit for estimating the position of the blood vessel in the measurement target (specifically, the wrist) close to the lens substrate, and at least one of the blood vessel positions estimated by the estimating unit. A calculation unit that determines the range of the unit by calculation, determines the blood glucose level in the determined range as the blood glucose level to be measured, and displays the blood glucose level on the display unit 13.

6 to 9 are flowcharts showing the operation of the blood sugar level detection process executed by the CPU 301.
In the initialization in the main flow (not shown), the CPU 301 loads the corresponding data previously stored in the EEPRM 302 into the SRAM 302 and prepares for realizing a quick processing speed.

  In FIG. 6A, the CPU 301 first performs clock display and displays time on the display unit 13 (step S101). The clock display performs digital display and analog display as shown in FIG. 4A. As described above, the area of the analog display is the icon 14 constituting the touch switch.

  The CPU 301 determines whether or not the icon 14 has been turned on (step S102). When it is determined that the icon 14 has been turned on (step S102; YES), the menu screen is displayed on the display unit 13 (step S103). FIG. 10 shows an example of the menu screen. On the menu screen, a selection candidate icon 13a, an OK (OK) icon 13b, and a switching (cyclic) icon 13c are displayed.

  That is, in FIG. 10 (A), the selection candidate icon 13a of "blood glucose measurement" is displayed. The user turns on either the decision icon 13b or the switching icon 13c.

  The CPU 301 determines whether the blood sugar level measurement is on, that is, whether the determination icon 13b is on (step S104). When it is determined that the blood sugar level measurement has been turned on (step S104; YES), a blood sugar level measurement process is executed (step S105a). On the other hand, when the blood sugar level measurement is not on, that is, when the switching icon 13c is turned on (step S104; NO), the CPU 301 displays the screen of the “meal start” selection candidate icon 13a shown in FIG. I do.

  The CPU 301 determines whether or not the meal start icon 13a has been selected (step S106). When it is determined that the meal start icon 13a has been selected (step S106; YES), the CPU 301 executes a blood sugar level measurement process (step S105b). Further, the flag F is set to "1" and the time is set (step S107).

  For example, when a meal start is selected at 0: 5 pm, intervals of 30 minutes elapse, 0:35 pm, 13: 5, 13:35, 14: 5, and 14: 6 ( Set the last time). The clock unit 31 illustrated in FIG. 5A inputs a timer interrupt to the CPU 301 every elapse of one second, for example, and includes date and time and time information therein. For example, at 14:05, "2017; 07; 03; 14; 05; 00" is input.

  When the meal start icon 13a is not selected, that is, when the switching icon 13c is turned on (step S106; NO), the CPU 301 displays a screen of a new selection candidate on the display unit 13 and the other icon switches are switched. It is determined whether the switch has been turned on (step S108). When another icon switch is turned on (step S108; YES), the CPU 301 executes another menu process related to the selection (step S109).

  Thus, the CPU 301 switches the contents of the selection candidates on the menu screen every time the switching icon 13c is turned on. Other selection candidates include "data input", "blood collection start", "measurement mode", "history information", and the like.

  When the data input is selected, the CPU 301 displays the blood sugar level to be corrected and / or the input space of the HbA1C and the numeric keypad.

  When the start of blood collection is selected, the CPU 301 measures the blood glucose level at the selected time and stores the measurement result together with the time information in the blood glucose level data area of the first storage area 302a of the SRAM 302. As a result, it is possible to compare the blood sugar level obtained by collecting blood at the same time with the blood sugar level measured by the blood sugar level measuring device. By this comparison, the accuracy (error) of the corresponding data stored in the EEPROM 303 can be determined. The details of the comparison between the blood glucose level obtained by the blood collection and the blood glucose level by the blood glucose level measuring device will be further described later.

  When the measurement mode is selected, the CPU 301 further displays a screen of the measurement mode on the display unit 13. The displayed measurement modes include a “manual measurement mode”, a “continuous measurement mode”, and other measurement modes. The default is the manual measurement mode. When the continuous measurement mode is selected, the CPU 301 starts measurement every time a predetermined time (settable) elapses from that time, and performs measurement continuously until, for example, 24:00 on the next day.

