JP2009089994A - Laser puncture apparatus and blood test instrument using the same - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To solve the problem that the replacement of a transparent member to prevent a lens from getting stained is troublesome to keep the constant irradiation intensity of laser light. <P>SOLUTION: A blood test instrument comprises a housing 12, a paracentesis opening portion 13 provided in the housing 12, a laser unit 14 provided face to face with the paracentesis opening portion 13, and a transparent member 15a interposed between the laser unit 14 and the paracentesis opening portion 13. The transparent member 15a is shaped into a rotatable disk and rotated by a predetermined amount on the basis of a paracentesis count. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

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

  Hereinafter, a conventional laser puncturing apparatus will be described. FIG. 23 is a cross-sectional view of a conventional laser puncture device and its periphery. A conventional laser puncture apparatus 1 includes a casing 2, a puncture opening 3 provided in the casing 2, a laser unit 4 provided to face the puncture opening 3, and the laser unit 4 and the puncture opening. It was comprised with the transparent member 5 provided between the parts 3. FIG.

  The operation of the laser puncture apparatus 1 configured as described above will be described below. When the laser beam 4a is emitted from the laser unit 4, the laser beam 4a penetrates (transmits) the lens 6 and the transparent member 5, and punctures the skin 9 of the patient. When the skin 9 is punctured, the transpiration material 7 evaporates from the skin 9 first. Thereafter, blood 10 exudes from the punctured skin 9.

  When the transpiration material 7 evaporated from the skin 9 adheres to the lens 6, the irradiation intensity of the laser beam 4a is attenuated. Therefore, the transparent member 5 is inserted in a replaceable manner. That is, the vaporized matter 7 is adhered to the transparent member 5 before adhering to the lens 6 to protect the lens 6 from contamination.

  However, even if the transpiration material 7 adheres to the transparent member 5, the irradiation intensity of the laser beam 4a is also attenuated for the same reason. In order to prevent the attenuation of the irradiation intensity, the transparent member 5 is detachably provided, and is replaced with a new transparent member 5 every time the skin is punctured or a predetermined number of times of puncture.

  FIG. 24 is a plan view showing a state of the transpiration material 7 attached to the transparent member 5 when puncturing is performed about 10 times with the laser beam 4a. By puncturing about 10 times in this manner, the transmission performance of the laser light 4a is reduced by about 10%, so that the transparent member 5 needs to be replaced.

As prior art document information related to the invention of this application, for example, Patent Document 1 is known.
US Pat. No. 5,993,439

  However, in such a conventional laser puncture apparatus 1, it is necessary to replace the transparent member 5 with a new one every time a predetermined number of punctures are performed, and the replacement is troublesome.

  The present invention solves such a problem, and an object of the present invention is to provide a laser puncture apparatus in which the number of times of replacement of a transparent member is reduced or unnecessary.

  In order to achieve this object, the transparent member of the laser puncture device of the present invention has a rotatable point-symmetric shape and rotates the transparent member by a predetermined angle based on the number of punctures. Thereby, the intended purpose can be achieved.

  As described above, the transparent member of the laser puncture apparatus of the present invention is a rotatable point-symmetric shape and rotates the transparent member by a predetermined angle based on the number of punctures. Since the unused portion is used by rotating, the number of replacement of the transparent member can be remarkably reduced or made unnecessary without attenuating the irradiation intensity of the laser beam by the transpiration material. Therefore, the trouble of replacing the transparent member is significantly reduced.

(Embodiment 1)
Hereinafter, embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a cross-sectional view of laser puncture apparatus 11 in the first embodiment. In FIG. 1, reference numeral 12 denotes a housing made of resin and having a substantially rectangular parallelepiped shape, and a puncture opening 13 is formed on one side of the housing 12. A laser unit 14 is attached to face the puncture opening 13, and a transparent unit 15 is attached between the laser unit 14 and the puncture opening 13. In addition, a drive unit 16 is provided in connection with the transparent unit 15.

