JP2010094166A - Blood examination apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To solve a problem wherein an appropriate quantity of blood can not be obtained to disturb the accurate measurement because of bubbles generated from the difference in negative pressure between an upper holder and a lower holder in a puncture part. <P>SOLUTION: The blood examination apparatus includes: the puncture part 23 formed in such a state that a sensor 25 is held between the upper holder 23a and the lower holder 23b; a laser puncture unit 24 disposed to face the puncture part 23 and to penetrate a reservoir part 34 formed in the sensor 25 to puncture the skin 4; an electric circuit part 30 connected to the sensor 25; and a negative pressure means 27 connected to the electric circuit part 30 to apply negative pressure to the upper holder 23a. The blood examination apparatus has a fluid-penetrating hole 36 to make the pressure in the upper holder 23a identical to the pressure in the lower holder 23b. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a blood test apparatus.

  Hereinafter, a conventional blood test apparatus will be described. As shown in FIG. 13, the conventional blood test apparatus 1 has a puncture portion 2 formed so as to sandwich a blood sensor (hereinafter referred to as a sensor) 3 between an upper holder 2 a and a lower holder 2 b, and is opposed to the puncture portion 2. The laser puncture unit 5 that punctures the skin 4 through the storage portion 3a (see FIG. 14) formed in the sensor 3 and an electric circuit connected to the sensor 3 loaded in the puncture portion 2 Unit 6, a negative pressure means 7 that is connected to the electric circuit unit 6 and applies a negative pressure to the upper holder 2 a, a battery 8 that supplies power to them, and a sensor cartridge 9 in which the sensor 3 is stacked and housed These were housed in the housing 10.

  The operation of blood test apparatus 1 configured as described above will be described below. First, the lowermost sensor 3 stacked and accommodated in the sensor cartridge 9 is loaded into the puncture unit 2 from the outlet 9a. The sensor 3 is sandwiched and fixed between the upper holder 2a and the lower holder 2b.

  Next, as shown in FIG. 14, the finger skin 4 is brought into contact with the puncture unit 2. And by operating the negative pressure means 7, a negative pressure is applied in the upper holder negative pressure space 2c formed in the upper holder 2a from the suction port 7b. The negative pressure applied to the upper holder 2 a causes the inside of the lower holder negative pressure space 2 d formed in the lower holder 2 b to be negative pressure via the storage portion 3 a formed in the sensor 3. When a negative pressure is applied to the lower holder 2b, the lower holder negative pressure space 2d is in a reduced pressure state, and the skin 4 rises and closes the reservoir 3a.

  In this state, when the puncture button 5a (see FIG. 13) is pressed, the laser puncture unit 5 emits laser light 5b. This laser beam 5b penetrates the reservoir 3a and punctures the skin 4. Blood 11 exudes from the punctured skin 4. The exuded blood 11 is stored in the storage unit 3a and then taken into the sensor 3 through the supply path derived from the storage unit 3a. The blood 11 taken into the sensor 3 chemically reacts with the reagent. The reaction result is calculated in the electric circuit unit 6 to calculate the blood sugar level.

As prior art document information related to the invention of this application, for example, Patent Document 1 and Patent Document 2 are known.
Special Table 2003-52496 JP 2002-219114 A

  However, in such a conventional blood test apparatus 1, since the storage part 3a is blocked, a pressure difference is generated between the upper holder 2a and the lower holder 2b constituting the puncture part 2. For this reason, there are the following problems. That is, the surface of the skin 4 is not uniform and uneven, and the contact between the skin 4 and the lower holder 2b is not always constant. In such a case, when air leaks from the vicinity of the reservoir 3a due to a negative pressure difference, the blood 11 and air are mixed, and bubbles 12 are generated as shown in FIG. The bubbles 12 are mixed into the blood 11 and flow into the supply path.

  Since the bubbles 12 flow into the supply path of the sensor 3, a predetermined blood volume cannot be ensured, and accurate measurement is hindered, or the blood 11 is scattered when the bubbles 12 burst. There is a problem that the inside of blood test apparatus 1 may be soiled.

  SUMMARY OF THE INVENTION Accordingly, an object of the present invention is to provide a blood test apparatus that prevents the generation of bubbles that cause such problems.

