JP2010178818A - Laser puncture instrument and blood test device using the same - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To solve such a problem that a battery and capacitors inside a laser puncture instrument are adjacently disposed and there is a risk of sparking between the battery and the capacitor terminals. <P>SOLUTION: This laser puncture instrument includes a housing 12, a laser puncture unit 16 disposed inside the housing 12, and the capacitors 13a and 13b and the battery 15 disposed sandwiching the laser puncture unit 16. This constitution can accomplish the purpose desired. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a laser puncture apparatus and a blood test apparatus using the same.

  A diabetic patient needs to regularly measure a blood glucose level, inject insulin based on the blood glucose level, and keep the blood glucose level normal. Therefore, the patient must collect a small amount of blood from the fingertip. In order to collect this blood, a puncture device is required.

  Hereinafter, a blood test apparatus (an example of a puncture apparatus) including a conventional laser puncture apparatus will be described. As shown in FIG. 16, a conventional laser puncture apparatus 1 has a substantially rectangular parallelepiped shape and a housing 2 having a protruding portion 2a on one side, and a laser puncturing unit 3 mounted across the housing 2 and the protruding portion 2a. A finger pad 4 facing the laser puncture unit 3 and mounted on the protrusion 2a, a battery 5 mounted on the other side of the housing 2, and an electric circuit section 6 adjacent to the battery 5 Was composed.

  The laser puncture unit 3 is composed of a laser rod 3c and a flash lamp 3d. During laser puncture, the flash lamp 3d emits light, and the emitted excitation light is taken into the laser rod 3c. The light emitted when the excited Er molecules return to the stable state is amplified by stimulated emission between the laser rods 3c, and a part of the light is emitted through the end face. As a result, the laser beam 3b is emitted from the laser puncture unit 3.

  The usage method of the laser puncture apparatus 1 comprised as mentioned above is demonstrated based on FIG. First, the laser puncture device 1 is grasped with the right hand 7a. Then, the finger rest 4 is brought into contact with the skin 9 of the left hand 7b. In this state, the puncture button 3a is pressed with the middle finger 8c of the right hand 7a. Laser light 3b (see FIG. 16) is emitted from the laser puncture device 1 to puncture the skin 9. Blood 10 exudes from the skin 9.

As prior art document information related to the invention of this application, for example, Patent Document 1 is known.
International Publication No. 2008/087982 Pamphlet

  However, in such a conventional laser puncture apparatus 1, when a laser puncture is performed, if a voltage is directly supplied from the battery 5 to the flash lamp 3d mounted in the laser puncture unit 3, the voltage applied to the battery is Is insufficient to cause the flash lamp 3d to emit light. Accordingly, it is necessary to supply the voltage to the flash lamp 3d after increasing the voltage in advance in the electric circuit section 6.

  Here, generally, a capacitor (not shown) electrically connected to the electric circuit unit 6 is used as means for increasing the voltage. However, if the battery 5 and the electric circuit unit 6 are disposed adjacent to each other, the electric circuit The distance between the capacitor terminal (not shown) connected to the unit 6 and the battery 5 is short, and there is a risk of sparking between the capacitor terminal and the battery 5.

  Therefore, the present invention has been made to solve such problems, and an object of the present invention is to provide a laser puncture device that can avoid a spark between a capacitor terminal and a battery and can reliably perform a puncture operation.

  In order to achieve this object, a laser puncture apparatus according to the present invention includes a housing, a laser puncture unit disposed inside the housing, and a capacitor and a battery disposed so as to sandwich the laser puncture unit. A puncture device is provided. Thereby, the intended purpose can be achieved.

  As described above, according to the present invention, there is provided a laser puncture device including a housing, a laser puncture unit disposed inside the housing, and a capacitor and a battery disposed so as to sandwich the laser puncture unit. By disposing the capacitor and the battery in this way, the distance between the capacitor terminal and the battery is separated by at least the laser puncture unit. Therefore, the distance between the battery and the terminal of the capacitor that handles high voltage is increased, and sparking between the battery and the capacitor terminal can be avoided.

