Abstract:
Provided is a blood testing apparatus capable of measuring a blood sugar level while keeping the operability, even if the remaining battery life is short. This blood testing apparatus includes a casing ( 12 ) having a cylindrical opening cylinder ( 12   b ), a blood sensor ( 22 ) mounted removably in the opening cylinder ( 12   b ) of the casing ( 12 ) for analyzing the blood, a blood introducing portion ( 34 ) formed in the blood sensor ( 22 ) and having an opening for storing this opening with the blood having flown from the skin by a pierce, a laser emitting device ( 13 ) disposed in the casing ( 12 ) for causing a laser beam to pierce the skin through the inside of the opening cylinder ( 12   b ) of the casing and the opening of the blood introducing portion ( 34 ), and a needle piercing unit ( 18 ) disposed in the casing for piercing the skin with the needle through the opening of the blood introducing portion ( 34 ).

Description:
TECHNICAL FIELD  
       [0001]    The present invention relates to a blood test apparatus for testing the property of blood and the so on. 
       BACKGROUND ART  
       [0002]    Diabetes patients need to measure their blood sugar level on a regular basis and inject insulin based on the measured blood sugar level to maintain a normal blood sugar level. To maintain this normal blood sugar level, diabetes patients need to measure the blood sugar level on a regular basis, and sample a small amount of blood from their fingertips using a blood test apparatus and measure the blood sugar level from the sampled blood 
         [0003]    A shown in  FIG. 1 , a conventional blood test apparatus has: housing  2 ; cylindrical body  2   a  forming this cylindrical body  2 ; puncturing opening part  2   c  provided at the front end of this cylindrical body  2   a ; laser emitting apparatus  3  provided inside cylindrical body  2 ; blood sensor  4  (hereinafter, referred to as “sensor”) that is provided facing this laser emitting apparatus  3  and that has blood guiding part  4   a ; electrical circuit section  5  connected to this blood sensor  4 ; and electric battery  6  that supplies power to this electrical circuit section  5  and laser emitting apparatus  3 . 
         [0004]    The operation of blood test apparatus  1  constituted as described above will be explained below. As shown in  FIG. 2 , for example, blood test apparatus  1  is held by the right hand and is abutted on skin  7  of the left hand. Then, puncturing button  3   b  shown in  FIG. 1  is pressed. Then, laser light  3   a  is emitted from laser emitting apparatus  3 . This laser light  3   a  punctures skin  7 . As a result of this puncturing, blood  8  flows out from skin  7 . This blood  8  is temporarily stored in blood guiding part  4   a  provided in sensor  4 . The blood sugar level of blood  8  stored in this blood guiding part  4   a  is measured in electrical circuit section  5  provided inside blood test apparatus  1 . 
         [0005]    In this way, conventional blood test apparatus  1  uses laser emitting apparatus  3  as a puncturing means and, consequently, there is no burden of replacing the puncturing needle every puncturing. Further, each time electric battery  6  is consumed and its remaining power is decreased, electric battery  6  needs to be replaced with new electric battery (not shown). 
         [0006]    Furthermore, for example, Patent Literature 1 is known as prior art reference information related to the present invention. 
       Citation List 
     Patent Literature 
       [0000]    
       
         PTL 1: Japanese Patent Application Laid-Open No. 2004-533866 
       
     
       SUMMARY OF INVENTION  
     Technical Problem 
       [0008]    However, such conventional blood test apparatus  1  uses laser emitting apparatus  3  and does not need to replace a puncturing needle, but consumes great power. Further, when electric battery  6  is consumed and its remaining power is decreased, puncturing by the laser emitting apparatus is not possible. As a result, the blood sugar level cannot be measured and administering an adequate dose of insulin becomes difficult. Therefore, the disease may be likely to worsen. 
         [0009]    Further, a puncturing method using a simple needle to be used upon emergency has poor operability and unreliability. 
         [0010]    The present invention solves such a problem, and, to measure the blood sugar level without deteriorating the operability even when remaining power of the electric battery is decreased, the object of the present invention is to provide a blood test apparatus formed such that an emergency puncturing means can be mounted. 