  In order to achieve this object, the blood test apparatus of the present invention is provided with pressure equalizing means for making the pressures of the upper holder and the lower holder the same. Thereby, the initial purpose can be achieved.

  As described above, the present invention is provided with the pressure equalizing means for making the pressures of the upper holder and the lower holder the same. By this pressure equalizing means, the pressure of the upper holder and the lower holder becomes the same. Bubbles are not generated and mixed. Therefore, measurement can be performed using a predetermined appropriate amount of blood, and accurate measurement can be performed.

  In addition, since no bubbles are generated, the bubbles do not burst in the first place, and the blood test apparatus is not soiled. Therefore, it leads to the improvement of hygiene and safety of the blood test apparatus.

(Embodiment 1)
FIG. 5 is a perspective plan view of blood test apparatus 21 in the first embodiment. In FIG. 5, 22 is a housing formed of resin, and the housing 22 is composed of a main body portion 22a and a lid portion 22b. The lid portion 22b is rotatably connected to the main body portion 22a by a hinge portion 22c. An opening / closing sensor 22d for detecting opening / closing of the lid portion 22b is attached to the lower side of the main body portion 22a.

  In the lower left corner of the main body 22a, there is provided a puncture portion 23 composed of an upper holder 23a and a lower holder 23b. A laser puncture unit 24 (used as an example of puncture means) is opposed to the puncture portion 23. ) Is installed. This is not limited to the laser puncture unit 24, and may be a needle puncture means using a puncture needle. A sensor cartridge 26 in which blood sensors (hereinafter referred to as sensors) 25 are stacked and accommodated in parallel with the laser puncture unit 24 is detachably inserted.

  In addition, a slide plate 26a forming a conveying means is provided below the sensor cartridge 26. By this slide plate 26a, the lowermost sensor 25 of the sensors 25 stacked and accommodated from the outlet 26b to the puncture portion 23. It is conveyed to.

  A negative pressure means 27 is accommodated above the sensor cartridge 26, and negative pressure is supplied from the negative pressure means 27 to the puncture portion 23 via a negative pressure path 27a. An electric circuit unit 30 is mounted above the laser puncture unit 24, and a secondary battery 29 is detachably inserted above the electric circuit unit 30.

  Next, details of the sensor cartridge 26 will be described. The sensor cartridge 26 is a sensor chamber 26d in which the sensors 25 are stacked and housed, a desiccant chamber 26e provided in parallel with the sensor chamber 26d, and transport means for transporting the sensor 25 in the sensor chamber 26d to the puncture unit 23. Slide plate 26a. A desiccant 26f is accommodated in the desiccant chamber 26e. The reason why the desiccant 26f is accommodated is that the performance of the sensor 25 deteriorates due to moisture, so that the performance deterioration due to this moisture is prevented.

  The sensor chamber 26d is provided with a pressing plate 26g that presses the sensor 25 downward. The pressing plate 26g is biased downward by a spring 26h. In addition, a loading lever 26j is integrally connected to the slide plate 26a, and the sensor 25 is loaded into the puncture portion 23 by moving the loading lever 26j to the left with a finger. The loading lever 26j is biased rightward by a spring 26k. Therefore, when the finger is released, the loading lever 26j returns to the original position.

  FIG. 2 is a plan view of the sensor 25 loaded in the puncture unit 23. The sensor 25 is a rectangular plate, the width dimension 25a is 12 mm, and the length dimension 25b is 14 mm. A storage portion 34 formed of a through hole is formed at the approximate center of the sensor 25, and a supply path 35 formed of a capillary tube is formed from the storage portion 34 toward one side. An air hole 38 is provided at the end of the supply path 35.

  Reference numeral 36 denotes a fluid through hole (used as an example of pressure equalizing means), which is provided through the plate body. Accordingly, the pressures of the upper holder 23a and the lower holder 23b constituting the puncture unit 23 can be made the same. The fluid through hole 36 is provided in the vicinity of a substantially intermediate position of the supply path 35 that connects the storage portion 34 and the air hole 38. By providing the fluid through hole 36 at this position, it is not necessary to provide a special space for forming the fluid through hole 36, and the sensor 25 can be downsized.