  The skin 9 to be collected is brought into contact with the puncture opening 13, and the laser light 14 a is irradiated from the laser unit 14 so as to penetrate the transparent unit 15 and puncture the skin 9 in a straight line. That is, the laser unit 14 is disposed to face the puncture opening 13, and the transparent unit 15 is disposed between the laser unit 14 and the puncture opening 13. The puncture opening 13 is preferably provided with a lid (cover) for closing the puncture opening 13 except during laser irradiation.

  Hereinafter, the transparent unit 15 will be described. A disk-shaped transparent member 15a is rotatably mounted on the transparent unit 15. In addition, you may provide this transparent member 15a so that replacement | exchange is possible. The transparent member 15a is formed of a translucent fluorine-based resin (PFA, FEP, PTFE, etc.), and is fixed to the rotating shaft 15b. The rotary shaft 15b is rotatably mounted by a gear 15d in the casing 15c of the transparent unit 15. The rotary shaft 15b is connected to the drive unit 16, and the transparent member 15a is rotated by the drive unit 16.

  The laser beam 14a passes through the circumference of the transparent member 15a. Reference numeral 14b denotes a lens disposed on the optical axis of the laser beam 14a, which is mounted between the laser unit 14 and the transparent member 15a. Its function is to focus the laser beam 14 a on the skin 9. The lens 14b may be provided in the laser unit 14.

  The transparent member 15a has a diameter of 24 mm as shown in FIG. The laser beam 14a penetrates (transmits) through a circle 15e having a diameter of 2 mm for every puncture on the circumference of the transparent member 15a. Each time the laser beam 14a penetrates, the transpiration material 7 evaporated from the skin 9 adheres to the circle 15e and protects the lens 14b from dirt.

  Thus, since the transpiration material 7 adheres in the circle 15e, the lens 14b is not soiled. Even if a single circle 15e is irradiated with the laser beam 14a several times to about 10 times, its transmission performance hardly deteriorates. Further, when the inside of the circle 15e becomes dirty with the transpiration material 7 and the laser beam 14a is at a level that deteriorates, the transparent member 15a can be rotated by the drive unit 16 and moved to the next circle 15e. This prevents the strength of the material from decreasing, and reduces or eliminates the troublesome replacement of the transparent member 15a.

  About 30 circles 15e can be formed on the circumference of the transparent member 15a. Therefore, the single transparent member 15a can be used about 300 times in total. The rotation control of the transparent member 15a by the driving unit 16 may be used for a total of 300 punctures by rotating each time of puncture, or after irradiating one circle 15e several times to about 10 times, The rotation may be controlled to the circle 15e and used for a total of 300 punctures.

  As described above, since the unused portion of the transparent member 15a is used for each puncture or based on the number of punctures, the number of replacements of the transparent member 15a can be remarkably reduced without attenuating the laser beam 14a by the transpiration material 7. Can be reduced. Therefore, the trouble of replacement is significantly reduced. Note that the service life can be further extended by making the transparent member 15a replaceable.

(Embodiment 2)
The second embodiment is different from the first embodiment in that a transparent unit 21 (corresponding to the transparent unit 15 in the first embodiment) is equipped with a cleaner portion 21a for cleaning the transparent member 15a. The same parts as those in the first embodiment are denoted by the same reference numerals, and the description is simplified. The same applies to the following embodiments.

  As shown in FIG. 3, the transparent unit 21 according to the second embodiment has a cleaner portion 21a fixedly attached to the lower side (the puncture opening 13 side) of the transparent member 15a. As shown in FIG. 5, a triangular notch 21b through which the laser beam 14a passes is formed in the cleaner portion 21a, and a cleaner 21c is attached to the upper surface thereof.

  The cleaner 21c is disposed so as to contact the circle 15e of the transparent member 15a. Therefore, when the transparent member 15a rotates, the circle 15e is cleaned by the cleaner 21c and the transpiration material 7 is wiped off. By this cleaner 21c, the transparency of the circle 15e is maintained. Accordingly, it is not necessary to replace the transparent member 15a.

  3 and 4, the laser beam 14a penetrates the skin 9 through the lens 14b, the transparent member 15a, the notch 21b of the cleaner 21a, and the puncture opening 13.

(Embodiment 3)
The third embodiment is different from the first embodiment in that the transparent unit 22 (corresponding to the transparent unit 15 in the first embodiment) is provided with an eccentric portion 22a that decenters the center of the transparent member 15a.