  When the history information is selected, the CPU 301 displays a screen on which a date and time or a period can be specified on the display unit 13. When the date and time or the period is specified, the CPU 301 searches the SRAM 302 and displays past data related to the specification. I do.

  Next, the timer interrupt in FIG. 6B will be described. When a timer interrupt is input from the clock unit 31, the CPU 301 determines whether the flag F is "1" (step S301). When F is “1” (step S301; YES), the CPU 301 determines whether or not the last time has elapsed (step S302).

  If the last time has not elapsed (step S302; NO), it is determined whether or not the measurement time has been reached (step S303). That is, it is determined whether or not the time information from the clock unit 31 matches the time set in step S107. If the times match (step S303; YES). The blood glucose measurement process is executed (Step S105c).

  On the other hand, if the last time has not elapsed (step S302; YES), F is reset to “0” and the set time is cleared (step S304).

  If F is not “1” (step S301; NO), if it is not the measurement time (step S303; NO), after executing the blood sugar level measurement process (step S105), or reset and set F to “0” After clearing the time (step S304), the timer interrupt ends.

  In FIG. 6A, after the blood sugar level measurement process (step S105a), F is set to “1” and the time is set (step S107), or when another menu process (step S109) ends. The CPU 301 performs the clock display in step S101.

  FIG. 7 is a flowchart of the blood glucose measurement process in step S105a, S105b, or S105c of FIG. The CPU 301 drives the 720 optical units sequentially (sequentially) to acquire an electric signal corresponding to the intensity of the received light.

  FIG. 11 is a diagram showing an arrangement of 721 optical units. In this figure, regular hexagons H1, H2, Hn-1, and Hn indicated by dotted lines are frames connecting the centers of optical units that expand in the radial direction as a multiple of 6, and are represented by a variable f (hereinafter, referred to as a variable f). "Hf"). The optical unit of each Hf is represented by a variable s, and is designated clockwise (or counterclockwise) by Hf (s). Here, s = 1, 2, 3,... 15,.

  A semiconductor circuit including each lens 1 of the lens group, each light emitting element 2 corresponding to each lens 1 and a driving circuit 33 for each light emitting element, each light receiving element 3 corresponding to each lens 1 and amplification of an electric signal from the light receiving element 3 The semiconductor circuit including the circuit 341 and the A / D conversion circuit 342 constitutes a honeycomb-shaped optical unit, and a plurality of regular hexagonal frames are radially spread around one optical unit located at the center of the lens substrate. Of optical units are located at respective centers on each frame.

Each honeycomb-shaped optical unit on the lens substrate is uniquely designated by the following coordinates (defined as Honeycomb Coordinates) with one optical unit H0 located at the center as the origin.
Hf (1-6f)
Here, f is an integer of 1 or more, and 1 to 2f are specified in a clockwise (or counterclockwise) order. Then, the light emission processing and the light reception processing are performed in the designated order. Generally, circular coordinates represented by a radius and an angle are well known, but the honeycomb coordinates are discrete digital coordinates. Further, it is characterized in that the maximum value of the variable s of each Hf (s) is always a multiple “6f” of “6”.

  For example, in the case of H1, each optical unit is designated by H1 (1), H1 (2), H1 (3), H1 (4), H1 (5), and H1 (6). Note that H1 (1) indicates the uppermost optical unit and proceeds clockwise (or counterclockwise) (incremented). In the case of H2, each optical unit is designated by H2 (1) and H2 (2) to H2 (12). In the case of Hn-1, each optical unit is designated by Hn-1 (1), Hn-1 (2) to Hn-1 (6f), and in the case of Hn, Hn (1), Hn Each optical unit is designated by (2) to Hn (6f). Each optical unit is driven in this order. That is, since the light emitting elements 2 of all the optical units are not driven at the same time, the power required for light emission is small.

  In this embodiment, since n = 15, in the case of H15, each optical unit is designated by H15 (1), H15 (2), and H15 (90). As described above, since the number of optical units differs for each Hf, it is inconvenient for the CPU 301 to store and process the data of the electric signal obtained from each optical address as a table. For this reason, it is divided into a sequence of a fixed length and converted into a usual so-called matrix type array C {p, q}.