  A suction port 27b is connected to the negative pressure path 27a (see FIG. 5), and is formed in the upper holder 23a. Therefore, when the sensor 25 is loaded into the puncture portion 23, the fluid through hole 36 is loaded so as to be positioned on the suction port 27b side. By providing the fluid through-hole 36 on the suction port 27b side, suction loss can be reduced and suction can be performed efficiently.

The area of the hole of the reservoir 34 and 12.6 mm ^2, the area of the fluid through-hole 36 is set to 0.785 mm ^2, the area of the air hole 38 is set to 0.007 mm ^2. This is because the generation of the bubbles 12 can be prevented by setting the area of the fluid through hole 36 to 6.2% or more of the area of the storage portion 34.

  In the present embodiment, the above values are set in consideration of downsizing of the sensor 25. The area of the air hole 38 is a value set to prevent blood 11 from flowing out of the air hole 38 and to ensure the effect of capillary action. For this reason, the area of the fluid through hole 36 is smaller than the area of the reservoir 34 and larger than the area of the air hole 38. Connection electrodes 41 a to 45 a and 47 a connected to the electric circuit unit 30 are formed on the other side of the sensor 25.

  FIG. 3 is a plan view showing the relationship between the upper holder 23 a and the sensor 25. A sensor 25 indicated by a dotted line is loaded below the upper holder 23a. And the laser beam 24a (refer FIG. 1, FIG. 5) penetrates the storage part 34, and punctures the skin 4 (refer FIG. 1). Reference numeral 49 denotes a connector connected to the electric circuit unit 30, and the connectors 49 (49 a to 49 f) are connected to connection electrodes 41 a to 45 a and 47 a formed on the sensor 25, respectively. An upper holder negative pressure space 23c, which is a first space, is formed in the upper holder 23a, and a suction port 27b is connected to the upper holder negative pressure space 23c. In a state where the sensor 25 is loaded in the puncture portion 23, the sensor 25 is loaded so that the fluid through hole 36 is located in the upper holder negative pressure space 23c.

  FIG. 4 is a perspective view of the puncture unit 23 loaded with the sensor 25 as viewed from below. The sensor 25 is loaded between the upper holder 23a and the lower holder 23b. In a state where the sensor 25 is loaded in the puncture portion 23, the storage portion 34 and the fluid through hole 36 formed in the sensor 25 are disposed in the lower holder negative pressure space 23d that is the second space formed in the lower holder 23b. To be loaded. The skin contact portion 23e that forms the lower holder negative pressure space 23d is provided with a skin detection sensor 27c that detects the contact of the skin 4.

  FIG. 1 shows a cross-sectional view of the main part around the puncture portion 23 at the time of puncture. The puncture part 23 is comprised by the upper holder 23a and the lower holder 23b, and the sensor 25 is loaded between this upper holder 23a and the lower holder 23b. A suction port 27b is connected to the upper holder negative pressure space 23c provided in the upper holder 23a, and applies a negative pressure to the upper holder negative pressure space 23c. On the top surface of the upper holder negative pressure space 23c, a laser transmission film 23f that transmits laser light and is detachable is attached. This is because the portion of the laser puncture unit 24 is not soiled by scattered matter that scatters during laser puncture.

  During the puncturing operation, the skin contact portion 23e forming the lower holder negative pressure space 23d provided in the lower holder 23b contacts the skin 4. The lower holder negative pressure space 23 d is supplied with negative pressure from the upper holder negative pressure space 23 c via the storage portion 34 formed in the sensor 25 and the fluid through hole 36.

  When the skin detection sensor 27c provided in the skin contact portion 23e detects the skin 4, the negative pressure means 27 operates to generate a negative pressure. The negative pressure is applied to the upper holder negative pressure space 23c through the negative pressure path 27a and the suction port 27b. The negative pressure in the upper holder negative pressure space 23 c applies a negative pressure to the lower holder negative pressure space 23 d through the storage portion 34 and the fluid through hole 36.

  When a negative pressure is applied to the lower holder negative pressure space 23d, the skin 4 is sucked up and swells to block the reservoir 34. In this state, when the puncture button 24b (see FIG. 5) is pressed, the laser beam 24a is emitted from the laser puncture unit 24. The laser beam 24a passes through the transparent film 23f, the upper holder negative pressure space 23c, the storage portion 34, and the lower holder negative pressure space 23d in this order, and punctures the skin 4. Blood 11 exudes from the punctured skin 4. The exuded blood 11 is taken into the reservoir 34.