  In FIG. 6, an eccentric portion 22a that eccentrically rotates the rotating shaft 15b of the transparent member 15a is mounted below the transparent member 15a. By moving the rotating shaft 15b using the eccentric portion 22a, the laser beam 14a penetrates the circle 15e on the first circumference or the circle 15f on the second circumference as shown in FIG. It can be used as a transparent member. Therefore, it is possible to use about 300 times in the circle 15e on the first circumference, about 300 times in the circle 15f on the second circumference, and 600 times in total, and use the transparent member 15a. The service life can be extended about twice.

  FIG. 8 is a plan view of the eccentric portion 22a. 22c is a rotation center of the eccentric plate 22d, and 22e is a bearing portion of the rotation shaft 15b of the transparent member 15a.

  FIG. 9A is a cross-sectional view of the eccentric portion 22a in the first state, and the laser light 14a passes through a circle 15e formed on the first circumference of the transparent member 15a. After all the circles 15e formed on the first circumference are contaminated with the transpiration product 7, the eccentric plate 22d is rotated 180 degrees to the state shown in FIG. 9B. FIG. 9B is a cross-sectional view of the eccentric portion 22a in the second state, and the laser light 14a passes through a circle 15f formed on the second circumference of the transparent member 15a. In this way, the service life of the transparent member 15a is extended approximately twice.

(Embodiment 4)
In the fourth embodiment, the transparent member 23a (corresponding to the transparent member 15a in the first embodiment) in the transparent unit 23 (corresponding to the transparent unit 15 in the first embodiment) can be easily replaced. Is different.

  In FIG. 10, the transparent member 23a is accommodated in the protective cover 23b. The protective cover 23b has holes 23c and 23d through which the laser light 14a passes. The holes 23c and 23d are provided corresponding to a circle 23e (corresponding to the circle 15e in the first embodiment) formed on the first circumference forming the transparent member 23a.

  The transparent member 23a is formed of a thick member, and teeth 23f to which the rotational driving force is transmitted are formed on the outer peripheral edge thereof. The teeth 23f are exposed on the side opposite to the holes 23c and 23d formed in the protective cover 23b. Reference numeral 23g denotes a rotating shaft, which is fitted in a hole 23h provided in the protective cover 23b and is rotatably stored. In the present embodiment, since the transparent unit 23 is housed in the protective cover 23b, it can be easily connected to and detached from the drive unit 16 and can be easily replaced.

  FIG. 11 shows the connection of the transparent unit 23 to the drive unit 16. FIG. 11A is a cross-sectional view, in which teeth 23f mesh with a gear 23j connected to the drive unit 16, and the power of the drive unit 16 is transmitted to the transparent member 23a. FIG. 11B is a plan view thereof, and the transparent member 23a rotates in the direction of the arrow 24b when the gear 23j rotates in the direction of the arrow 24a.

  In addition, there exists a structure shown in FIG. 12, FIG. 13 as another example which transmits the rotational force by the gearwheel 23j to the transparent member 23a. That is, in FIG. 12, the gear 23k is mounted on the rotating shaft 23g of the transparent member 23p (corresponding to the transparent member 23a), and the gear 23k is rotated by the gear 23j. As shown in FIG. 13, a lotus gear (corresponding to the gear 23k) 23m and a lotus gear 23n (corresponding to the gear 23j) meshing with the lotus gear 23m are used. The transparent member 23a may be rotated by rotating it. In these cases, since the rotating shaft 23g is rotated to transmit the driving force, the transparent member 23p can be thinned.

(Embodiment 5)
The fifth embodiment is different in that the transparent member 25a in the transparent unit 25 (corresponding to the transparent unit 15 in the first embodiment) can be realized at a lower price than the transparent member 23a in the fourth embodiment.

  The transparent member 25a is formed of a thick member (the material is the same as that of the transparent member 15a), and a rotation shaft 25b is mounted at the center. Further, teeth 25c are formed on the outer peripheral edge. Holes 25d and 25e are formed on the upper and lower surfaces on the outer periphery of the transparent member 25a so as to face each other. The holes 25d and 25e are provided at positions corresponding to the circle 15e in the first embodiment. By forming the holes 25d and 25e, a transmitting portion 25f of the laser beam 14a formed by a thin member that transmits the laser beam 14a is formed between the holes 25d and 25e.

