JP2009031118A - Blood test device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To solve the problem wherein the mounting of a sensor part by a patient whose sight has deteriorated is lowered is difficult. <P>SOLUTION: This blood examination device is constituted of a circular sensor part 14 and its body part 12, provided with a mounting part 12a, to which the sensor part 14 is fitted freely detachably and having a built-in electric circuit part 31 connected to the sensor part 14. The sensor part 14 has a plurality of the detection electrodes 25-29 provided to a sensor 15 and a plurality of the electrode terminals 25b-29b, respectively led out of the detection electrodes 25-29 and keeps the body part 12, equipped with the connectors 13 (13a-13e), respectively connected to the electrode terminals 25b-29b. At least the electrode terminals 25b-29b or the connectors 13 (13a-13e) are formed into a concentric circular shape or a cylindrical shape. Accordingly, the desired purpose is obtained. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a blood test apparatus for measuring a blood sugar level or the like.

  A diabetic patient needs to regularly measure a blood glucose level, inject insulin based on the measured blood glucose level, and keep the blood glucose level normal. In order to keep this blood glucose level normal, it is necessary to constantly measure the blood glucose level. For this purpose, a small amount of blood is collected from the fingertip of the patient using a blood test apparatus, and the blood glucose level is measured from the collected blood.

  Hereinafter, a conventional blood test apparatus will be described. As shown in FIG. 18, the conventional blood test apparatus 1 is composed of a main body portion 2 having a mounting portion 2a formed on one side and a sensor portion 3 that is detachably mounted on the mounting portion 2a. The sensor unit 3 includes a holder 3a and a blood sensor (hereinafter referred to as a sensor) 3b mounted in the holder 3a. A plurality of detection electrodes 3c (not shown) are formed on the sensor 3b, and each of these detection electrodes 3c is led to an electrode terminal 3d. By inserting the sensor unit 3 into the mounting unit 2a, these electrode terminals 3d are connected to a plurality of connectors 2c provided at the tip of the mounting unit 2a. The signal of the connector 2 c is connected to an electric circuit unit 4 provided in the main body unit 2.

  In the main body 2, a laser emitting device 5 provided to face the sensor 3 b and a battery 6 for supplying electric power to the laser emitting device 5 and the electric circuit unit 4 are accommodated. Here, the reason that the sensor unit 3 is provided so as to be detachable from the main body unit 2 is that the sensor 3b must be replaced every time the puncture is performed.

  Further, since the signals of the plurality of detection electrodes 3c are associated with each other and guided to the electric circuit unit 4, it is necessary to make the outer shape of the mounting unit 2a and the outer shape of the sensor unit 3 asymmetric. Therefore, for example, as shown in FIG. 19A, the mounting portion 2a is formed with a convex portion 2d, the holder 3a is formed with a concave portion 3e as shown in FIG. 19B, and the convex portion 2d is formed with the concave portion 3e. And then inserted.

  The operation of blood test apparatus 1 configured as described above will be described below. The patient first attaches a new sensor unit 3 to the main body unit 2. In this case, the concave portion 3e formed in the holder 3a is aligned with the convex portion 2d formed in the mounting portion 2a while rotating, and then the sensor portion 3 is inserted into the main body portion 2.

  Next, as shown in FIG. 20, blood test apparatus 1 is held in the right hand, for example, and brought into contact with skin 7 of the left hand. Then, the puncture button 5b shown in FIG. 18 is pressed. Then, the laser beam 5a is emitted from the laser emitting device 5. This laser beam 5a punctures the skin 7. By this puncture, blood 8 exudes from the skin 7. This blood 8 is temporarily stored in a reservoir provided in the sensor 3b. The blood 8 stored in the storage part is detected by the detection electrode 3c, and the blood sugar level is measured by the electric circuit part 4 provided in the main body part 2.

As prior art document information related to the invention of this application, for example, Patent Document 1 is known.
Special Table 2003-52496

  However, in such a conventional blood test apparatus 1 of the related art, the concave portion 3e formed in the holder 3a must be fitted to the convex portion 2d formed in the mounting portion 2a while rotating each time puncture is performed. It is necessary to rotate 360 degrees at the maximum for this fitting. After fitting in this way, the sensor unit 3 must be inserted.