  In addition, a heavy capacitor is disposed on one side of the housing, and another heavy battery is disposed on the other side of the housing. By arranging in this way, the center of weight becomes substantially the center of the housing. Therefore, in blood glucose measurement after meals at restaurants, etc., when performing puncture under a table or the like so as not to be seen by humans, the center of gravity should be approximately in the center of the housing and be operated in a stable state. Can do.

  Furthermore, since the main components of the battery, the capacitor, and the laser puncture unit can be efficiently arranged in parallel in the housing, the size can be reduced.

(Embodiment 1)
FIG. 1 is a cross-sectional view of laser puncture apparatus 11 in the first embodiment. In FIG. 1, reference numeral 12 denotes a rectangular parallelepiped housing 12, and a high voltage generation circuit 14 (see FIG. 5) including a large-capacitance capacitor 13 (13 a, 13 b) on one side 12 a of the housing 12. ) Is installed. A battery 15 is detachably inserted on the other 12b side. A laser puncture unit 16 is mounted between the battery 15 and the capacitor 13.

  A finger pad 17 is provided on one side surface 12 c in the longitudinal direction of the housing 12. The finger pad 17 is disposed so as to block the irradiation axis of the laser beam emitted from the laser puncture unit 16. In addition, a puncture button 16a for issuing a drive command to the laser puncture unit 16 is disposed at a corner portion (upper right in FIG. 1) of the other side surface 12d. The housing 12 has a size that can be held with one hand (see FIG. 4).

  A terminal 15a for charging the battery 15 is provided on the side 12b (the lower side in FIG. 1) on which the battery 15 in the housing 1 is mounted, and the laser puncture device 11 is connected to the cradle (FIG. The terminal 15a and the terminal of the cradle are brought into contact with each other to be charged.

  A laser cover 18 is provided so as to surround the finger rest 17. The laser cover 18 is slidably provided, and is provided with a power switch (not shown) that detects “open” of the laser cover and supplies power to the high voltage generation circuit 14.

  As described above, the capacitor 13 and the battery 15 are arranged with the laser puncture unit 16 in between, and the distance between the positive terminal 13c of the capacitor 13 and the battery 15 is at least the distance of the laser puncture unit 16. Will just leave. Accordingly, the distance between the terminals 13c and 13d of the capacitor 13 where the high voltage is exposed and the low voltage battery 15 is separated by at least the laser puncture unit 16, and the battery 15 and the terminal 13c of the capacitor 13 or the battery 15 are separated from each other. Sparks can be avoided between the terminals 13d.

  A heavy capacitor 13 is disposed on one side 12a of the rectangular parallelepiped casing 12, and another heavy battery 15 is disposed on the other 12b side of the rectangular parallelepiped casing 12. Is the approximate center of the housing 12 having a rectangular parallelepiped shape. Therefore, the center of gravity is approximately at the center of the housing 12, and a stable operation can be performed during the laser puncturing operation.

  Furthermore, since the capacitor 13, the laser puncture unit 16, and the battery 15 constituting the main components can be efficiently arranged in parallel in the housing 12, the laser puncture device 11 can be downsized. Furthermore, the capacitor 13 is not a single large-capacity capacitor having a large size, but the large-capacitance capacitor 13 is realized by the combined capacitance of the small-capacitance capacitors 13a and 13b.

  FIG. 2 is a perspective view of the laser puncture device 11 with the laser cover 18 closed. Since the laser cover 18 is closed, the finger pad 17 is covered with the laser cover 18. Since the laser cover 18 is provided, the laser beam 16b (see FIG. 5) is not emitted outside the housing 12 and is safe. In addition, the laser cover 18 is closed, so that the size is reduced and the camera is convenient to carry. Reference numeral 20 denotes an operation unit provided in the housing 12, which adjusts the puncture depth (laser output) by the laser puncture unit 16.

  FIG. 3 is a perspective view of the laser puncture device 11 in a state where the laser cover 18 is pulled out. Since the laser cover 18 is pulled out, the finger pad portion 17 is exposed and appears. By pulling out the laser cover 18, the power switch 19 (see FIG. 5) is turned on, and power is supplied to the high voltage generation circuit 14. When the laser cover 18 is closed, the power switch 19 is turned off, and the power supply of the high voltage generation circuit 14 is turned off. As described above, since the power source is turned on / off in conjunction with the opening / closing of the laser cover 18, the operation is easy and the battery is not wasted.