  In the present embodiment, since the protective cover 23b used in the fourth embodiment is not necessary, the price can be reduced.

(Embodiment 6)
The sixth embodiment is different in that the transparent member 25a in the transparent unit 26 (corresponding to the transparent unit 25 in the fifth embodiment) can be easily formed as compared with the transparent member 25a in the fifth embodiment.

  In FIG. 15, a rotating shaft 26b is provided at the center of a disk-shaped transparent member 26a, and teeth 26c for applying a rotational driving force to the transparent member 26a are formed at the circumferential edge. Further, through holes 26d are formed at the positions of the holes 25d and 25e in the fifth embodiment. A film 26e is attached to the upper surface of the through hole 26d. The material of the film 26e is the same material as the transparent member 15a. In the present embodiment, a through-hole 26d is provided in the passage of the laser beam 14a, and the film 26e is attached to the upper surface (the lens 14b side), so that it is not necessary to provide the opposed holes 25d and 25e. Becomes easy.

(Embodiment 7)
In the seventh embodiment, the mounting relationship of the transparent unit 25 (the same applies to the transparent units 15, 21, 22, 23, and 26) to the laser unit 14 will be described.

  In FIG. 16A, a transparent unit 25 is attached to the radiating portion of the laser light 14 a of the laser unit 14. One of the rotating shafts 25b of the transparent member 25a is rotatably inserted into the first bearing 25h constituting the transparent unit 25. The other of the rotation shafts 25b is rotatably supported by the second bearing 25j. The second bearing 25j is fitted with a gear 23j that meshes with teeth 25c formed on the edge of the transparent member 15a. The gear 23j is connected to the drive unit 16 (see FIG. 1). Yes.

  FIG. 16B is a plan view of the first bearing 25h and its periphery as seen from above. In FIG. 16B, a hole 25k through which the laser beam 14a passes is provided in one of the first bearings 25h (on the opposite side of the gear 23j), and a lens 14b is mounted in the hole 25k. Yes.

  FIG. 16C is a plan view of the second bearing 25j and its periphery as viewed from below. In FIG. 16 (c), one of the second bearings 25j (on the opposite side of the gear 23j) is provided with a cut 25m for inserting the rotating shaft 25b attached to the transparent member 25a in the horizontal direction from the outside. . The laser beam 14a passes through the dotted line 25n at the tip of the cut 25m.

  Next, the laser unit 14 will be described with reference to FIG. In the oscillation tube 14c constituting the laser unit 14, an Er: YAG (yttrium, aluminum, garnet) laser crystal 14e and a flash light source 14f (an example of a light source) are stored. A partial transmission mirror 14g having a transmittance of about 1% is attached to one end of the oscillation tube 14c, and a total reflection mirror 14h is attached to the other end. A convex lens 14b is mounted in front of the partial transmission mirror 14g, and is set so that the laser beam 14a is focused on the patient's skin.

  The operation of the laser unit 14 configured as described above will be described below. The puncture button 14j (see FIG. 21) is pressed. Then, the flash light source 14f emits light. The light emitted from the flash light source 14f enters the Er: YAG laser crystal 14e, where it is reflected and amplified while being reflected between the total reflection mirror 14h, the YAG laser crystal 14e, and the partial transmission mirror 14g. . A part of the amplified laser beam passes through the partial transmission mirror 14g by stimulated emission. The laser light 14 a that has passed through the partial transmission mirror 14 g is emitted through the lens 14 b and focused under the skin 9. The depth of focus when puncturing is suitably 0.1 mm to 1.5 mm from the skin 9, and is 0.5 mm in the present embodiment.

(Embodiment 8)
In the eighth embodiment, blood test apparatus 51 using laser puncture apparatus 11 described in the first to seventh embodiments will be described.