  At this time, even if a minute gap is formed between the raised skin 4 and the reservoir 34, the pressures in the upper holder negative pressure space 23c and the lower holder negative pressure space 23d are equalized via the fluid through hole 36. . Therefore, there is no flow of air through the minute gap formed between the storage portion 34 and the skin 4, and the bubbles 12 are not generated. That is, the air bubbles 12 do not enter the blood 11, and a predetermined appropriate amount of blood 11 can be flowed into the supply path, so that accurate measurement can be performed. In addition, since the bubbles 12 are not generated, the bubbles 12 do not burst in the first place, and the blood test apparatus 21 is not soiled. Therefore, the blood test apparatus 21 is improved in terms of hygiene and safety.

  Next, the internal structure of the sensor 25 will be described. FIG. 6 is a cross-sectional view of the sensor 25. The sensor 25 includes a substrate 31, a spacer 32 bonded to the upper surface of the substrate 31, and a cover 33 bonded to the upper surface of the spacer 32.

  Reference numeral 34 denotes a reservoir for blood 11 (see FIG. 1). The reservoir 34 is formed in the substrate hole 31a formed substantially at the center of the substrate 31 and the spacer 32 corresponding to the substrate hole 31a. A spacer hole 32a and a cover hole 33a formed in the cover 33 corresponding to the substrate hole 31a are formed in communication.

  Reference numeral 35 denotes a supply path of blood 11 having one end connected to the storage section 34, and is a path that guides the blood 11 stored in the storage section 34 to the detection section 37 at once by capillary action. The other end of the supply path 35 is connected to the air hole 38. The volume of the reservoir 34 is 0.904 μL, and the volume of the supply path 35 is 0.144 μL. In this way, it is possible to test with a small amount of blood 11, thereby reducing the burden on the patient.

  Reference numeral 40 denotes a reagent placed on the detection unit 37. This reagent 40 is a 0.01 to 2.0 wt% CMC aqueous solution, PQQ-GDH 0.1 to 5.0 U / sensor, potassium ferricyanide 10 to 200 mM, maltitol 1 to 50 mM, and taurine 20 to 200 mM. The reagent solution is prepared by adding and melting it, and it is formed by dropping it on the detection electrodes 41 and 43 (see FIG. 7) constituting the detection unit 37 formed on the substrate 31 and drying it. .

  A conductive layer is formed on the upper surface of the substrate 31 by a sputtering method or a vapor deposition method using gold, platinum, palladium or the like as a material, and this is derived from the detection electrodes 41 to 45 and the detection electrodes 41 to 45 by laser processing, respectively. The connection electrodes 41a to 45a and the identification electrode 47a are integrally formed.

  FIG. 7 is a perspective plan view of the sensor 25. Connection electrodes 41a to 45a and an identification electrode 47a are formed on one end. An identification portion 47 formed of a conductor pattern is formed between the connection electrode 43a and the identification electrode 47a.

  Reference numeral 34 denotes a blood 11 storage part provided substantially at the center of the sensor 25, and a supply path 35 having one end connected to the storage part 34 is provided toward the detection electrode 42. The other end of the supply path 35 is connected to the air hole 38. On the supply path 35, the detection electrode 44 connected to the connection electrode 44a in order from the reservoir 34 side, the detection electrode 45 connected to the connection electrode 45a, the detection electrode 43 connected to the connection electrode 43a, A detection electrode 41 connected to the connection electrode 41a and a detection electrode 42 connected to the connection electrode 42a are provided. A reagent 40 is placed on the detection electrodes 41 and 43.

  Whether or not the sensor 25 is attached to the puncture unit 23 can be identified based on whether or not there is electrical continuity between the connection electrode 43a and the identification electrode 47a. If there is no electrical continuity, the sensor 25 is not attached to the puncture portion 23.

  In addition, by changing the electric resistance value of the identification unit 47, it is possible to store information on a calibration curve to be used or store manufacturing information. Therefore, a more precise blood test can be performed using these pieces of information.