  FIG. 4 is a front view showing a state in which the laser cover 18 is pulled out and the laser puncture device 11 is gripped by the right hand 7a. By pulling out the laser cover 18, a space 18 a is formed between the laser cover 18 and the finger pad portion 17. The ring finger 8d is inserted into the space 18a, and the ring finger 8d is brought into contact with the finger contact portion 17. Then, the puncture button 16a is pressed with the thumb 8a. By pressing the puncture button 16a, laser light (see FIG. 5) is emitted and the ring finger 8d is punctured. Thus, in a state where the laser puncture device 11 is grasped with one hand, both pressing of the puncture button 16a and blood collection from the contacted skin can be performed. Therefore, it can be easily operated under a table or the like without being conscious of human eyes.

  Note that the hand holding the laser puncture device 11 is not necessarily the right hand 7a, and may be the left hand. Further, the finger 8 to be punctured does not need to be the ring finger 8d, and may be another finger 8. In short, blood can be collected with any finger of the left and right hands.

  FIG. 5 is a block diagram of the laser puncture unit 16 and the high voltage generation circuit 14 that supplies a high voltage to the laser puncture unit 16. The high voltage generation circuit 14 includes a booster circuit 14a connected from the battery 15 via the power switch 19, a capacitor 13 (13a, 13b) connected to the output of the booster circuit 14a, and a positive terminal 13c of the capacitor 13 The trigger switch 14b is connected to the trigger switch 14b, and the trigger circuit 14c is connected to the output of the trigger switch 14b. Since the capacitor 13 requiring a large capacity has a large shape, a large capacity is realized by a combined capacity of the capacitor 13a and the capacitor 13b connected in parallel.

  Further, both terminals 13 c and 13 d of the capacitor 13 are connected to both electrodes of the light emitting lamp 16 c constituting the laser puncture unit 16. The output of the trigger circuit 14c is connected to the trigger electrode of the light emitting lamp 16c.

  Two capacitors 13 having a capacitance of 270 μF and a withstand voltage of 350 V are used in parallel to realize a large-capacitance capacitor 13 having a capacitance of 440 μF. An IGBT (insulated gate bipolar transistor) is used for the trigger switch 14b. The trigger switch 14b is turned on by the output of the puncture button 16a.

  The laser puncture unit 16 is provided with a flash lamp 16c, a laser rod 16d provided in the vicinity of the flash lamp 16c and formed of Er: YAG (yttrium, aluminum, garnet), and a front of the laser rod 16d. And a lens 16e. A total reflection mirror 16f is attached to the rear of the laser rod 16d, and a partial transmission mirror 16g is attached to the front. The flash lamp 16c and the laser rod 16d are covered with a cover (not shown) whose inner surface is a mirror surface and whose section is an ellipse. A flash lamp 16c and a laser rod 16d are disposed at the focal position of the ellipse of the cover. This is for efficiently supplying the light emitted from the flash lamp 16c to the laser rod 16d. The cover and the lens 16e are positioned by a resin casing (not shown).

  Next, operations of the high voltage generation circuit 14 and the laser puncture unit 16 will be described. The voltage supplied from the battery 15 is supplied to the booster circuit 14 a via the power switch 19 and boosted by the booster circuit 14 a to charge the capacitor 13. The charging voltage can be controlled by the booster circuit 14a from the operation unit 20, the laser output can be controlled by controlling the charging voltage, and the puncture depth can be adjusted. The voltage charged in the capacitor 13 is supplied to both electrodes of the flash lamp 16c. After this voltage is boosted to a predetermined voltage (300 V or higher), the trigger circuit 14c is activated via the trigger switch 14b when the puncture button 16a is pressed, and the flash lamp 16c emits light. The light emitted from the flash lamp 16c excites Er: YAG in the laser rod 16d to generate laser light. The laser light is amplified while reciprocating between the total reflection mirror 16f and the partial transmission mirror 16g, and a part of the laser light passes through the partial transmission mirror 16g and is output to the outside of the laser rod 16d. The laser beam 16b output to the outside of the laser rod 16d passes through the lens 16e and the finger pad 17 in a straight line and punctures the skin 9. Blood 10 exudes from the punctured skin 9.