  FIG. 17A is a cross-sectional view of the blood test apparatus 51 viewed from the side. In FIG. 17A, when blood test apparatus 51 is viewed from the side, puncture portion 53 (corresponding to puncture opening portion 13 in the first embodiment) provided on one side of main body portion 52a, and puncture portion 53 The laser unit 14 provided opposite to the laser unit 14 and the transparent unit 25 provided between the laser unit 14 and the puncture unit 53 (this is the transparent units 15, 21, 22, 23 described in the first to seventh embodiments). , 26), and a drive unit 16 connected to the transparent unit 25 is disposed.

  Further, when this blood test apparatus 51 is viewed from the first front, as shown in FIG. 17B, a main body 52a and a lid 52b provided so as to be rotatable at the main body 52a and the fulcrum 52c. It is configured. The opening / closing of the lid 52b is detected by an opening / closing sensor 52d (see FIG. 17C).

  A blood sensor (hereinafter referred to as a sensor) 55 (see FIGS. 18, 19, and 20) is stacked and housed in the main body 52a, and a detachable sensor cartridge 54, and a sensor outlet provided below the sensor cartridge 54 54a, a puncture portion 53 connected to the sensor outlet 54a and provided at the corner of one side of the main body 52a, a laser unit 14 provided opposite to the puncture portion 53, and the laser unit 14 And a transparent unit 25 provided between the puncture unit 53 and the puncture unit 53. Reference numeral 54 c denotes a desiccant stored in the sensor cartridge 54. The desiccant 54c prevents the reagent (see FIG. 18) placed in the sensor 55 from deteriorating due to moisture.

  Here, the puncture portion 53 includes an upper holder 53a and a lower holder 53b, and is connected to the sensor outlet 54a and provided on a straight line. The upper holder 53a is fixed to the main body 52a, and the lower holder 53b is urged toward the upper holder 53a by a leaf spring. Then, the lowermost sensor 55a of the sensors 55 stacked and accommodated in the sensor cartridge 54 is conveyed toward the puncture portion 53 by the slider 54b via the sensor outlet 54a. The sensor 55 conveyed by the slider 54b is inserted and sandwiched between the upper holder 53a and the lower holder 53b.

  When this blood test apparatus 51 is viewed from the second front side, as shown in FIG. 17C, the measurement circuit unit 57 and the battery 58 are accommodated in the main body 52a adjacent to the laser unit 14 and the transparent unit 25. ing. A puncture button 14j is provided on the other surface (upper surface) of the main body 52a.

  17A, 17B, and 17C show a state where the lid 52b is opened. The lid 52b is provided so as to be able to stop at two stages of opening angles with respect to the main body 52a. The stop position by the two-stage opening angle is two stop positions: a first-stage stop position that stops at an opening angle of about 30 degrees and a second-stage stop position that stops at an opening angle of about 90 degrees.

  When the lid 52b is opened, the sensor outlet 54a is opened, and the lowermost sensor 55 in the sensor cartridge 54 is set between the upper holder 53a and the lower holder 53b by the slider 54b.

  In this blood test apparatus 51, the skin 9 (see FIG. 1) is brought into contact with the puncture portion 53 and the puncture button 14j is pressed, whereby the laser light 14a is emitted from the laser unit 14 to puncture the skin 9. It is. At this time, the lid 52b is set at the first stage stop position with an opening angle of about 30 degrees, so that the laser beam 14a does not leak to the outside and is safe. In replacement of the sensor cartridge 54, the sensor cartridge 54 can be easily inserted and removed by setting the lid portion 52b to the second stage stop position with an opening angle of about 90 degrees. Further, by closing the lid portion 52b, even when the blood test apparatus 51 is not used, even if the puncture button 14j is accidentally pressed, the laser light 14a is not emitted to the outside and is safe.

  Hereinafter, the details of each part in the present embodiment will be described. FIG. 18 is a cross-sectional view of the sensor 55. The sensor 55 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 10, and the reservoir 34 includes a substrate hole 31a formed substantially at the center of the substrate 31, and a spacer hole 32a formed in the spacer 32 corresponding to the substrate hole 31a. A cover hole 33a formed in the cover 33 is formed in communication with the substrate hole 31a. Reference numeral 36 denotes a positioning hole that determines the mounting position of the sensor 55 on the puncture portion 53, and is provided through the sensor 55.