  As described above, the operation of fitting the convex portion 2d and the concave portion 3e and then inserting the convex portion 2d is troublesome even for a normal person. This is even more difficult for patients whose vision has decreased due to diabetes or the like.

  Accordingly, the present invention has been made to solve such problems, and an object thereof is to provide a blood test apparatus in which a sensor unit can be easily inserted.

  In order to achieve this object, in the blood test apparatus of the present invention, at least one electrode terminal or connector is formed in a concentric or cylindrical shape. Thereby, the initial purpose can be achieved.

  As described above, according to the present invention, at least one of the electrode terminals or the connector is formed in a concentric or cylindrical shape, and is formed in a concentric or cylindrical shape. Even if it is inserted from any direction of 360 degrees, the electrode terminal is connected to the corresponding connector only by pressing at the same angle, and the insertion becomes very easy.

  That is, for example, it is not necessary to rotate the position of the convex portion and the concave portion by rotating up to 360 degrees as in the conventional case, and the sensor portion can be easily attached to the main body portion.

  In addition, an electrode terminal only for identification of the electrode terminal is not necessary, and the size and the price can be reduced.

(Embodiment 1)
FIG. 1 is a perspective view of blood test apparatus 11 in the first embodiment. In FIG. 1, reference numeral 12 denotes a main body portion of the blood test apparatus 11, and one of the main body portions 12 is provided with a cylindrical mounting portion 12 a. A plurality of connectors 13 are provided on the surface of the mounting portion 12a. The connector 13 is formed in a ring shape. Reference numeral 34 denotes a display unit provided on the surface of the main body unit 12.

  Reference numeral 14 denotes a circular sensor unit that is detachably mounted to the mounting unit 12a. As shown in FIG. 2, the sensor unit 14 includes a holder 14a and a blood sensor (hereinafter referred to as a sensor) 15 mounted in the holder 14a.

  The cross section of the holder 14a has a bowl shape, and electrode terminals 25b to 29b are formed in a row inside the upper portion 14b. The electrode terminals 25b to 29b are in contact with the connectors 13 (13a to 13e) formed on the mounting portion 12a. The connector 13 is connected to an electric circuit portion 31 (see FIG. 7) provided in the main body portion 12. A positioning concave portion 14c is formed in the vicinity of the upper end of the upper portion 14b, and the positioning concave portion 14c is fitted and positioned with a positioning convex portion 12c formed in the mounting portion 12a. Therefore, it is possible to puncture at a predetermined depth, and the inside of the mounting portion 12a is sealed so that negative pressure cannot escape.

  The lower part 14d has a smaller diameter than the upper part 14b, and the lower part 14d of the second sensor part 14 can be inserted into the upper part 14b of the first sensor part 14. Therefore, the sensor units 14 can be stacked, and can be stored in a small space.

  The upper portion 14b has an inclination that opens upward, and the contact portion 19 in which the connector 13 of the mounting portion 12a is formed has an inclination that narrows downward. The inclination angles are both approximately 15 degrees to facilitate the insertion / extraction of the sensor unit 14 and the contact of the electrodes.

  The lower part 14d of the holder 14a opens downward, and this opening forms a negative pressure chamber 33a. A skin detection sensor 33b is provided at the lower end of the lower portion 14d.

  FIG. 3 is a circuit diagram in the vicinity of the contact portion 19. As shown in FIGS. 2 and 3, the signal of the skin detection sensor 33b is connected to the electrode terminal 14g. The electrode terminal 14g is provided on the extension of the electrode terminals 25b to 29b. The electrode terminal 14g is connected to the electric circuit unit 31 through the connector 13g.

  14f is an electrode terminal for detection of the sensor unit 14 formed on the holder 14a, and the two electrode terminals 14f are short-circuited. The electrode terminal 14f is connected to the electric circuit unit 31 through two corresponding connectors 13f. By detecting a short circuit between the connectors 13f, it is detected whether or not the sensor unit 14 is inserted. The electrode terminal 14f is also provided on the extension of the electrode terminals 25b to 29b. One of the two electrode terminals 14f can be shared with any one of the electrode terminals 25b to 29b.

  The electrode terminal 14f is preferably provided on the connector 13 located on the uppermost side of the holder 14a. This is an important consideration for detecting that the sensor unit 14 is securely inserted all the way.