  FIG. 12 shows an array C {p, q} of the first storage area of the SRAM 302 shown in FIG. The CPU 301 executes the drive processing sequence H1 (1), H1 (2), H1 (3),... Hf (1), Hf (2), Hf (3),. 1), Hn (2), Hn (3),..., Hn (6n) are stored in the array C {p, q}. Therefore, any Hf (s) uniquely corresponds to the array C {p, q}.

  Therefore, the CPU 301 sets the variable p of the array to 1 (step S201), and sets the variable q to 1 (step S202). Then, the CPU 301 repeats the processing of steps S203 to S209 while incrementing the variables p and q.

  The CPU 301 performs a light emission process at C {p, q} (step S203), and performs a light reception process at C {p, q} (step S204). That is, the CPU 301 performs the light emission processing and the light reception processing at Hf (s) uniquely corresponding to C {p, q}.

  Next, the CPU 301 refers to the corresponding data in the SRAM 302 (step S205). The CPU 301 calculates a blood sugar level by referring to the corresponding data (step S206). Here, the expression “calculation” is used because the CPU 301 determines that the intensity of the electric signal obtained by the light receiving process, that is, the blood glucose level by voltage calculation or the current value does not completely correspond to the blood glucose level by the proportional calculation. Is calculated.

  Next, the CPU 301 stores the calculated blood sugar level in the array C {p, q} of the SRAM 302 (step S207). Next, the CPU 301 increments the variable q (step S208). That is, the next column is specified. Then, the CPU 301 determines whether or not the variable q has exceeded the value of the last q (step S209). For example, in the present embodiment, when 720 optical units are arranged in 24 columns and 30 rows, the CPU 301 determines whether or not the incremented value of q exceeds 24.

  If the value of q does not exceed the value of the last q (step S209; NO), the CPU 301 proceeds to step S203 and repeats the processing up to step S209.

  When the incremented value of q exceeds 24 (step S209; YES), the CPU 301 increments the variable p (step S210). That is, the next line is specified. Then, the CPU 301 determines whether or not the variable p has exceeded the last p (step S211). For example, the CPU 301 determines whether the value of p has exceeded 30.

  If the value of p does not exceed the value of the last p (step S211; NO), the CPU 301 proceeds to step S202, sets the variable q of the specified row to 1, and performs the processing up to step S211. repeat.

  If the value of p exceeds the last value of p (step S211; YES), the blood glucose level corresponding to the intensity of the electric signal from all the optical units is stored in the first storage of the SRAM 302 shown in FIG. It is stored in the area 302a. FIG. 13 shows the position of the blood vessel 400 before estimation by a two-dot chain line.

  Next, the operation of the CPU 301 for estimating the position of a blood vessel will be described. 8, the CPU 301 sets variables p and j to 1 (step S212), and sets variables q and k to 1 (step S213). This is a process of setting the variables of the array C {p, q} and the variables of the array E {j, k} for estimating the position of the blood vessel in FIG.

  While incrementing the values of the variables q, k, p, and j, the CPU 301 refers to the array of FIG. 12 and extracts data for estimating the position of a blood vessel. That is, CPU 301 refers to array C {p, q} (step S214) and determines whether the blood sugar level of C {p, q} is greater than threshold th1 (step S215). If the blood sugar level is greater than th1 (step S215; YES), CPU 301 copies the data of C {p, q} to array E {j, k} (step S216).

  Next, the CPU 301 increments the value of the variable k (step S217). Further, the value of the variable q is incremented (step S218). On the other hand, if the blood sugar level is equal to or less than th1 (step S215; NO), the variable k is not incremented, but only the variable q is incremented (step S218). This is because there is no need to increment the storage area of the current array E {j, k} because it is still empty.

  After incrementing the value of q in step S218, the CPU 301 determines whether the value of q has exceeded the value of the last q (step S219). If the value does not exceed the last value of q (step S219; NO), the CPU 301 proceeds to step S214 and repeats the processing up to step S219.