  Since it is configured as described above, when the blood 11 is spotted on the reservoir 34, the blood 11 passes through the detection electrodes 45 and 43 in order by capillarity in the supply path 35 and onto the detection electrode 42. Led. By guiding the blood 11 to the detection electrode 42, it can be known that sufficient blood 11 has reached the detection electrodes 41 and 43 that constitute the detection unit 37 located in front of the detection electrode 42. This blood 11 reacts with the reagent 40. The reaction result is guided to the connection electrodes 41a and 43a.

  FIG. 8 is a block diagram of the electric circuit unit 30 and its surroundings. In FIG. 8, the connection electrodes 41a to 45a and the identification electrode 47a (see FIG. 7) of the sensor 25 are connected to the switching circuit 30a via connectors 49 (49a to 49e) provided on the upper holder 23a. The output of the switching circuit 30a is connected to the input of the current / voltage converter 30b. The output is connected to the input of the arithmetic unit 30d via an analog / digital converter (hereinafter referred to as A / D converter) 30c. The output of the arithmetic unit 30d is connected to the display unit 50 and the communication unit 30e formed of liquid crystal. A reference voltage source 30f is connected to the switching circuit 30a. The reference voltage source 30f may be a ground potential.

  Reference numeral 30g denotes a control unit. The output of the control unit 30g includes a high voltage generation circuit 30h connected to the laser puncture unit 24, a control terminal of the switching circuit 30a, a calculation unit 30d, a communication unit 30e, a negative pressure Connected to means 27. Further, a puncture button 24b for emitting laser light 24a, a connector 49f, a skin detection sensor 27c, a timer 30k, and an open / close detection sensor 22d are connected to the input of the control unit 30g.

  Hereinafter, the operation of the electric circuit unit 30 will be described. First, the puncture button 24 b is pressed and the skin 4 is punctured with the laser puncture unit 24. And the property of the blood 11 exuded by this puncture is measured. In the measurement operation for measuring the property of the blood 11, the switching circuit 30a is switched to connect the detection electrode 41 (see FIG. 7) to the current / voltage converter 30b. In addition, a detection electrode 42 serving as a detection electrode for detecting the inflow of blood 11 is connected to the reference voltage source 30f. A constant voltage is applied between the detection electrode 41 and the detection electrode 42. In this state, when blood 11 flows in, a current flows between detection electrodes 41 and 42. This current is converted into a voltage by the current / voltage converter 30b, and the voltage value is converted into a digital value by the A / D converter 30c. And it outputs toward the calculating part 30d. The calculation unit 30d detects that the blood 11 has sufficiently flowed based on the digital value. At this time, the operation of the negative pressure means 27 is turned off.

  Next, glucose, which is a blood component, is measured. In the measurement of the glucose component amount, first, the switching circuit 30a is switched by a command from the control unit 30g, and the detection electrode 41 serving as a working electrode for measuring the glucose component amount is connected to the current / voltage converter 30b. Further, a detection electrode 43 serving as a counter electrode for measuring the glucose component amount is connected to the reference voltage source 30f.

  Note that the current / voltage converter 30b and the reference voltage source 30f are kept off while glucose in the blood reacts with its oxidoreductase for a certain time. Then, after a certain time (1 to 10 seconds), a certain voltage (0.2 to 0.5 V) is applied between the detection electrodes 41 and 43 according to a command from the control unit 30g. Then, a current flows between the detection electrodes 41 and 43. This current is converted into a voltage by the current / voltage converter 30b, and the voltage value is converted into a digital value by the A / D converter 30c. And it outputs toward the calculating part 30d. The computing unit 30d converts 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 30a is switched by a command from the control unit 30g. Then, the detection electrode 45 serving as a working electrode for measuring the Hct value is connected to the current / voltage converter 30b. Further, the detection electrode 41 serving as a counter electrode for measuring the Hct value is connected to the reference voltage source 30f.

  Next, a constant voltage (2 V to 3 V) is applied between the detection electrodes 45 and 41 from the current / voltage converter 30b and the reference voltage source 30f according to a command from the control unit 30g. The current flowing between the detection electrodes 45 and 41 is converted into a voltage by the current / voltage converter 30b, and the voltage value is converted into a digital value by the A / D converter 30c. And it outputs toward the calculating part 30d. The calculation unit 30d 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 50. To display. Further, the corrected result is transmitted from the transmission unit 30e to the injection device for injecting insulin.