       Solution to Problem 
       [0011]    To achieve this object, the blood test apparatus according to the present invention employs a configuration which includes: a housing that has an open body of a cylindrical shape of a cylindrical shape; a blood sensor that can be attached detachably to the open body of a cylindrical shape of the housing and that analyzes blood; a blood guiding part that is formed in the blood sensor, that has an opening part and that stores blood which flows out from skin as a result of puncturing, in the opening part; a laser emitting apparatus that is provided in the housing and that punctures skin by means of laser light which passes an interior of the open body of a cylindrical shape of the housing and the opening part of the blood guiding part and punctures skin; and a needle-puncturing apparatus that is provided in the housing and that punctures skin by means of a needle which passes the opening part of the blood guiding part and punctures skin. 
       Advantageous Effects of Invention 
       [0012]    The present invention can selectively use for a puncturing means a laser emitting apparatus that requires a supply of power or a needle-puncturing apparatus that does not require a supply of power, so that it is possible to measure the blood sugar level without deteriorating the operability even when remaining power of the electric battery is decreased. 
         [0013]    Moreover, the laser emitting apparatus and needle-puncturing apparatus both can puncture skin by means of laser light and a puncturing needle that pass the vicinity of the blood guiding part, and, consequently, perform blood test using the same blood sensor. Accordingly, for example, a blood sensor needs not be prepared separately, and the same blood sensor can be used in both the laser emitting apparatus and needle-puncturing apparatus. That is, even when the puncturing means changes, another blood sensor needs not to be prepared, so that the burden on a user decreases. 
     
    
     
       BRIEF DESCRIPTION OF DRAWINGS 
         [0014]      FIG. 1  is a cross-sectional view of a conventional blood test apparatus; 
           [0015]      FIG. 2  illustrates the state of use of the conventional blood test apparatus; 
           [0016]      FIG. 3  is a cross-sectional view of a blood test apparatus according to Embodiment 1 of the present invention; 
           [0017]      FIG. 4  is a cross-sectional view of a puncturing unit constituting the blood test apparatus according to Embodiment 1 of the present invention; 
           [0018]      FIG. 5  is a cross-sectional view of an A-A line of the puncturing unit according to Embodiment 1 of the present invention; 
           [0019]      FIG. 6  is a perspective view of the puncturing unit according to Embodiment 1 of the present invention; 
           [0020]      FIG. 7  is a cross-sectional view and perspective plan view of a sensor unit according to Embodiment 1 of the present invention; 
           [0021]      FIG. 8  is a plan view of a sensor unit seen from the bottom surface according to Embodiment 1 of the present invention; 
           [0022]      FIG. 9  is an exploded plan view of guiding parts according to Embodiment 1 of the present invention;  FIG. 10  is a cross-sectional view of a sensor according to 
           [0023]    Embodiment 1 of the present invention; 
           [0024]      FIG. 11  is a perspective plan view of the sensor according to Embodiment 1 of the present invention (in case where the sensor is hexagonal); 
           [0025]      FIG. 12  is a plan view of components constituting the sensor according to Embodiment 1 of the present invention; 
           [0026]      FIG. 13  is a cross-sectional view of main parts in the sensor according to Embodiment 1 of the present invention; 
           [0027]      FIG. 14  is a plan view of main parts in the sensor according to Embodiment 1 of the present invention; 
           [0028]      FIG. 15  is a cross-sectional view of the sensor according to Embodiment 1 of the present invention in the first state; 
           [0029]      FIG. 16  is a cross-sectional view of the sensor according to Embodiment 1 of the present invention in the second state; 
           [0030]      FIG. 17  is a cross-sectional view of the sensor according to Embodiment 1 of the present invention in the third state; 
           [0031]      FIG. 18  is a cross-sectional view and perspective plan view of another sensor unit according to Embodiment 1 of the present invention; 
           [0032]      FIG. 19  is a cross-sectional view and perspective plan view of another example of the sensor unit according to Embodiment 1 of the present invention; 
           [0033]      FIG. 20  is a cross-sectional view and perspective plan view of another example of the sensor unit according to Embodiment 1 of the present invention; 
           [0034]      FIG. 21  is a cross-sectional view showing the entire blood test apparatus, to which the puncturing unit mounting the sensor unit shown in  FIG. 7 ,  FIG. 18  and  FIG. 19  is attached, according to Embodiment 1 of the present invention; 
           [0035]      FIG. 22  is a cross-sectional view showing the entire blood test apparatus, to which the puncturing unit mounting the sensor unit shown in  FIG. 20  is attached, according to Embodiment 1 of the present invention; 
           [0036]      FIG. 23  is a cross-sectional view of the laser emitting apparatus constituting the blood test apparatus according to Embodiment 1 of the present invention; 
           [0037]      FIG. 24  is a block diagram showing an electrical circuit section and its vicinity according to Embodiment 1 of the present invention; 
           [0038]      FIG. 25  illustrates the operation according to Embodiment 1 of the present invention; 
           [0039]      FIG. 26  is a cross-sectional view of the blood test apparatus according to Embodiment 2 of the present invention; 
           [0040]      FIG. 27  is a cross-sectional view of the blood test apparatus according to Embodiment 3 of the present invention; 
           [0041]      FIG. 28  is a cross-sectional view of the blood test apparatus according to Embodiment 4 of the present invention; and 
           [0042]      FIG. 29  is a cross-sectional view of the blood test apparatus according to Embodiment 5 of the present invention. 