  FIG. 4 is a cross-sectional view of the sensor 15 attached to the holder 14a. The sensor 15 includes a substrate 16, a spacer 17 bonded to the upper surface of the substrate 16, and a cover 18 bonded to the upper surface of the spacer 17.

  Reference numeral 20 denotes a reservoir for blood 8 (see FIG. 20). The reservoir 20 is formed in the spacer 17 corresponding to the substrate hole 16a formed in the approximate center of the substrate 16 and the substrate hole 16a. A spacer hole 17a and a cover hole 18a formed in the cover 18 corresponding to the substrate hole 16a are formed in communication.

  Reference numeral 21 denotes a supply path for blood 8 having one end connected to the storage section 20, and is a path that guides the blood 8 stored in the storage section 20 to the detection section 22 at once by capillary action. Further, the other end of the supply path 21 is connected to the air hole 23. The volume of the reservoir 20 is 0.904 μL, and the volume of the supply path 21 is 0.128 μL. In this way, it is possible to test with a small amount of blood 8, thereby reducing the burden on the patient.

  Reference numeral 24 denotes a reagent placed on the detection unit 22. This reagent 24 is a 0.01 to 2.0 wt% CMC aqueous solution, 0.1 to 5.0 U / sensor of PQQ-GDH, 10 to 200 mM of potassium ferricyanide, 1 to 50 mM of maltitol, and 20 to 200 mM of taurine. The reagent solution is prepared by adding and melting the solution, and the reagent solution is dropped on the detection electrodes 25 and 27 (see FIG. 5) formed on the substrate 16 and dried.

  Here, a conductive layer is formed on the upper surface of the substrate 16 by a sputtering method or a vapor deposition method using gold, platinum, palladium or the like as a material, and this is formed by laser processing from the detection electrodes 25 to 29 and the detection electrodes 25 to 29. The connection electrodes 25a to 29a respectively led out are integrally formed.

The substrate 16, spacer 17, and cover 18 are all made of polyethylene terephthalate (PET). Management costs are reduced by sharing materials.
FIG. 5 is a perspective plan view of the circular sensor 15, and connection electrodes 25 a to 29 a are led out from the detection electrodes 25 to 29, respectively.

  Reference numeral 20 denotes a blood 8 storage section provided substantially at the center of the sensor 15, and a supply path 21 having one end connected to the storage section 20 is provided toward the detection electrode 26. The other end of the supply path 21 is connected to the air hole 23. On the supply path 21, the detection electrode 28 sequentially connected to the connection electrode 28a from the storage unit 20, the detection electrode 29 connected to the connection electrode 29a, the detection electrode 28 connected to the connection electrode 28a again, The detection electrode 27 connected to the connection electrode 27a, the detection electrode 25 connected to the connection electrode 25a, the detection electrode 27 connected again to the connection electrode 27a, and the detection electrode 26 connected to the connection electrode 26a are provided. ing. A reagent 24 (see FIG. 4) is placed on the detection electrodes 25 and 27.

  The connection electrodes 25a to 29a of the sensor 15 configured as described above are led to electrode terminals 25b to 29b formed in the sensor unit 14 as shown in FIGS.

  FIG. 6 is a block diagram of the electric circuit unit 31 and the vicinity thereof. In FIG. 6, connection electrodes 25a to 29a (see FIG. 5) of the sensor 15 are connected to a switching circuit 31a via electrode terminals 25b to 29b (see FIG. 3) and connectors 13a to 13e. The output of the switching circuit 31a is connected to the input of the current / voltage converter 31b. The output is connected to the input of the arithmetic unit 31d through an analog / digital converter (hereinafter referred to as A / D converter) 31c. The output of the calculation unit 31d is connected to a display unit 34 and a transmission unit 31e made of liquid crystal. A reference voltage source 31f is connected to the switching circuit 31a. The reference voltage source 31f may be a ground potential.

  31g is a control unit, and the output of the control unit 31g includes a high voltage generation circuit 31h connected to the laser emitting device 32, a control terminal of the switching circuit 31a, a calculation unit 31d, a transmission unit 31e, and a negative pressure. Connected to means 33. Further, the input of the control unit 31g includes a detection connector 13f (see FIG. 3) that detects insertion of the sensor unit 14, a puncture button 32j that causes the laser emission device 32 to emit laser light 32h, a skin detection sensor 33b, A timer 31k is connected.