  The glucose measurement has been described above as an example. However, the reagent 40 of the sensor 25 can be replaced, and the measurement can be applied to the measurement of blood components such as lactate and cholesterol in addition to glucose measurement.

  Next, the inspection method will be described using the operation flowchart of FIG. First, in step 61, the lid 22b of the blood test apparatus 21 is opened. The opening of the lid 22b is detected by an open / close detection sensor 22d. Next, the process proceeds to step 62, and the slide plate 26a is moved toward the outlet 26b of the sensor cartridge 26. As a result, the sensor 25 at the bottom of the stacked sensors 25 can be transported to the puncture unit 23. This conveyance confirmation is performed by detecting the continuity between the connection electrode 43a (see FIG. 7) of the sensor 25 and the identification electrode 47a. Thereafter, the slide plate 26a returns to the standby state by the force of the spring 26k.

  Next, the process proceeds to step 63. In step 63, the puncture part 23 of the blood test apparatus 21 is brought into contact with the patient's skin 4. The contact with the skin 4 is performed by the output of the skin detection sensor 27c. When the contact with the skin 4 is confirmed, the routine proceeds to step 64 where the negative pressure means 27 is operated to apply a negative pressure to the lower holder negative pressure space 23d of the puncture portion 23. The skin 4 is raised by applying a negative pressure. Since the negative pressure to the lower holder negative pressure space 23d is applied via the reservoir 34 and the fluid through hole 36, even if the reservoir 34 is blocked by the rise of the skin 4, the negative pressure is applied via the fluid through hole 36. Thus, the pressures in the upper holder negative pressure space 23c and the lower holder negative pressure space 23d are equal.

  When the current change caused by the operation of the negative pressure means 27 or the time predetermined by the timer 30k elapses, it is determined that the skin 4 in the lower holder negative pressure space 23d is sufficiently raised by the negative pressure, and the routine proceeds to step 65. . In step 65, the display unit 50 displays that puncture is possible. Then, the process proceeds to step 66 and waits for pressing of the puncture button 24b. This puncture can also be performed automatically. When performing automatically, it is desirable to display the puncture timing on the display unit 50 or warn the patient with a sound.

  When the puncture button 24b is pressed, the laser beam 24a is emitted and the process proceeds to step 67. In step 67, the display on the display unit 50 performed in step 65 is turned off. Then, the process proceeds to step 68. In step 68, the exuded blood 11 is taken into the storage part 34 of the sensor 25 by puncturing the skin 4. The blood 11 taken into the storage part 34 is taken into the detection part 37 at a stroke (at a fixed flow rate) by capillary action by the supply path 35. Then, the blood glucose level of blood 11 is measured.

  When the blood glucose level is measured at step 68, the routine proceeds to step 69 where the negative pressure means 27 is turned off. Then, the process proceeds to step 70. In step 70, the measured blood glucose level is displayed on the display unit 50. The negative pressure means 27 may be turned off when the blood 11 reaches the detection electrode 42.

  This completes the measurement of blood 11 and proceeds to step 71. In step 71, the used sensor 25 is discarded. The confirmation of the discard can confirm the continuity between the connection electrode 43a and the identification electrode 47a, confirm whether or not the sensor 25 is present in the puncture unit 23, and display that fact on the display unit 50. .

  Next, the process proceeds to step 72. In step 72, the lid 22b of the blood test apparatus 21 is closed. The closing of the lid 22b is detected by an open / close detection sensor 22d.

  As described above, in step 64, since the negative pressure to the lower holder negative pressure space 23 d is applied through the storage portion 34 and the fluid through hole 36, the storage portion 34 is blocked by the rise of the skin 4. Even if it is, it is added through the fluid through hole 36. Therefore, the pressures in the upper sensor negative pressure space 23c and the lower sensor negative pressure space 23d are always equal, no air flows in through the reservoir 34, and bubbles 12 are not generated. Therefore, since the measurement can be performed using a predetermined appropriate amount of blood 11, accurate measurement can be performed.

(Embodiment 2)
FIGS. 10-12 has shown the figure in Embodiment 2 of this invention. FIG. 10 is a cross-sectional view of the main part around the puncture unit using blood test apparatus 81 in the second embodiment (corresponding to blood test apparatus 21 in the first embodiment).