       
    
    
     DESCRIPTION OF EMBODIMENTS  
       [0043]    Hereinafter, embodiments of the present invention will be explained based on the accompanying drawings. 
       Embodiment 1 
       [0044]      FIG. 3  is a cross-sectional view showing blood test apparatus  11  according to Embodiment 1 of the present invention. In  FIG. 3 , housing  12  is made of a resinic material and is provided with cylindrical body  12   b  of a cylindrical shape that has puncturing opening part  12   a . Laser emitting apparatus  13  is attached inside this cylindrical body  12   b . Further, vacuuming means  14  continuing to vacuuming passage  14   a , is attached to cylindrical body  12   b . Further, electrical circuit section  15  is provided next to cylindrical body  12   b . Electric battery  16  is replacably accommodated at one end of housing  12  at the other end of which puncturing opening part  12   a  is located. 
         [0045]    Sensor unit  17  is attached detachably to puncturing opening part  12   a . This sensor unit  17  is constituted by holder  17   a  and blood sensor  22  (hereinafter “sensor”), and sensor  22  is attached inside this holder  17   a  detachably. In virtually the center of sensor  22 , blood guiding part  34  that stores blood  8  is formed. 
         [0046]    Puncturing unit  18  is a unit that punctures skin by means of a needle (an example of a needle-puncturing apparatus is used here), and is attached detachably between puncturing opening part  12   a  and sensor unit  17  in blood test apparatus  11 . That is, upper part  18   a  of puncturing unit  18  is attached detachably to puncturing opening part  12   a , and sensor unit  17  is attached detachably to lower part  18   b  of puncturing unit  18 . That is, both sensor unit  17  and puncturing unit  18  can be attached to puncturing opening part  12   a . When a needle-puncturing unit is attached, use of laser emitting apparatus  13 , which is built in the blood test apparatus, is automatically prevented. That is, power supply to laser emitting apparatus  13  from electric battery  16  and control signals to laser emitting apparatus  13  are automatically stopped or blocked by electrical circuit section  15 . 
         [0047]    Consequently, it is possible to selectively perform puncturing by attaching sensor unit  17  directly to puncturing opening part  12   a  and using laser emitting apparatus  13 , and puncturing by attaching puncturing unit  18  to puncturing opening part  12   a  and sensor unit  17  to puncturing unit  18  and using a needle-puncturing apparatus. That is, in case where puncturing unit  18  is used, puncturing is performed by means of a puncturing needle, so that it is possible to perform puncturing without using electric battery  16 . Consequently, even when electric battery  16  is consumed and its remaining power is decreased, it is still possible to measure the blood sugar level. Accordingly, it is possible to adequately prevent the disease from worsening. 
         [0048]    Further, laser emitting apparatus  13  and puncturing unit  18  both make laser light and a puncturing needle pass near blood guiding part  34  to perform puncturing, so that it is possible to test blood  8  using same sensor  22 . Accordingly, for example, another sensor needs not to be prepared and, even when the puncturing means changes, the burden on the user decreases. Further, the vicinity of blood guiding part  34  generally refers to the range of 0.5 millimeters to 5 millimeters around blood guiding part  34 . 