(Embodiment 2)
FIG. 6 is a cross-sectional view of blood test apparatus 25 in the second 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.

  Blood test apparatus 25 according to Embodiment 2 takes blood collected by a laser puncture apparatus into blood sensor 30 (see FIGS. 10 to 12) on the spot and calculates a blood sugar level. Accordingly, blood sampling and blood glucose level calculation can be performed in a single operation (one-step operation).

  In FIG. 6, reference numeral 26 denotes a rectangular parallelepiped casing (corresponding to the casing 12 in the first embodiment), and an electric circuit portion 27 is mounted on one side 26 a of the casing 26. The electric circuit section 27 includes a high voltage generation circuit 14 (see FIG. 5) including a large-capacitance capacitor 13 (13a, 13b) as components and a measurement circuit section 28 (see FIG. 13). A battery 15 is detachably inserted on the other 26b side. A laser puncture unit 16 is mounted between the battery 15 and the capacitor 13. A display unit 29 is attached to one side 26 a of the housing 26.

  A finger pad 23 (corresponding to the finger pad 17 in the first embodiment) is provided on one side surface 26c of the casing 26 in the longitudinal direction. This finger pad 23 is provided corresponding to the laser puncture unit 16. A blood sensor 30 (see FIGS. 10 to 12) is disposed between the finger pad 23 and the laser puncture unit 16, and the blood sensor 30 is a sensor connector that is rotatably attached to the housing 26. 47 is detachably mounted. A laser cover 18 is provided so as to surround the finger rest 23. The laser cover 18 is slidably provided, and a power switch (not shown) for detecting “open” of the laser cover 18 and supplying electric power to the electric circuit unit 27 is provided.

  In addition, a puncture button 16 a that issues a drive command to the laser puncture unit 16 is disposed at an upper corner of the other side surface 26 d of the housing 26. The housing 26 is of a size that can be grasped by hand (see FIG. 9).

  As described above, the blood test apparatus 25 according to the present embodiment includes the blood sensor 30 and the measurement circuit unit 28. Therefore, the blood glucose level can be obtained from collection of the blood 10 (see FIG. 15) in one operation. In addition to the features that can be calculated, it has the same features as the laser puncture device.

  FIG. 7 is a front view of blood test apparatus 25 with laser cover 18 closed, and FIG. 8 is a perspective view of blood test apparatus 25 with laser cover 18 pulled out. Between the laser cover 18 and the housing 26, a finger pad 23 and a sensor connector 47 for mounting the blood sensor 30 are rotatably mounted.

  Reference numeral 24 denotes an operation unit. The operation unit 24 performs operations for adjusting the puncture depth (laser output) and displaying the blood sugar level data stored in the memory on the display unit 29.

  FIG. 9 is a cross-sectional view in a state where the laser cover 18 is pulled out and the blood test apparatus 25 is gripped by the right hand 7a. By pressing the puncture button 16a with the thumb 8a, the laser puncture unit 16 emits laser light 16b (see FIG. 13). The laser beam 16b travels in a straight line through a reservoir 34 (see FIGS. 10 to 12) formed in the blood sensor 30 and a hole 23a formed in the finger pad 23, and the skin 9 ( Puncture (see FIG. 15). Blood 10 (see FIG. 15) exudes from the punctured skin 9. This blood 10 is taken directly into the blood sensor 30. Therefore, not only is the amount of waste of the exuded blood 10 small, but there is little contamination with blood to other places, and it can be sanitized.

  FIG. 10 is a cross-sectional view of blood sensor 30 inserted into sensor connector 47. The blood sensor 30 includes a substrate 31, a spacer 32, and a cover 33. Reference numeral 34 denotes a storage portion provided so as to penetrate substantially the center in the width direction of the substrate 31.

  Reference numeral 35 denotes a supply path for blood 10 having one end connected to the storage section 34, and a path for guiding the blood 10 stored in the storage section 34 to the detection section 37 all at once by capillary action. The other end of the supply path 35 is connected to the air hole 38.