  In the second embodiment, the same components as those in the first embodiment are denoted by the same reference numerals, and the description is simplified.

  FIG. 11 is a plan view showing the relationship between the upper holder 82a (corresponding to the upper holder 23a in the first embodiment) and the sensor 83 (corresponding to the sensor 25 in the first embodiment).

  A sensor 83 indicated by a dotted line is loaded below the upper holder 82a. Then, the laser beam 24a (see FIGS. 5 and 10) penetrates the reservoir 34 and punctures the skin 4. Reference numeral 49 denotes a connector connected to the electric circuit unit 30, and the connectors 49 (49 a to 49 f) are connected to connection electrodes 41 a to 45 a and 47 a formed on the sensor 83, respectively. An upper holder negative pressure space 82c, which is a first space, is formed in the upper holder 82a, and the upper holder suction path 82e (see FIG. 10) enters the upper holder negative pressure space 82c via a branch path 84. Are connected.

  FIG. 12 is a perspective view of the puncture unit 82 loaded with the sensor 83 as viewed from below. The sensor 83 is loaded between the upper holder 82a and the lower holder 82b (corresponding to the lower holder 23b in the first embodiment). In a state in which the sensor 83 is loaded in the puncture portion 82, the second space formed in the upper holder negative pressure space 82c and the lower holder 82b, which are the first spaces formed in the upper holder 82a, via the branch path 84. The lower holder negative pressure space 82d, which is a space, is connected to the upper holder suction path 82e and the lower holder suction path 82f, respectively. The skin contact portion 23e that forms the lower holder negative pressure space 82d is provided with a skin detection sensor 27c (see FIG. 10) that detects the contact of the skin 4.

  Next, in FIG. 10, the puncture portion 82 is composed of an upper holder 82a and a lower holder 82b, and laser light is transmitted through the top surface of the upper holder negative pressure space 82c provided in the upper holder 82a. A detachable laser transmitting film 23f is attached. This is provided so as to prevent the laser puncture unit 24 from being soiled by scattered matter scattered during laser puncture.

  The sensor 83 conveyed from the sensor cartridge 26 (see FIG. 5) is sandwiched and fixed between the upper holder 82a and the lower holder 82b.

  In the sensor 83, the fluid through hole 36 is not formed. As a supplement to the role of the fluid through-hole 36, a branch portion 84 (used as an example of a pressure equalizing means) connected to the negative pressure means 27 is branched into an upper holder suction path 82e and a lower holder suction path 82f. The upper holder suction path 82e is connected to the upper holder negative pressure space 82c that is the first space, and the lower holder suction path 82f is connected to the lower holder negative pressure space 82d that is the second space.

  During the puncturing operation, the skin contact portion 23e forming the lower holder negative pressure space 82d provided in the lower holder 82b contacts the skin 4. The lower holder negative pressure space 82d is supplied with negative pressure from the negative pressure means 27 through the upper holder suction path 82e and the lower holder suction path 82f connected to the storage section 34 and the branch section 84 formed in the sensor 83. Is done.

  When the skin detection sensor 27c provided in the skin contact portion 23e detects the skin 4, the negative pressure means 27 operates to generate a negative pressure. This negative pressure is applied to the upper holder negative pressure space 82c and the lower holder negative pressure space 82d through the upper holder suction path 82e and the lower holder suction path 82f connected to the branch portion 84.

  When a negative pressure is applied to the lower holder negative pressure space 82d, the skin 4 is sucked and swelled to block the storage portion 34. In this state, when the puncture button 24b (see FIG. 5) is pressed, the laser beam 24a is emitted from the laser puncture unit 24. The laser beam 24a passes through the laser transmitting film 23f, the upper holder negative pressure space 82c, the storage portion 34, and the lower holder negative pressure space 82d in this order in a straight line, and punctures the skin 4. Blood 11 exudes from the punctured skin 4. The exuded blood 11 is taken into the reservoir 34.