  If the incremented q value exceeds the last q value in step S218 (step S219; YES), the CPU 301 determines whether or not all q values of the current p row are equal to or smaller than the threshold th1. It is determined (step S220).

  When at least one value of q is larger than th1, that is, when it is estimated that the value is within the range of the blood vessel (step S220; NO), to specify the next row of the array E {j, k}, The value of j is incremented (step S221). On the other hand, when all the values of q in the p-th row are equal to or smaller than the threshold th1 (step S220; YES), the value of j is incremented because the j-th row of the current array E {j, k} is blank. No need.

  Therefore, when all the values of q in the p-th row are equal to or smaller than the threshold th1, or after the value of j is incremented in step S221, the CPU 301 increments the value of p to obtain the array C {p, q}. Is specified (step S222). Thereafter, the CPU 301 determines whether the incremented value of p has exceeded the value of the last p (step S223).

  If the value does not exceed the last value of p (step S223; NO), the CPU 301 proceeds to step S213 and repeats the processing up to step S223. If the last value of p has been exceeded (step S223; YES), the reference to the array C {p, q} in FIG. 12 ends, and an array E {j, k} for estimating the position of the blood vessel is created. Has ended.

  FIG. 14 shows the estimation result of the array E {j, k} that has been created, that is, the position of the blood vessel. FIG. 15A shows the position of the blood vessel 400 after the estimation by cross-hatching.

  Next, the CPU 301 refers to the array E {j, k} in FIG. 9 (step S224). The CPU 301 sets the value of the variable j that specifies the row of the array E {j, k} to 1 (step S225), and sets the value of k that specifies the column to 1 (step S226). Then, the CPU 301 extracts, from the array E {j, k} that is the estimation result of the position of the blood vessel, data having a larger blood sugar level in order to determine the range of the blood vessel with high measurement accuracy.

  That is, the CPU 301 determines whether the blood sugar level of E {j, k} is greater than a predetermined threshold th2 (th2> th1) (step S227). Then, when the blood sugar level is larger than the threshold th2 (step S227; YES), the CPU 301 maps the data of E {j, k} (step S228).

  That is, the CPU 301 converts the data of E {j, k} into the array Hf (s) of the blood vessel position of the estimation result shown in FIG. Check. The mapped data is stored in a cache memory (not shown) inside the CPU 301. This mapping expands the array Hf (s) in the VRAM in the cache memory, for example.

  Thereafter, or when the blood sugar level is equal to or smaller than the threshold th2 (step S227; NO), the CPU 301 increments the value of k (step S229). Then, CPU 301 determines whether or not the data of E {j, k} in the designated column is end (or NULL) (step S230).

  That is, CPU 301 determines whether or not there is data in a column subsequent to the designated column k. When data is stored in the designated column k (step S230; NO), the CPU 301 proceeds to step S227 and repeats the processing up to step S230.

  If there is no data in the column subsequent to the specified column k (step S230; YES), the CPU 301 increments the value of the variable j specifying the row of the array E {j, k} (step S231). Then, the CPU 301 determines whether or not the array E {j, k} of the specified row j is NULL (data is not present in all columns of the row) (step S232).

  If the array E {j, k} of the row j is not NULL (step S232; NO), the CPU 301 proceeds to step S226 and repeats the processing up to step S232.

  If the array E {j, k} of the row j is NULL (step S232; YES), since the subsequent rows are also NULL, the reference for all the data in FIG. 14 has been completed. As a result, as shown in FIG. 15B, the pattern of the blood sugar level exceeding the threshold value th2 is shown in black.

  This pattern is substantially straight and extends continuously in the direction of the arrow across the entire optical unit 10. As a result, the CPU 301 determines that this pattern is in a range where the measurement accuracy is high.

  Therefore, the CPU 301 calculates the blood sugar level based on the mapping (step S233), and stores the calculated blood sugar level in the SRAM (step S234). In this case, the calculation method may be to calculate the average value of all the data of the blood sugar level exceeding the threshold value th2, and may further extract the data exceeding the predetermined threshold value th3 and calculate the average value. , May be calculated based on the maximum blood sugar level.