  Hereinafter, the operation of the electric circuit unit 31 will be described. First, the puncture button 32j is pressed, and the skin 7 (see FIG. 20) is punctured with the laser emitting device 32. Then, the property of blood 8 exuded by puncture is measured. In the measurement operation, the switching circuit 31a is switched to connect the detection electrode 25 (see FIG. 5) to the current / voltage converter 31b. Further, a detection electrode 26 serving as a detection electrode for detecting the inflow of blood 8 is connected to the reference voltage source 31f. Then, a constant voltage is applied between the detection electrode 25 and the detection electrode 26. In this state, when blood 8 flows in, a current flows between detection electrodes 25 and 26. This current is converted into a voltage by the current / voltage converter 31b, and the voltage value is converted into a digital value by the A / D converter 31c. And it outputs toward the calculating part 31d. The calculation unit 31d detects that the blood 8 has sufficiently flowed based on the digital value. At this time, the operation of the negative pressure means 33 is turned off.

  Next, glucose, which is a blood component, is measured. In the measurement of the glucose component amount, first, the switching circuit 31a is switched by a command from the control unit 31g, and the detection electrode 25 serving as a working electrode for measuring the glucose component amount is connected to the current / voltage converter 31b. Further, the detection electrode 27 serving as a counter electrode for measuring the glucose component amount is connected to the reference voltage source 31f.

  Note that the current / voltage converter 31b and the reference voltage source 31f are turned off while glucose in the blood is reacted with its oxidoreductase for a predetermined time. Then, after a predetermined time (1 to 10 seconds), a constant voltage (0.2 to 0.5 V) is applied between the detection electrodes 25 and 27 according to a command from the control unit 31g. As a result, a current flows between the detection electrodes 25 and 27. This current is converted into a voltage by the current / voltage converter 31b, and the voltage value is converted into a digital value by the A / D converter 31c. And it outputs toward the calculating part 31d. In the calculation part 31d, it converts into the glucose component amount based on the digital value.

After the measurement of the glucose component amount, the Hct value is measured. The Hct value is measured as follows. First, the switching circuit 31a is switched by a command from the control unit 31g. Then, the detection electrode 29 serving as a working electrode for measuring the Hct value is connected to the current / voltage converter 31b. Further, the detection electrode 25 serving as a counter electrode for measuring the Hct value is connected to the reference voltage source 31f.
Next, a constant voltage (2 V to 3 V) is applied between the detection electrodes 29 and 25 from the current / voltage converter 31b and the reference voltage source 31f according to a command from the control unit 31g. The current flowing between the detection electrodes 29 and 25 is converted into a voltage by the current / voltage converter 31b, and the voltage value is converted into a digital value by the A / D converter 31c. And it outputs toward the calculating part 31d. The calculation unit 31d converts the Hct value based on the digital value.

  Using the Hct value and the glucose component amount obtained in this measurement, the glucose component amount is corrected with the Hct value by referring to a calibration curve or a calibration curve table obtained in advance, and the corrected result is displayed on the display unit 34. To display. Further, the calibration curve or the result corrected by the calibration curve table is transmitted from the transmission unit 31e to the injection device for injecting insulin. For this transmission, radio waves can be used, but it is preferable to transmit by optical communication that does not interfere with the medical device.

  By transmitting the measurement data corrected in this way from the transmission unit 31e, the amount of insulin to be administered by the patient is set in the injection device if the dose of insulin is automatically set in the injection device. There is no need, and the troublesome setting is eliminated. In addition, since the amount of insulin can be set in the injection device without using artificial means, setting errors can be prevented.

  Although the measurement of glucose has been described above as an example, the reagent 24 of the sensor 15 can be exchanged, and in addition to the measurement of glucose, the measurement can also be applied to the measurement of blood components such as lactate and cholesterol.

  FIG. 7 is a cross-sectional view of blood test apparatus 11. The blood test apparatus 11 includes a main body portion 12 made of resin, a mounting portion 12a formed on one side of the main body portion 12, and a circular sensor portion 14 that is detachably mounted on the mounting portion 12a. It is configured.