  At this time, even if a minute gap is formed between the raised skin 4 and the storage part 34, the upper holder negative path is connected via the upper holder suction path 82e and the lower holder suction path 82f. The pressures in the pressure space 82c and the lower holder negative pressure space 82d are equal. Accordingly, the pressures in the upper holder negative pressure space 82c and the lower holder negative pressure space 82d are always equal. That is, even if the reservoir 34 is blocked by the skin 4, there is no pressure difference between the upper holder negative pressure space 82c and the lower holder negative pressure space 82d, so a minute gap between the skin 4 and the reservoir 34 is present. Inflow of air due to is eliminated, and bubbles 12 are not generated. Therefore, since the measurement can be performed using a predetermined appropriate amount of blood 11, accurate measurement can be performed. In addition, since the bubbles 12 are not generated, the bubbles 12 do not peel off in the first place, and the blood test apparatus 21 is not soiled. Therefore, the hygiene and safety of the blood test apparatus 21 are improved.

  The blood test apparatus according to the present invention can be used for a blood test apparatus and the like because appropriate blood can be obtained and accurately measured.

Sectional drawing of the principal part around the puncture part of the blood test apparatus in Embodiment 1 of the present invention The top view of the sensor loaded in the puncture unit The top view showing the relationship between the upper holder and the sensor The perspective view seen from the lower holder side of the puncture part Same as above, perspective view of blood test equipment Cross section of the sensor used in the blood test equipment Same perspective plan view of sensor Same as above, block diagram of electrical circuit and its surroundings Same operation flowchart Sectional drawing of the principal part around the puncture part of the blood test apparatus in Embodiment 2 of the present invention The top view which shows the relationship between the upper holder and sensor in a puncture part similarly The perspective view seen from the lower holder side of the puncture part A perspective plan view of a conventional blood test apparatus The principal part sectional drawing of the 1st state at the time of puncture The principal part sectional drawing of the 2nd state at the time of puncture

Explanation of symbols

DESCRIPTION OF SYMBOLS 4 Skin 21 Blood test apparatus 23 Puncture part 23a Upper holder 23b Lower holder 23c Upper holder negative pressure space 23d Lower holder negative pressure space 24 Laser puncture unit 25 Sensor 27 Negative pressure means 30 Electric circuit part 34 Blood storage part 36 Fluid through-hole

Claims (11)

A puncture portion formed so as to sandwich the blood sensor between the upper holder and the lower holder, and provided to face the puncture portion, and pierce the skin through the blood storage portion formed in the blood sensor Puncturing means, an electric circuit section connected to the blood sensor, and negative pressure means connected to the electric circuit section and applying negative pressure to the first space formed by the upper holder and the blood sensor And a blood test apparatus provided with pressure equalizing means for making the pressures of the first space and the second space formed by the lower holder, the blood sensor and the skin the same. The blood test apparatus according to claim 1, wherein the pressure equalizing means is a fluid through hole formed in the blood sensor. The blood test apparatus according to claim 2, wherein the fluid through hole is provided at a substantially intermediate position of a blood supply path that connects the blood reservoir and the air hole, and is provided on a suction port side that supplies negative pressure. The fluid through-hole is in a circular shape centered on the blood reservoir and having a radius between the blood reservoir and the air hole, and is connected to the blood reservoir and the air hole and the blood supply path connecting them. The blood test apparatus according to claim 2, wherein the blood test apparatus is provided at a position that does not overlap. The blood test apparatus according to claim 3, wherein the area of the fluid through hole is larger than the area of the air hole. The blood test apparatus according to claim 1, wherein the pressure equalizing means branches off the negative pressure path connected to the negative pressure means and connects to the upper holder and the lower holder, respectively. The blood test apparatus according to claim 1, wherein the fluid through hole is provided at a position not in contact with the skin and blood. The blood test apparatus according to claim 1, wherein the puncturing means is a laser puncturing unit. The blood test apparatus according to claim 1, wherein a film is provided on a top surface of the upper holder. The blood test apparatus according to claim 8, wherein a laser transmission film that transmits laser light is provided on a top surface of the upper holder. A puncture part formed so as to sandwich the blood sensor between the upper holder and the lower holder, an electric circuit part connected to the blood sensor via a connector provided in the puncture part, and connected to the electric circuit part And a negative pressure means for applying a negative pressure to the first space formed by the upper holder and the blood sensor, and formed by the first space, the lower holder, the blood sensor and the skin. A blood test apparatus provided with pressure equalizing means for making the pressure in the second space the same.

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