  Alternatively, it may be calculated based on a known algorithm that also considers the data of the array C {p, q} shown in FIG. 12 and / or the data of the array E {j, k} shown in FIG. . In any case, the method of estimating and determining the position of the blood vessel according to the present embodiment is applied.

  FIG. 16 shows blood glucose level data stored in the first area 302a of the SRAM. Here, blood sugar levels for 90 days are stored for each date. When storing a new blood glucose level here, the oldest data is deleted and the latest data is stored. That is, data push processing is performed.

  After storing the new blood sugar level data, the CPU 301 calculates the average value (Average) of the blood sugar level data for 90 days and calculates HbA1C as shown in FIG. 16 (step S235). .

  Next, the CPU 301 displays the blood glucose level (mg / dL) stored in the SRAM and the calculated HbA1C (%) on the display unit 13 together with the date and time information (step S236).

  Next, the CPU 301 deletes the data of C {p, q} (FIG. 12) and the data of E {j, k} (FIG. 14) in the first storage area of the SRAM (step S237). Then, the CPU 301 proceeds to step S101 in FIG. 6 and displays a clock.

  When a blood glucose level is measured by blood collection at a medical institution, the user turns on “blood glucose level measurement” 13a (touch switch) shown in FIG. 10A immediately before or immediately after blood collection. That is, the blood glucose level is measured by this device almost simultaneously with the blood collection, and the difference between the two is confirmed.

  FIG. 17 and FIG. 18 show the measurement result by blood collection and the measurement result by the device (simultaneous measurement result). When the two are compared, a slight difference is seen in the blood glucose level and HbA1C.

  For this reason, the user selects data input from the menu screen and corrects the measurement result shown in FIG. 18 according to the measurement result of blood collection. In this case, it is assumed that the measurement result obtained by blood collection is a correct value. The present embodiment is not concerned with this assumption.

  FIG. 19 shows data correction performed by the blood sugar level measuring device 11 in the present embodiment. Since the data correction using the touch switch on the display unit 13 of the device 11 is too narrow to display all the numeric keys for inputting numerical values, four numerical input icons are displayed, and the numerical values are cyclically displayed by touch operation. Is changed.

  In FIG. 19, when the ten-key whose default is "3" is operated twice, the numerical value "5" blinks as an input candidate. Here, when the “OK” icon is operated, the numerical value “5” is determined as the correction data.

  This data correction operation can also be performed by an external device, for example, a mobile terminal or a personal computer. In that case, the communication setting shown in FIG. 10C is selected to establish a wireless communication line with an external device.

  FIG. 20 shows a case where a wireless communication line is established between the device 11 and the portable terminal 100 or the personal computer 200 in the present embodiment. In this case, the data can be corrected by the touch screen 101 of the mobile terminal 100 (for example, a smartphone) having a touch screen or a keyboard larger than the touch screen of the device 11 or the keyboard 201 of the personal computer 200.

  FIG. 21 is a plan view of the optical semiconductor device 12a removed from the main body. Although the spring 12e is fixed to the main body, it is superimposed on this figure to show the positional relationship with the optical semiconductor device 12a. As shown in FIG. 21, when mounted on the main body side, the optical semiconductor device 12a includes connectors 12h (1) and 12h (2) for connecting to the main body side.

  FIGS. 22A and 22B are cross-sectional views taken along line XX of FIG. 21 and illustrating the function of the spring 12e. 22A and 22B, the optical semiconductor device 12a is attached to the main body 12 so as to be displaceable in the direction of the arrow in the figure. The spring 12e has one end fixed to the upper main body 12b and the other end fixed to the flat plate 12d in a space formed by the upper main body 12b and the lower main body 12c.

  FIG. 22A shows a state in which the spring 12e presses the flat plate 12d downward. As a result, the optical semiconductor device 12a is located at the lowermost part of the space. Therefore, the connector 12h (1) contacts the connector 12h (3) of the lower main body 12c. In this state, if the band of the device 11 is loosely tightened, the optical semiconductor device 12a may not be in close contact with the surface of the wrist.

  On the other hand, FIG. 22B shows a state in which the optical semiconductor device 12a pushes up the spring 12e from below. That is, the tightness of the band of the apparatus 11 is good, and the optical semiconductor device 12a and the surface of the wrist are in close contact. In this case, the connector 12h (1) separates from the connector 12h (3) of the lower body 12c.