  In the main body 12, a laser emitting device (used as an example of a puncturing means) 32 provided to face the sensor unit 14, an electric circuit unit 31 connected to the laser emitting device 32, and the sensor unit 14 The negative pressure means 33 for supplying a negative pressure to the negative pressure chamber 33a formed in the above and a battery 36 for supplying power to these are housed. A puncture button 32j emits laser light 32h from the laser emitting device 32. The puncture button 32j and the display unit 34 (see FIG. 1) are mounted on the surface of the main body unit 12.

  The laser emitting device 32 includes an oscillation tube 32a and a cylindrical body 32b connected to the oscillation tube 32a. In the oscillation tube 32a, an Er: YAG (yttrium, aluminum, garnet) laser crystal 32c and a flash light source 32d (an example of a light source) are stored. A partial transmission mirror 32e having a transmittance of about 1% is attached to one end of the oscillation tube 32a, and a total reflection mirror 32f is attached to the other end. A convex lens 32g is mounted in the cylindrical body 32b in front of the partial transmission mirror 32e, and is set so as to focus on the patient's skin under the laser beam 32h.

  The operation of the laser emitting device 32 configured as described above will be described below. The puncture button 32j is pressed. Then, the high voltage generation circuit 31h (see FIG. 6) is driven and the flash light source 32d is excited. The emitted light emitted when the flash light source 32d is excited enters the Er: YAG laser crystal 32c, where it is reflected between the total reflection mirror 32f, the YAG laser crystal 32c, and the partial transmission mirror 32e to resonate. And amplified. A part of the amplified laser light passes through the partial transmission mirror 32e by stimulated emission. The laser beam 32h that has passed through the partial transmission mirror 32e is emitted through the lens 32g and is focused under the skin 7. The depth of focus when puncturing is suitably 0.1 mm to 1.5 mm from the skin 7, and is 0.5 mm in the present embodiment.

  In this embodiment, since the laser emitting device 32 that can puncture the patient's skin 7 without contact is used, it is hygienic. In addition, there are no moving parts and there are fewer failures. Furthermore, the whole blood test apparatus 11 can be easily waterproofed, and the whole can be washed. The puncture voltage with this laser beam 32h is about 300V. Therefore, there is little pain to the patient. In this embodiment, the laser emitting device 32 is used as the puncturing means, but this is not limited to the laser emitting device 32, and a needle puncturing device that performs puncturing with a puncture needle may be used. If this needle puncturing device is used, power is not consumed at the time of puncturing, so that the battery 36 can be made to last longer.

Next, a test method using the blood test apparatus 11 will be described with reference to FIG. First, in step 41, the sensor unit 14 is mounted on the mounting unit 12a. The sensor unit 14 can be mounted by pressing and inserting from any direction of 360 degrees since the connector 13 is formed in a ring shape. This attachment is detected by a signal from the connector 13f (see FIG. 3). When the sensor unit 14 is mounted, the process proceeds to step 42. In step 42, blood test apparatus 11 is brought into contact with patient's skin 7. The contact with the skin 7 is performed by the output of the skin detection sensor 33b. When contact with the skin 7 is confirmed, the process proceeds to step 43, where the timer 31k is started and the negative pressure means 33 is operated to apply a negative pressure into the negative pressure chamber 33a. The skin 7 is raised by applying a negative pressure.
When the current change caused by the operation of the negative pressure means 33 or the time predetermined by the timer 31k elapses, it is determined that the skin 7 in the reservoir 20 is sufficiently raised by the negative pressure, and the routine proceeds to step 44. In step 44, the display unit 34 displays that puncturing is possible. Then, the process proceeds to step 45 and waits for pressing of the puncture button 32j. When the puncture button 32j is pressed, a laser beam 32h is emitted from the laser emitting device 32. This laser beam 32 h penetrates the storage part 20 of the sensor 15 and punctures the skin 7.

  Then, the process proceeds to step 46. In step 46, the exuded blood 8 is taken into the reservoir 20 of the sensor 15 by puncturing the skin 7. The blood 8 taken into the storage unit 20 is taken into the detection unit 22 (see FIGS. 4 and 5) at a stroke (at a fixed flow rate) by capillary action by the supply path 21. In step 46, the display performed in step 44 is turned off and the negative pressure is also turned off. Then, the process proceeds to step 47. In step 47, the blood glucose level of blood 8 is measured. For the measurement of the blood glucose level, refer to the description of FIG.