  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. 11) constituting the detection part 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 subjected to laser processing to detect electrodes 41 to 45 (see FIG. 11) and the detect electrodes 41 to 41. Connection electrodes 41 a to 46 a respectively led out from 45 are integrally formed.

  FIG. 11 is a perspective plan view of blood sensor 30. Connection electrodes 41 a to 46 a are formed at one end of blood sensor 30. An identification portion 46 formed of a conductor pattern is formed between the connection electrode 43a and the connection electrode 46a.

  On the supply path 35, the detection electrode 44 connected to the connection electrode 44a in order from the storage portion 34 side, the detection electrode 45 connected to the connection electrode 45a, the detection electrode 43 connected to the connection electrode 43a, and the connection A detection electrode 41 connected to the electrode 41a and a detection electrode 42 connected to the connection electrode 42a are provided. A reagent 40 (see FIG. 10) is placed on the detection electrodes 41 and 43. Whether or not blood sensor 30 is attached to sensor connector 47 can be identified based on whether or not there is electrical continuity between connection electrode 43a and connection electrode 46a.

  Further, by changing the electric resistance value of the identification unit 46, it is possible to store information on the calibration curve to be used or store manufacturing information. Therefore, a more precise blood test can be performed using these pieces of information.

  FIG. 12 is a perspective view of blood sensor 30 having a rectangular shape and formed of a plate. 30a and 30b are notches formed by notching the corners on the connection electrodes 41a to 46a side of the blood sensor 30, and facilitate insertion into the sensor connector 47 (see FIG. 8) of the blood sensor 30. It is.

  Since it is configured as described above, when the blood 10 flows into the reservoir 34, the blood 10 passes through the detection electrodes 45, 43, and 41 in order through the supply path 35 by capillary action and onto the detection electrode 42. Led. By guiding the blood 10 to the detection electrode 42, it can be detected that sufficient blood 10 has reached the detection electrodes 41 and 43 that constitute the detection unit 37 located in front of the detection electrode 42. This blood 10 reacts with the reagent 40. The reaction result is guided to the connection electrodes 41a and 43a.

  FIG. 13 is a block diagram of the electric circuit unit 27 and its periphery. The electric circuit unit 27 includes a measurement circuit unit 28 and a high voltage generation circuit 14.

  In FIG. 13, connection electrodes 41a to 46a of blood sensor 30 are connected to switching circuit 28a via sensor connectors 47 (47a to 47e) shown in FIG. The output of the switching circuit 28a is connected to the input of the current / voltage converter 28b. The output is connected to the input of the arithmetic unit 28d via an analog / digital converter (hereinafter referred to as A / D converter) 28c. The output of the calculation unit 28d is connected to a display unit 29 and a transmission unit 28e made of liquid crystal. A reference voltage source 28f is connected to the switching circuit 28a.

  28g is a control unit, and the output of the control unit 28g is connected to the high voltage generation circuit 14 connected to the laser puncture unit 16, the control terminal of the switching circuit 28a, the calculation unit 28d, and the transmission unit 28e. ing. Further, the puncture button 16a, the operation unit 24, the timer 28k, the connector 47a (but commonly used), and the connector 47f are connected to the input of the control unit 28g.

  First, measurement of blood glucose level will be described. When the puncture button 16a is pressed, the control unit 28g turns on the trigger switch 14b (see FIG. 5) of the high voltage generation circuit 14. When the trigger switch 14b is turned on, laser light 16b is emitted from the laser puncture unit 16 and punctures the skin 9. Blood 10 exudes from the skin 9 by puncturing the skin 9. Then, the exuded blood 10 is measured.

  In the measurement operation, first, it is detected whether or not the blood 10 flows into all the detection electrodes 41 to 45. That is, the switching circuit 28a is switched to connect the detection electrode 41 to the current / voltage converter 28b. Further, a detection electrode 42 serving as a detection electrode for detecting the inflow of blood 10 is connected to the reference voltage source 28f. Then, a constant voltage is applied between the detection electrode 41 and the detection electrode 42 (voltage application means).