  FIG. 23 shows an equivalent circuit of the switch SW1 including the connector 12h (1) and the connector 12h (3). The connector 12h (1) is connected to GND via the resistor R1. On the other hand, the connector 12h (3) is connected to the power supply Vcc. Therefore, in the case of FIG. 22A, SW1 is closed (ON state). Therefore, a high-level signal is supplied to the input port of the CPU 301 in FIG. On the other hand, in the case of FIG. 22B, SW1 is open (OFF state). Therefore, a low-level signal is supplied to the input port of the CPU 301.

  The CPU 301 can determine whether or not the optical semiconductor device 12a is in close contact with the surface of the wrist based on the signal supplied to the input port. If the band is loose, the CPU 301 notifies the user of a warning message.

  FIG. 24 shows a state where the optical semiconductor device 12a is not in close contact with the surface of the wrist (not shown). In FIG. 24A, if the band 15 is loosely tightened, a message “Please tighten the band more” is displayed on the display unit 13 as shown in FIG. 24B.

  Although not shown in the drawing, when the band 15 is properly tightened, that is, when it is detected that the SW1 in FIG. 24 is in the OFF state, a message indicating that the band 15 is properly tightened is displayed. I do.

  The connector 12h (2) in FIG. 21 is a connector for connecting the optical semiconductor device 12a to the main body 12b in FIG. 5, and as shown in FIGS. 22A and 22B, the optical semiconductor device 12a Is connected to the connector 12f (1) of the main body (upper) 12b or the connector 12f (2) of the lower body 12c.

  As described above, according to the present embodiment, it is not necessary to finely adjust the optical axis of the light emitting element and the light receiving element, and the conditions restrained by the position of the blood vessel of the user are alleviated manually and It is possible to automatically measure a stable blood sugar level.

  According to the present embodiment, when the user performs manual measurement, the display unit 13, that is, the touch switch 14 is pressed with a finger, so that the optical semiconductor device 12 a comes into close contact with the user's wrist. Even in this case, it is possible to determine whether or not the optical semiconductor device 12a is in close contact with the surface of the user's wrist, so that an appropriate message is notified to the user.

  As a modification of the present embodiment, a connector may be provided at the top of the space of the upper main body 12b. When the band is too tight and the connector 12h (1) of the optical semiconductor device 12a comes into contact with this connector, the display unit 13 displays "Please loosen the band a little. It will hurt your wrist." A message may be displayed.

  Next, a second embodiment of the present invention will be described. In the second embodiment, not only the light receiving element 3 of the optical unit but also the light receiving elements 3 of a plurality of optical units surrounding the optical unit reflect the light emitted by the light emitting element 2 of one optical unit. Receives light simultaneously.

  For this purpose, in the present embodiment, coordinate conversion processing is performed on the optical unit of the honeycomb coordinates. Coordinate conversion is performed on Hi (s) (i = 0 to nm; s = 1 to 6i) of an arbitrary optical unit to generate converted honeycomb coordinates (TH0, TH1, TH2,...). Here, n is the maximum value of the frame f, and in this embodiment, n = 15.

  FIG. 25A shows a case where 19 optical units simultaneously receive reflected light. As shown in FIG. 25A, a converted honeycomb coordinate centered on an arbitrary optical unit Hi (origin optical unit) is created. This is defined as a "floating origin system". The coordinate conversion table (not shown) is stored in the EEPROM 303 in FIG.

  The reflected light emitted from the light emitting element of TH0 and reflected by the blood flowing through the measurement object, that is, the blood vessel of the user, is simultaneously received by the light receiving elements of TH0, TH1, and TH2. Therefore, even if the reflected light spreads, the light collection rate increases. In this floating origin system, as shown in FIG. 25B, a shallow groove 12a (3) is formed in a lens barrel 12a (2) of an optical semiconductor device 12a, and an interchangeable lens 12a (EX) is mounted. A configuration that can be used may be adopted. The interchangeable lens 12a (EX) may be, for example, an aspheric lens that converts the spread reflected light into parallel light.