         [0049]    Next, puncturing unit  18  will be explained in detail using  FIGS. 4 ,  5  and  6 .  FIG. 4  is a cross-sectional view showing puncturing unit  18  from the side, and  FIG. 5  is a cross-sectional view cutting puncturing unit  18  in the A-A plane and showing puncturing unit  18  from above. Further,  FIG. 6  is a perspective view of puncturing unit  18 . Puncturing unit  18  has a cylindrical shape and is sealed by upper surface  18   c  and lower surface  18   d . Further, these upper surface  18   c  and lower surface  18   d  communicate through two vacuuming passages  18   e . Consequently, even when middle part  18   f  between upper surface  18   c  and lower surface  18   d  is opened to air, it is possible to apply a negative pressure from upper surface  18   c  to lower surface  18   d.    
         [0050]    Guard  18   h  formed in stick  18   g  is led outside cylinder  18   j  to form handle  18   k.  Guide  18   m  is formed integrally with upper surface  18   c , and guides stick  18   g  so as to slide in the up and down direction. Further, guide  18   n  is formed to extend from cylinder  18   j,  and guides stick  18   g  so as to slide only in the up and down direction in conjunction with guide  18   m.    
         [0051]    Springs  18   p  are inserted between upper surface  18   c  and guard  18   h  to urge stick  18   g  downward. Latch claw  18   q  of handle  18   k  is formed integrally with puncturing button  18   r.  These latch claw  18   q  and puncturing button  18   r  are urged by springs  18   s  toward the outside of cylinder  18   j.    
         [0052]    Puncturing depth adjusting knob  18   t  provided in cylinder  18   j  moves guard  18   h  on screws  18   u  to define the location where guard  18  stops. By defining the location where guard  18   h  stops, the distance stick  18   g  falls is defined and the depth to which the puncturing needle punctures skin is adjusted. 
         [0053]    A plurality of conductors  18   w,  which communicate upper part  18   a  with lower part  18   b , lead signals from sensor  22  to electrical circuit section  15  through puncturing opening part  12   a . These conductors  18   w  are connected to connector electrodes in upper part  18   a  and lower part  18   b , and these connector electrodes are provided evenly in a circle. Further, these connector electrodes contact and connect with connectors  53  ( 53   a  to  53   g ) formed in puncturing opening part  12   a  in upper part  18   a , and contact and connect with connection electrodes  41   a  to  45   a  (see  FIG. 11 ) formed in sensor  22  in lower part  18   b.    
         [0054]    Further, in the inner surface of the ring formed in upper part  18   a  and in the outer surface of lower part  18   b , guide parts  20  (see  FIG. 9 ) are formed to define the rotation angle when the puncturing unit is inserted, and make the connector electrodes abut on upper part  18   a  and lower part  18   b  reliably. Needle unit  19  is inserted removably between stick  18   g  and lower surface  18   d . Consequently, it is possible to readily replace needle unit  19 . Inside this needle unit  19 , puncturing needle  19   a  is urged upward by springs  19   b . Detecting sensor  18   y  detects whether or not there is needle unit  19 . Signals outputted from this detecting sensor  18   y  are connected to the connector electrodes through conductors  18   w.    
         [0055]    Next, the operation of this puncturing unit  18  will be explained. First, handle  18   k  slides upward against springs  18   p.  Then, latch claw  18   q  latches with handle  18   k.  In this state, needle unit  19  is inserted. Then, puncturing button  18   r  is pressed. Then, latch claw  18   q  and handle  18   k  are disengaged, so that stick  18   g  hits puncturing needle  19   a  of puncturing unit  19 . Puncturing needle  19   a  passes blood guiding part  34  of sensor  22  and punctures skin  7 . Further, the puncturing depth is adjusted in advance by knob  18   t.    
         [0056]      FIG. 7A  is a cross-sectional view of sensor unit  17  of one example, and  FIG. 8  is a plan view showing  FIG. 7(A)  from the bottom surface. Sensor unit  17  is constituted by holder  17   a  and sensor  22  that is inserted in this holder  17   a . Inside holder  17   a , receiving board  17   c  having hole  17   b  in the center is provided and sensor  22  is mounted on this receiving board  17   c . Further, this sensor  22  is latched by latching convex parts  17   e  formed inside holder  17   a . Further, convex part  17   f  of a ring shape is formed below receiving board  17   c , forming vacuuming chamber  14   b.    