  In this state, when blood 10 flows in, a current (also referred to as a response current) flows between detection electrodes 41 and 42. This current is converted into a voltage by the current / voltage converter 28b, and the voltage value is converted into a digital value by the A / D converter 28c. And it outputs toward the calculating part 28d. The calculation unit 28d detects that the blood 10 has sufficiently flowed based on the digital value.

  Next, glucose, which is a blood component, is measured. In the measurement of the glucose component amount, first, the switching circuit 28a is switched by a command from the control unit 28g, and the detection electrode 41 serving as a working electrode for measuring the glucose component amount is connected to the current / voltage converter 28b. In addition, a detection electrode 43 serving as a counter electrode for measuring the glucose component amount is connected to the reference voltage source 28f.

  Then, a current (also referred to as response current) flows between the detection electrodes 41 and 43. This current is converted into a voltage by the current / voltage converter 28b, and the voltage value is converted into a digital value by the A / D converter 28c. And it outputs toward the calculating part 28d. The computing unit 28d converts it into a 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 28a is switched by a command from the control unit 28g. Then, the detection electrode 45 serving as a working electrode for measuring the Hct value is connected to the current / voltage converter 28b. Further, the detection electrode 41 serving as a counter electrode for measuring the Hct value is connected to the reference voltage source 28f.

  Next, a constant voltage is applied between the detection electrodes 45 and 41 from the current / voltage converter 28b and the reference voltage source 28f in accordance with a command from the control unit 28g (voltage applying means). A current (also referred to as a response current) flowing between the detection electrodes 45 and 41 is converted into a voltage by the current / voltage converter 28b, and the voltage value is converted into a digital value by the A / D converter 28c. And it outputs toward the calculating part 28d. The calculation unit 28d converts the Hct value based on the digital value.

  Using the Hct value and the glucose component amount obtained by 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 29. To display. Which calibration curve or calibration curve table is used is determined based on the identification unit 46 in the blood sensor 30.

  As described above, the measurement of glucose has been described as an example. However, the reagent 40 of the blood sensor 30 can be exchanged, and in addition to the measurement of glucose, the measurement can be applied to the measurement of blood components such as lactate and cholesterol.

  FIG. 14 is an operation flowchart of a blood test using the blood test apparatus 25 (see FIG. 6). First, in step 51, the laser cover 18 (see FIG. 7) is slid and opened. When the laser cover 18 is “opened”, the power is turned on. Next, the process proceeds to step 52. In step 52, the finger pad 23 (see FIG. 8) and the sensor connector 47 (see FIG. 8) are rotated and opened. Then, blood sensor 30 (see FIG. 8) is inserted into sensor connector 47. The insertion detection of the blood sensor 30 is performed by the conduction of the identification unit 46 (see FIGS. 11 and 12). Next, the process proceeds to step 53. In step 53, the finger rest 23 and the sensor connector 47 are rotated and returned to their original positions. Then, the ring finger 8d is inserted into the space 18a (see FIG. 9) and brought into contact with the finger pad 23.

  Next, the process proceeds to step 54. In step 54, the puncture button 16a (see FIG. 9) is pressed with the thumb 8a (see FIG. 9). By pressing the puncture button 16a, laser light 16b (see FIG. 13) is emitted, and the ring finger 8d (see FIG. 9) is punctured. Blood 10 (see FIG. 5) exudes from the pierced ring finger 8d (see FIG. 9). The exuded blood 10 (see FIG. 5) is taken into the blood sensor 30 (see FIG. 11).

  Next, the process proceeds to step 55. In step 55, blood 10 (see FIG. 5) taken into blood sensor 30 (see FIG. 11) chemically reacts with reagent 40 (see FIG. 10). The result of this reaction is calculated by the measurement circuit unit 28 (see FIG. 13) to determine the blood glucose level. And the result is displayed on the display part 29 (refer FIG. 13). When blood 10 reaches detection electrode 42 of blood sensor 30 (see FIG. 11), a message to that effect is displayed on display 29 (see FIG. 13). If this display is displayed, the process may proceed to step 56. In step 56, the ring finger 8d is removed from the finger rest 23, and the finger rest 23 and the sensor connector 47 (see FIG. 8) are rotated to open, and the blood sensor 30 is removed and discarded. Then, the sensor connector 47 and the finger pad 23 are returned to the original state, and the process proceeds to Step 57. In step 57, the laser cover 18 is closed. The power is turned off by closing the laser cover 18.