  As described above, since an arbitrary optical unit is converted into an origin unit and is constituted by a plurality of optical units surrounding the origin unit, the peripheral portion of the lens substrate cannot be used. That is, it is necessary to satisfy the boundary condition. The reason why Hi (s) (i = 0 to nm; s = 1 to 6i) of an arbitrary optical unit is set is to exclude frames from the maximum frame n to the frame m. In the case of the present embodiment, m = 2, and H0 to H13 (15-2) can be candidates for the origin optical unit. Therefore, the number of optical units that can be used in the floating origin system is 78.

  FIG. 25C shows the configuration of the addition circuit 304 and the selection circuit 305 necessary for the floating origin system. The CPU 301 outputs to the selection circuit 305 a command for selecting the honeycomb coordinates of the plurality of optical units in the floating origin system. As a result, the electric signal added by the adding circuit 304 is input to the CPU 301.

  In this case, the adder circuit 304 is configured not by hardware but by software. Therefore, the CPU 301 can select the light receiving circuit 34 of only one honeycomb coordinate by the selection circuit 305. As a result, if the configuration of the adding circuit 304 is skipped by software, the configuration becomes the same as that of the first embodiment. That is, there is no difference in hardware between the first embodiment and the second embodiment, and the first embodiment and the second embodiment are realized by transition of the operation mode by software.

  In the present embodiment, the floating origin system is constituted by 19 optical units selected from 78 optical units, but the present invention is not limited to this. For example, the addition circuit 304 and the selection circuit 305 can be configured by a programmable logic circuit (PLC) and can be configured by any combination.

  As described above, according to the present embodiment, even when the reflected light is spread by the floating origin system, the light collection rate can be increased.

  Next, a third embodiment of the present invention will be described with reference to FIGS. In the present embodiment, the blood sugar level is measured in cooperation with the optical semiconductor device 12a separated from the main body 12 of the apparatus 11 and the portable terminal.

  As described above, when the optical semiconductor device 12a is separated from the main body 12b, the pressing operation of the hook switch 12g (1) and the rotating operation of the hinge 12g (2) are performed. In this case, when the optical semiconductor device 12a is separated from the device 11, the SW1 is turned off as shown in FIG. 23, and the connection with the display unit 13 (touch switch 14) and the clock unit 31 in FIG. There is no problem with hardware. However, the routine of detecting band tightness and displaying a message needs to be "skipped" by software. Therefore, for example, when there is no input of time information from the clock unit 31, the CPU 301 needs to perform this skip processing.

  The optical semiconductor device 12a separated from the main body of the apparatus 11 functions as an independent device as described below.

  26A and 26B show a case 300 for a portable terminal (smartphone), FIG. 26A is a plan view thereof, and FIG. 26B is a cross-sectional view taken along line YY of FIG. 6A. In this figure, a semicircular concave portion 302 for accommodating the optical semiconductor device 12a is formed adjacent to a space for accommodating the portable terminal, and a circular hole 303 is formed.

  FIG. 27 shows a case where the mobile terminal 100 and the optical semiconductor device 12a are mounted on the case 300. The mobile terminal 100 and the optical semiconductor device 12a are wirelessly connected by Bluetooth (registered trademark) of short-range wireless communication. That is, when the optical semiconductor device 12a is mounted on the apparatus 11, the display section 101 (touch switch 14) and the clock section 31 shown in FIG. The switch 101a) and the clock function are used.

  Therefore, the application software for the device 11 is installed in the mobile terminal 100 in advance, or is installed after the application.

  FIG. 27A shows the display unit 101 of the portable terminal 100, and FIG. 27B shows the measurement surface 1 of the optical semiconductor device 12a. Since the display unit 101 of the mobile terminal 100 is larger than the display unit 13 of the device 11, the menu 101a of the selection candidates can be displayed.

  The mobile terminal 100 can activate its own application at any time and transition to the blood glucose measurement mode. In the blood glucose measurement mode, the apparatus operates according to the control of the CPU 301 of the optical semiconductor device 12a instead of its own control unit. However, in the blood glucose measurement mode, as shown in FIG. 27A, the icon of the touch switch 101b for the disconnection process is always displayed, and the operation mode can be shifted to the original operation mode of the portable terminal 100.