         [0057]    Convex part  17   f  is provided with skin detecting sensors  17   d  that detect contact with skin. Signals from these skin detecting sensors  17   d  are connected with concave parts  20   d  formed in guides  20   b  through conductor wires. Skin detecting sensors  17   d  detect the resistance when skin detecting sensors  17   d  abut on skin  7 , and are constituted by conductor electrodes. Then, as shown in  FIG. 8 , skin detecting sensors  17   d  are connected such that a plurality of concave parts  20   d  are divided into two. This is to extract signals irrespective of the insertion direction of sensor unit  17  by acquiring signals from convex parts  20   c  that are located 180 degrees apart and that fit in these concave parts  20   d . Further, this relationship is possible even when concave parts  20   d  formed in sensor unit  17  and convex parts  20   c  formed in puncturing opening part  12   a  are switched. 
         [0058]      FIG. 7(B)  and  FIG. 7(C)  are perspective plan views showing sensor unit  17  shown in  FIG. 7(A)  from above.  FIG. 7(B)  shows a case where the shape of sensor  22  is hexagonal and blood guiding part  34  is in virtually the center of sensor  22 .  FIG. 7(C)  shows a case where the shape of sensor  22  is a square and blood guiding part  34  is provided in virtually the center of sensor  22 . 
         [0059]      FIG. 9  is an exploded plan view of guiding parts  20 . These guiding parts  20  are formed between puncturing opening part  12   a  and sensor unit  17 , between puncturing opening part  12   a  and upper part  18   a  of puncturing unit  18  and between lower part  18   b  of puncturing unit  18  and sensor unit  17 , in order to make electrodes contact each other to lead signals from sensor unit  22  even when sensor unit  17  or puncturing unit  18  and sensor unit  17  both are attached to puncturing opening part  12   a  carelessly. 
         [0060]    As shown in  FIG. 9 , guides  20   a  of a concave shape are provided in the outer surface of cylindrical body  12   b  forming puncturing opening part  12   a  and in the outer surface of lower part  18   b  of puncturing unit  18 . Further, guides  20   b  of a convex shape are provided in the inner surface of sensor unit  17  and in the inner surface of upper part  18   a  of puncturing unit  18 . Consequently, even when sensor unit  17  or puncturing unit  18  is inserted carelessly, the direction of sensor unit  17  or puncturing unit  18  is corrected along these guides  20   a  and  20   b . Consequently, the electrodes are reliably connected with each other, so that it is possible to lead signals from sensor  22  to electrical circuit section  15 . 
         [0061]    Convex parts  20   c  are formed in the depth parts of guides  20   a , and are electrically conductive and elastic. Concave parts  20   d  are provided at the front ends of guides  20   b , and are electrically conductive. These convex parts  20   c  and concave parts  20   d  fit, thereby positioning sensor unit  17  and puncturing unit  18  and leading signals from skin detecting sensors  17   d  attached to sensor unit  17  through these convex parts  20   c  and concave parts  20   d , to electrical circuit section  15 . 
         [0062]      FIG. 10  is a cross-sectional view of sensor  22  attached to sensor unit  17 . This sensor  22  is constituted by substrate  31 , spacer  32  pasted on the upper surface of this substrate  31  and cover  33  pasted on the upper surface of spacer  32 , and has a plate shape. 
         [0063]    Substrate hole  31   a  formed in virtually the center of substrate  31 , spacer hole  32   a  formed in virtually the center of spacer  32  and cover hole  33   a  formed in virtually the center of cover  33  communicate to form blood guiding part  34  of blood  8 . This blood guiding part  34  is open downward to abut on skin  7  and sample blood  8 . One end of supply channel  35  for blood  8  continues to this blood guiding part  34  and supply channel  35  leads blood  8  stored in blood guiding part  34  by capillary action to detecting section  37  formed on supply channel  35  (see  FIG. 11 ). Further, the other end of this supply channel  35  continues to air hole  38 . 
         [0064]    Here, a water-repellant material is used for upper surface  33   h  of cover  33 . Further, a hydrophillic material is used inside supply channel  35 . Here, preferably, ceiling  34   a  of blood guiding part  34  is treated to be less hydrophilic than supply channel  35  or treated to be less water-repellant than upper surface  33   h  of cover  33 . 