  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. 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 10, 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 the solution, and the reagent solution is dropped on the detection electrodes 41 and 43 (see FIG. 19) formed on the substrate 31 and dried. When the reagent 40 absorbs moisture, the performance deteriorates. Therefore, in order to prevent this performance deterioration, the desiccant 54c is accommodated in the sensor cartridge 54.

  Here, 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 formed by laser processing from the detection electrodes 41 to 45 and the detection electrodes 41 to 45. The connection electrodes 41a to 45a and the identification electrode 47a respectively led out are integrally formed.

The substrate 31, spacer 32, and cover 33 are all made of polyethylene terephthalate (PET). Management costs are reduced by sharing materials.
FIG. 19 is a perspective plan view of the sensor 55, and connection electrodes 41a to 45a and an identification electrode 47a are formed at 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 reservoir 10 of blood 10 provided substantially at the center of the sensor cartridge, and a supply path 35 having one end connected to the reservoir 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 sequentially connected to the connection electrode 44a from the reservoir 34, the detection electrode 45 connected to the connection electrode 45a, the detection electrode 44 connected to the connection electrode 44a again, A detection electrode 43 connected to the connection electrode 43a, a detection electrode 41 connected to the connection electrode 41a, a detection electrode 43 connected again to the connection electrode 43a, and a detection electrode 42 connected to the connection electrode 42a are provided. ing. A reagent 40 (see FIG. 18) is placed on the detection electrodes 41 and 43.

  Whether or not the sensor 55 is attached to the puncture portion 53 can be identified based on whether or not there is electrical continuity between the connection electrode 43a and the identification electrode 47a. That is, when the sensor 55 is conveyed to the puncture unit 53, it is detected whether or not the sensor 55 is correctly attached to the puncture unit 53 by detecting electrical continuity between the connection electrode 43a and the identification electrode 47a. Can do. If there is no electrical continuity, the sensor 55 is not attached to the puncture portion 53. In this case, a warning can be displayed on the display unit 60 (see FIG. 21) of the blood test apparatus 51.

  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.

  FIG. 20 is a perspective view of the sensor 55. The sensor 55 is formed of a rectangular plate. A storage section 34 is formed in the approximate center of the plate body, and connection electrodes 41a to 45a and an identification electrode 47a are formed at one end. A positioning hole 36 is formed in the vicinity of the other end. The positioning hole 36 has a trapezoidal shape in which the storage portion 34 side is narrowed. An air hole 38 is formed between the positioning hole 36 and the storage portion 34.

  FIG. 21 is a block diagram of the measurement circuit unit 57 and its vicinity. In FIG. 21, connection electrodes 41a to 45a (see FIG. 19) of the sensor 55 are connected to a switching circuit 57a via connectors 49a to 49e formed on the upper holder 53a. The output of the switching circuit 57a is connected to the input of the current / voltage converter 57b. The output is connected to the input of the arithmetic unit 57d via an analog / digital converter (hereinafter referred to as A / D converter) 57c. The output of the calculation unit 57d is connected to a display unit 60 and a transmission unit 57e made of liquid crystal. A reference voltage source 57f is connected to the switching circuit 57a. The reference voltage source 57f may be a ground potential.

  57g is a control unit, and the output of this control unit 57g is the drive unit 16, the high voltage generation circuit 57h connected to the laser unit 14, the control terminal of the switching circuit 57a, the calculation unit 57d, and the transmission unit 57e. It is connected to the. Further, the open / close sensor 52d, the puncture button 14j, the timer 57k, and the connector 49f are connected to the input of the control unit 57g.