  The measurement surface 1 is configured to slightly protrude from the surface of the case 300. Therefore, the user operates the portable terminal 100 with the other hand in a state in which the measurement surface 1 is in close contact with the palm of one hand, and the palm of the palm in which many blood vessels in close contact with the measurement surface 1 are gathered. Blood sugar levels can be detected.

  As described above, according to the present embodiment, by combining the optical semiconductor device 12a as an independent electronic component and the portable terminal 100, the blood glucose level can be measured at any part of the body of the user. The degree of freedom and convenience are improved.

  The first to third embodiments are merely exemplary embodiments of the present invention, and the present invention is not limited to these embodiments. Modifications and modified embodiments that can be easily conceived by those skilled in the art based on the above embodiments are also included in the scope of the present invention unless departing from the gist of the claims appended to this specification.

  For example, not all of the lens substrate is constituted by an optical unit, but a part of the lens substrate is constituted by a CCD (Cage Coupled Device) type or a MOS (Metal Oxide Semiconductor) type image sensor. Is also good. With the manufacturing technology as of 2017, an image sensor having 20,000 pixels can be realized for one optical unit area.

  For example, when an optical semiconductor device is combined with a portable terminal, an area corresponding to 18 optical units surrounding one optical unit is displayed on a display unit while displaying the position of a blood vessel by an image sensor of 380,000 pixels. Blood glucose can be measured.

  Further, when the optical semiconductor device is combined with a portable terminal, the degree of freedom of the shape of the lens barrel of the interchangeable lens mounted on the optical semiconductor device is increased. Therefore, it is possible to measure the blood sugar level using various optical systems.

  Further, when the optical semiconductor device is combined with a portable terminal, an interchangeable lens having a zooming function can be provided, so that the sugar content of food can be measured at a food counter such as a supermarket. Therefore, it is extremely effective for diabetics or preliminary users who are on a carbohydrate-restricted diet.

REFERENCE SIGNS LIST 1 lens 2 light emitting element 3 light receiving element 11 blood sugar level measuring device 12 main body 12 a optical semiconductor device 13 display unit 33 driving circuit 34 light receiving circuit 301 CPU
302 SRAM

Claims (2)

A smartphone that has a display unit and an operation unit configured by icons displayed on the display unit, and is provided for blood glucose measurement,
A case capable of accommodating the smartphone,
An optical device that is mounted in a recess formed inside the case and has a measurement surface that protrudes outside the case from a hole formed in the center of the recess, and is sandwiched between the contained smartphone and the case. A semiconductor device;
The optical semiconductor device,
A lens substrate on which a plurality of lens groups for converging light passing along the optical axis are arranged,
On one surface of the lens substrate that is perpendicular to the direction of the optical axis, light of a specific wavelength that is formed corresponding to each of the plurality of lenses and whose absorptance increases according to the blood glucose level, In response to a predetermined command input from the operation unit, a plurality of light emitting elements that sequentially emit light and transmit the corresponding lens,
The one surface of the lens substrate is formed corresponding to each of the plurality of lenses, surrounds the light emitting element by an inner edge close to an outer edge of the light emitting element, and has an outer edge outside the inner edge and the inner edge. In a region defined by and a plurality of light receiving elements that receive the light of the wavelength that is transmitted and incident through the corresponding lens and generate an electric signal indicating an intensity value of the light,
A storage unit that stores correspondence data indicating a correspondence relationship between a light intensity value and a blood glucose level indicated by an electric signal generated by the light receiving element,
A calculating unit that calculates a blood glucose level of a measurement object close to the lens substrate based on a blood glucose level of the corresponding data and an intensity value of light indicated by an electric signal generated from a light receiving element surrounding the light emitting element that sequentially emits light, Blood glucose level measuring device.   The smartphone and the optical semiconductor device perform short-range wireless communication, and the optical semiconductor device transmits the blood glucose level of the measurement target calculated according to the measurement instruction received from the smartphone to the smartphone. Blood glucose measurement device.

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