  When the blood glucose level is measured in step 47, the process proceeds to step 48, where the measured blood glucose level is displayed on the display unit 34 and stored in the memory. The negative pressure means 33 is turned off when the blood 8 reaches the detection electrode 26.

  As described above, since the connector 13 is formed in a ring shape, the sensor unit 14 in step 41 may be pressed and inserted from any direction 360 degrees. Accordingly, alignment or the like is not necessary, and the sensor unit 14 is remarkably easily attached.

  In addition, when the puncture button 32j is pressed in step 45, the laser light 32h penetrates through the storage unit 20, so that all the exuded blood 8 is collected in the storage unit 20 and used for blood tests. Accordingly, the exuded blood 8 is used without waste and the burden on the patient is minimized.

(Embodiment 2)
In the second embodiment, concentric connectors 52 (52a to 52e) are provided at the tip of blood test apparatus 51. Note that the same reference numerals are assigned to the same components as those in the first embodiment to simplify the description. The same applies to the following embodiments.

  FIG. 9 is a cross-sectional view of a main part of blood test apparatus 51 in the second embodiment. In FIG. 9, 53a is a mounting portion (corresponding to the mounting portion 12a in the first embodiment), and a connector 52 (corresponding to the connector 13 in the first embodiment) is formed concentrically at the tip of the mounting portion 53a. ing. The connector 52 is connected to the electric circuit unit 31.

  Reference numeral 54 denotes a sensor unit (corresponding to the sensor unit 14 in the first embodiment), and a sensor 55 (corresponding to the sensor 15 in the first embodiment) is mounted in the sensor unit 54. The sensor unit 54 is detachably inserted into and removed from the mounting unit 53a. 53c is a positioning convex portion (corresponding to the positioning convex portion 12c in the first embodiment) provided in the mounting portion 53a, and although not shown, in the holder 54a that forms the sensor portion 54 as in the first embodiment. Also, a positioning recess is formed, and the positioning recess is fitted and positioned.

  On the upper surface of the sensor 55, electrode terminals 56b to 60b (corresponding to the electrode terminals 25b to 29b in the first embodiment) respectively derived from the connection electrodes 25a to 29a (see FIG. 11) are formed in a line. By attaching the sensor portion 54 to the attachment portion 53a, the electrode terminals 56b to 60b are brought into contact with and connected to the connector 52 (52a to 52e). Although not shown, the signal of the skin detection sensor 33b and the mounting detection signal of the sensor unit 54 are also led to the electrode terminal and connected to the electric circuit unit 31 via the connector 52, as in the first embodiment. . FIG. 10 is a perspective view of the mounting portion 53 a and the sensor portion 54.

  FIG. 11 is a perspective plan view of the sensor 55, which is gathered linearly at the same location from the connection electrodes 25a to 29a provided on the substrate 16 (see FIG. 12) with the conducting wires 56c to 60c. Then, as shown in FIG. 12, the linearly collected positions are led out to the surface of the cover 18 of the sensor 15 through the via holes 56 d to 60 d and connected to the electrode terminals 56 b to 60 b.

  As described above, in the present embodiment, since the electrode terminals 56b to 60b are formed concentrically, the connection electrodes 25a to 29a formed on the sensor 55 no matter which direction the sensor unit 54 is inserted 360 degrees. Can be guided to the electric circuit section 31 through the corresponding connectors 52 (52a to 52e). Therefore, the patient can press and insert as it is without considering the directionality of the sensor unit 54.

(Embodiment 3)
In the third embodiment, concentric electrode terminals 63b to 67b (corresponding to the electrode terminals 25b to 29b in the first embodiment) are provided on the surface of the sensor 62 (corresponding to the sensor 15 in the first embodiment). .

  FIG. 13 is a perspective plan view of the sensor 62 according to the third embodiment. The sensor 62 is led out from the connection electrodes 25a to 29a provided on the substrate 16 (see FIGS. 4 and 5) to the surface of the cover 18 through the via holes 63c to 67c. And it connects to the concentric electrode terminal 63b-67b provided in the surface of this cover 18, respectively. 14 is a cross-sectional view of the sensor 62, and FIG. 15 is a cross-sectional view of a sensor unit 68 (corresponding to the sensor unit 14 in the first embodiment) in which the sensor 62 is built.