  At this time, the calculation result of the blood glucose level is stored in the memory. If the blood glucose level data is not yet stored in the memory when the power is turned off, the power is turned off after the end of these operations. Further, the blood glucose level data may be displayed on the display unit 29 (see FIG. 13) or the puncture depth (laser output) may be adjusted using the operation unit 24 (see FIG. 13) as necessary. it can.

(Embodiment 3)
FIG. 15 is a cross-sectional view of blood test apparatus 60 in the third embodiment. In the third embodiment, the same components as those in the first and second embodiments are denoted by the same reference numerals, and the description is simplified.

  In FIG. 15, reference numeral 61 denotes a rectangular parallelepiped casing (corresponding to the casing 12 in the first embodiment and the casing 26 in the second embodiment). Is attached, and the battery 15 is detachably inserted at a position facing the measurement circuit unit 62. The other 61b side includes a high voltage generation circuit 14 (see FIG. 5) including a large-capacity capacitor 13 as a component. A laser puncture unit 16 is mounted between the battery 15 and the capacitor 13. A display unit 29 is attached to one side 61 a of the casing 61.

  As described above, the measurement circuit unit 62 of the blood test apparatus 60 in the present embodiment is not arranged at a position overlapping with the capacitor 13 and the laser puncture unit 16. Therefore, since the distance between the capacitor 13 and the high voltage generation circuit 14 and the measurement circuit 62 is large, the measurement circuit 62 is affected by noise generated when a high voltage is applied from the capacitor 13 to the laser puncture unit 16. Can be reduced.

  The laser puncture device according to the present invention avoids sparking between the capacitor terminal and the battery, and can reliably perform the puncture operation. Therefore, the laser puncture device used for blood collection or a blood test for examining blood properties Applicable to equipment.

Sectional drawing of the laser puncture apparatus in Embodiment 1 of this invention Same perspective view with laser cover closed Same perspective view with laser cover open Same front view when used Block diagram of laser puncture unit and high voltage generation circuit Sectional drawing of the blood test apparatus in Embodiment 2 Front view with laser cover closed Same perspective view with laser cover open Same as above, sectional view Cross section of blood sensor Same perspective plan view Same perspective view Same as above, block diagram of electrical circuit and its surroundings Same operation flowchart Sectional drawing of the blood test apparatus in Embodiment 3 Sectional view of a conventional laser puncture device Same perspective view in use

DESCRIPTION OF SYMBOLS 11 Laser puncture apparatus 12 Case 12a One 12b The other 13a Capacitor 13b Capacitor 14 High voltage generation circuit 15 Battery 16 Laser puncture unit

Claims (9)

A laser puncture device comprising: a housing; a laser puncture unit disposed inside the housing; and a capacitor and a battery disposed so as to sandwich the laser puncture unit. The laser puncture apparatus according to claim 1, wherein a part of the exterior of the laser puncture unit facing a capacitor terminal is made of at least an insulator. The laser puncture device according to claim 1, wherein the battery is placed on the charger side with respect to the laser puncture unit when the battery is attached to a charger for charging. The laser puncture apparatus according to claim 1, wherein the capacitor generates a high voltage and is used to supply a high voltage to the laser puncture unit. 2. The laser according to claim 1, wherein the housing has a shape that can be grasped with one hand, a finger contact portion is provided so as to block an irradiation axis of the laser beam of the laser puncture unit, and the laser is irradiated toward the finger contact portion. Puncture device. The laser puncture device according to claim 1, wherein at least one capacitor is provided. A blood test apparatus having a blood sensor inserted into the laser puncture apparatus according to claim 6 for measuring a component concentration of a biological sample. The blood test apparatus according to claim 7, wherein the component concentration of the biological sample is a glucose concentration. A voltage applying means for applying a predetermined voltage to the electrodes of the blood sensor; and an electric circuit for calculating a component concentration of the biological sample from a response current from the blood sensor, and The blood test apparatus according to claim 7, wherein a circuit and the capacitor are arranged.

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