  Hereinafter, the operation of the measurement circuit unit 57 will be described. First, the puncture button 14 j is pressed and the skin 9 is punctured with the laser unit 14. Then, the property of blood 10 exuded by puncture is measured. In the measurement operation, the switching circuit 57a is switched to connect the detection electrode 41 (see FIG. 19) to the current / voltage converter 57b. Further, the detection electrode 42 serving as a detection electrode for detecting the inflow of blood 10 is connected to the reference voltage source 57f. A constant voltage is applied between the detection electrode 41 and the detection electrode 42. In this state, when blood 10 flows in, a current flows between detection electrodes 41 and 42. This current is converted into a voltage by the current / voltage converter 57b, and the voltage value is converted into a digital value by the A / D converter 57c. And it outputs toward the calculating part 57d. The computing unit 57d 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 57a is switched by a command from the control unit 57g, and the detection electrode 41 serving as a working electrode for measuring the glucose component amount is connected to the current / voltage converter 57b. Further, the detection electrode 43 serving as a counter electrode for measuring the glucose component amount is connected to the reference voltage source 57f.

  Note that the current / voltage converter 57b and the reference voltage source 57f are kept off while the glucose in the blood and its oxidoreductase are reacted for a certain time. Then, after a certain time (1 to 10 seconds) has elapsed, 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 57g. Then, a current flows between the detection electrodes 41 and 43. This current is converted into a voltage by the current / voltage converter 57b, and the voltage value is converted into a digital value by the A / D converter 57c. And it outputs toward the calculating part 57d. The computing unit 57d 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 57a is switched by a command from the control unit 57g. Then, the detection electrode 45 serving as a working electrode for measuring the Hct value is connected to the current / voltage converter 57b. Further, the detection electrode 41 serving as a counter electrode for measuring the Hct value is connected to the reference voltage source 57f.

  Next, a constant voltage (2 V to 3 V) is applied between the detection electrodes 45 and 41 from the current / voltage converter 57b and the reference voltage source 57f according to a command from the control unit 57g. The current flowing between the detection electrodes 45 and 41 is converted into a voltage by the current / voltage converter 57b, and the voltage value is converted into a digital value by the A / D converter 57c. And it outputs toward the calculating part 57d. The computing unit 57d 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 with reference to a calibration curve or a calibration curve table obtained in advance, and the corrected result is displayed on the display unit 60. To display. Which calibration curve or calibration curve table is used is determined based on the identification unit 47 in the sensor 55. Further, the calibration curve or the result corrected by the calibration curve table is transmitted from the transmission unit 57e 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.

  If the dose of insulin is automatically set in the injection device by transmitting the measurement data corrected in this way from the transmission unit 57e, the amount of insulin to be administered by the patient is 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.

As described above, the measurement of glucose has been described as an example. However, the reagent 40 of the sensor 55 can be replaced, 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.
Next, a test method using the blood test apparatus 51 will be described with reference to FIG. First, in step 61, the lid 52b of the blood test apparatus 51 is opened. The opening of the lid 52b is detected by an open / close sensor 52d. When the output of the open / close sensor 52d is detected, the high voltage generation circuit 57h is operated to start charging the capacitor with a high voltage. The sensor outlet 54a provided in the sensor cartridge 54 is opened in conjunction with the opening of the lid 52b.

  Next, the process proceeds to step 62. In step 62, the sensor 55 is conveyed by the slider 54b. That is, among the sensors 55 stored in a stacked manner, the lowermost sensor 55 a is conveyed to the puncture unit 53. This conveyance is confirmed by detecting the continuity between the connection electrode 43a of the sensor 55 and the identification electrode 47a. Then, the process proceeds to step 63.

  In step 63, the patient brings the blood test apparatus 51 into contact with the patient's skin 9 and presses the puncture button 14j. Then, the process proceeds to step 64.

  In step 64, the exuded blood 10 is taken into the storage part 34 of the sensor 55 by puncturing the skin 9. The blood 10 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 sugar level of blood 10 is measured.

  When the blood glucose level is measured in step 64, the process proceeds to step 65, where the measured blood glucose level is displayed on the display unit 60, and the puncture number counter in the same transparent unit 25 is counted up. The puncture number counter is reset when the transparent unit 25 is newly attached.

  Then, the process proceeds to step 66. If the puncture count counter is within 10 for one circle 15e (see FIG. 2) in step 66, the routine proceeds to step 67. In step 67, the transparent member 25a is rotated once, and the process proceeds to step 68. In step 68, the lid 52b of the blood test apparatus 51 is closed. The closure of the lid 52b is detected by an open / close sensor 52d. With the closing operation of the lid 52b, the sensor outlet 54a of the sensor cartridge 54 is closed.