  FIG. 16 is a cross-sectional view of the sensor unit 68 and the mounting unit 70 a of the blood test apparatus 61 that uses the sensor unit 68. Connectors 71 (71a to 71e) (corresponding to the connector 13 in the first embodiment) are provided in a row at the tip of the mounting portion 70a. FIG. 17 is a perspective view of the mounting portion 70 a and the sensor portion 68. The connector 71 is connected to the electric circuit unit 31. Further, the sensor portion 68 is detachably inserted into and removed from the mounting portion 70a.

  Reference numeral 70c denotes a positioning convex portion (corresponding to the positioning convex portion 12c in the first embodiment) provided in the mounting portion 70a. Although not shown, the holder 68a that forms the sensor portion 68 is not shown in the figure. It is positioned by fitting with the formed positioning recess. When the sensor unit 68 is mounted on the mounting unit 70a, the electrode terminals 63b to 67b provided on the sensor 62 are in contact with and connected to the connector 71 (71a to 71e). Although not shown, the signal of the skin detection sensor 33b and the wearing detection signal of the sensor unit 68 are also guided to the electrode terminal and connected to the electric circuit unit 31 via the connector 71, as in the first embodiment. . FIG. 17 is a perspective view of the mounting portion 70 a and the sensor portion 68.

  The blood test apparatus according to the present invention is useful as a blood test apparatus or the like because the sensor unit can be easily mounted.

The perspective view of the blood test apparatus in Embodiment 1 of this invention Same part cross section Same part circuit diagram Cross section of the sensor used in the blood test device Same perspective plan view Same as above, block diagram of electrical circuit part of blood test device and its vicinity Cross section of blood test equipment Same as above, inspection flowchart Sectional drawing of the principal part of the blood test apparatus in the second embodiment Same part perspective view Same as above, perspective plan view of sensor used in blood test apparatus Same as above, sectional view Same perspective plan view of sensor used in blood test apparatus in embodiment 3 Same as above, sectional view Same as above, sectional view of sensor Same sectional view of blood test equipment Same perspective view Sectional view of a conventional blood test device The same principal part sectional drawing, (a) is the same sectional drawing of the mounting part which comprises a blood test apparatus, (b) is the sectional view of the holder which comprises the same sensor part. Same usage diagram

Explanation of symbols

DESCRIPTION OF SYMBOLS 11 Blood test apparatus 12 Main-body part 12a Mounting part 13a Connector 13b Connector 13c Connector 13d Connector 13e Connector 14 Sensor part 15 Sensor 25 Detection electrode 26 Detection electrode 27 Detection electrode 28 Detection electrode 29 Detection electrode 25b Electrode terminal 26b Electrode terminal 27b Electrode terminal 28b Electrode terminal 29b Electrode terminal 31 Electric circuit part

Claims (9)

The sensor unit includes a circular sensor unit and a main body unit that is detachably fitted to the sensor unit and is connected to the sensor unit. The sensor unit includes a plurality of sensor units provided in the blood sensor. Each of the detection electrodes and a plurality of electrode terminals respectively derived from the detection electrodes, and the main body portion includes a connector connected to each of the electrode terminals, and at least one of the electrode terminals or the Connector is a blood test apparatus formed in a concentric or cylindrical shape. The blood test apparatus according to claim 1, wherein the sensor unit includes a blood sensor and a holder to which the blood sensor is mounted, and the main body unit is provided with a cylindrical mounting unit in which the holder is detachably inserted and removed. . The blood test apparatus according to claim 2, wherein a ring-shaped connector is provided on the mounting portion, and an electrode terminal is provided on the holder at a position in contact with the connector. The blood test apparatus according to claim 2, wherein the mounting portion and the holder are each provided with a positioning portion. The blood test apparatus according to claim 2, wherein a concentric connector is provided at a tip of the mounting portion. The blood test apparatus according to claim 2, wherein concentric electrode terminals are provided on one surface of the blood sensor. The blood test apparatus according to claim 2, wherein a detection electrode having the same shape as the electrode terminal is provided and mounting of the sensor unit is detected by the detection electrode. The blood test apparatus according to claim 2, wherein the main body is provided with puncturing means, and the puncturing means pierces through the blood sensor. The blood test apparatus according to claim 8, wherein the main body portion is provided with negative pressure means connected to the electric circuit portion, and negative pressure is applied to the holder by the negative pressure means.

Images