  In step 66, if the number of puncture counters exceeds 10 for all the circles 15e on the circumference of the transparent member 25a, the process proceeds to step 69. Then, the display unit 60 is instructed to replace the transparent unit 25, and the process proceeds to step 68.

  As described above, in step 66, since the number of uses of the transparent member 25a is counted and managed so as not to puncture 10 times or more with respect to one circle 15e, the intensity of the laser beam 14a is prevented from being lowered. can do.

  In addition, the number of replacements of the transparent member 25a can be significantly reduced by the rotation control by the drive unit 16. Therefore, the trouble of replacement is significantly reduced.

  Since the laser puncture apparatus according to the present invention can extremely reduce the number of replacements of the transparent member, it can be applied to a blood test apparatus using a laser unit.

Sectional drawing of the laser puncture apparatus in Embodiment 1 of this invention Plan view of transparent member used in the transparent unit Sectional drawing of the principal part of the laser puncture apparatus in Embodiment 2 Top view of the transparent member used in the transparent unit and its vicinity Perspective view of the cleaner Sectional drawing of the principal part of the laser puncture apparatus in Embodiment 3 Plan view of transparent member used in the transparent unit Plan view of the eccentric part Explanatory drawing of the operation, (a) is a sectional view showing the first state, (b) is a sectional view showing the second state. Sectional drawing of the transparent member used for the laser puncture apparatus in Embodiment 4 Explanatory drawing of the transparent member and its periphery, (a) is the same sectional view, (b) is the same plan view Sectional view of the main part of the second example Sectional view of the main part of the third example Explanatory drawing of the transparent member used for the laser puncture apparatus in Embodiment 5, (a) is the same sectional view, (b) is the same plan view Sectional drawing of the transparent member used for the laser puncture apparatus in Embodiment 6 Explanatory drawing of the laser puncture apparatus in Embodiment 7, (a) is the same sectional view, (b) is a plan view seen from the same upper side, (c) is a plan view seen from the lower same Explanatory drawing of the blood test apparatus in Embodiment 8, (a) is sectional drawing seen from the same side surface, (b) is sectional drawing by the same 1st cut surface, (c) is by the 2nd cut surface. Cross section Sectional view of the sensor inserted into the puncture unit Perspective plan view of the sensor External perspective view of the sensor Block diagram of the measurement circuit and its vicinity Flow chart of the inspection method Sectional view of a conventional laser puncture device Top view of transparent member constituting the laser puncture device

Explanation of symbols

12 Housing 13 Puncture opening 14 Laser unit 15a Transparent member

Claims (10)

A housing, a puncture opening provided in the housing, a laser unit provided to face the puncture opening, and a transparent member provided between the laser unit and the puncture opening. A laser puncture apparatus comprising the transparent member having a rotatable point-symmetric shape and rotating the transparent member by a predetermined amount based on the number of punctures. The laser puncture device according to claim 1, wherein the transparent member is cleaned based on the number of punctures. The laser puncture device according to claim 1, wherein the transparent member can be replaced. The laser puncture device according to claim 1, wherein the rotation center of the transparent member can be eccentric. The laser puncture device according to claim 3, wherein the transparent member is housed in a protective cover. The laser puncture apparatus according to claim 1, wherein an outer periphery of the transparent member is formed in a gear shape, and a laser beam transmitting portion is thin. The transparent member is formed of a thick resin, the outer edge of the transparent member is gear-shaped, a plurality of holes are provided in the laser light transmitting part, and a light transmissive film is attached to the hole. Item 4. The laser puncture device according to Item 3. The laser puncture device according to claim 3, wherein the replacement of the transparent member is notified. A blood having a measurement circuit unit using the laser puncture device according to claim 1, wherein a blood sensor is detachably mounted between the transparent member and the puncture opening, and a signal output from the blood sensor is connected thereto. Inspection device. The blood test apparatus according to claim 9, wherein a sensor cartridge in which blood sensors are stacked and housed in a housing is mounted, and blood sensors are transported one by one from the sensor cartridge to the puncture opening each time puncture is performed.

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