         [0065]    Reagent  30  is arranged on detecting section  37 . This reagent  30  can be obtained by adding and dissolving PQQ-GDH (0.1 to 5.0 U/sensor), potassium ferricyanide (10 to 200 millimole), maltitol (1 to 50 millimole) and taurine (20 to 200 millimole) in a CMC solution of 0.01 to 2.0 wt % to prepare a reagent solution and by dropping the reagent solution and drying reagent  30  on the detecting section. 
         [0066]      FIG. 11  is a perspective plan view of sensor  22 . The shape of sensor  22  is a regular hexagon, and connection electrodes  41   a  to  45   a  that are connected with connectors  53   a  to  53   f  provided in puncturing opening part  12   a  of blood test apparatus  11 , and reference electrode  43   c  that is connected with connection electrode  43   a , are formed in the respective six apexes of this regular hexagon. 
         [0067]    In blood guiding part  34 , supply channel  35 , one end of which is connected with this blood guiding part  34 , is provided toward detection electrode  42 . Further, the other end of this supply channel  35  continues to air hole  38 . On this supply channel  35 , there are, from the side closer to blood guiding part  34 , detection electrode  44  connected with connection electrode  44   a , detection electrode  45  connected with connection electrode  45   a , detection electrode  44 , which is provided again, connected with connection electrode  44   a , detection electrode  43  connected with connection electrode  43   a  and reference electrode  43   c , detection electrode  41  connected with connection electrode  41   a,  detection electrode  43 , which is provided again, connected with connection electrode  43   a  and reference electrode  43   c  and detection electrode  42  connected with connection electrode  42   a . Further, reagent  30  (see  FIG. 10 ) is arranged on detection electrodes  41  and  43 . 
         [0068]      FIG. 12  is an exploded plan view of sensor  22 .  FIG. 12(C)  is a plan view of regular hexagonal substrate  31  constituting sensor  22 , and its dimension  31   b  is about 9 millimeters. The material of this substrate  31  is polyethylene terephthalate (PET) and the thickness of substrate  31  is about 0.100 millimeters. 
         [0069]    An electrically conductive layer is formed on the upper surface of this substrate  31  by the sputtering method or the vapor deposition method using material such as gold, platinum, or palladium, and detection electrodes  41  to  45  and connection electrodes  41   a  to  45   a  and reference electrode  43   c  derived from these detection electrodes  41  to  45  are integrally formed by applying laser machining to this electrically conductive layer. Substrate hole  31   a  is provided in virtually the center of substrate  31 . 
         [0070]      FIG. 12(B)  is a plan view of spacer  32  and its dimension  32   b  is about 9 millimeters. Spacer hole  32   a  is provided in virtually the center of spacer  32  in a position to meet substrate hole  31   a.  This spacer  32  is formed by machining a regular hexagon, and six semicircular notches  32   f  are formed in the six apexes of this regular hexagon to meet connection electrodes  41   a  to  45   a  and reference electrode  43   c  of substrate  31 . 
         [0071]    Further, slit  32   c  is formed to continue to this spacer hole  32   a  and this slit  32   c  forms supply channel  35  for blood  8 . The wall surfaces of this slit  32   c  and the upper surface of substrate  31  to meet the wall surfaces of slit  32   c  are subjected to hydrophilic treatment. The width of this slit  32   c  is made about 0.600 millimeters and the length of slit  32   c  is made about 2.400 millimeters to form supply channel  35  with a cavity of about 0.144 microliters. In this way, it is possible to perform test with a small amount of blood  8 , so that patients do not have to get strained and scared. The material of spacer  32  is polyethylene terephthalate and the thickness of spacer  32  is about 0.050 millimeters. 
         [0072]      FIG. 12(A)  is a plan view of cover  33 . Its dimension  33   b  is about 9 millimeters. Cover hole  33   a  is provided in a position slightly decentered from the center of cover  33 . Air hole  38  is provided to meet the front end part of supply channel  35 . Diameter  38   a  of this air hole  38  is about 50 micrometers. The reason for reducing the diameter of air hole  38  in this way is to prevent blood  8  from flowing out from air hole  38 . Cover  33  is formed by machining a regular hexagon, and six semicircular notches  33   f  are formed in the six apexes of this regular hexagon, which is not machined yet, to meet connection electrodes  41   a  to  45   a  and reference electrode  43   c  of substrate  31 . The material of this cover  33  is polyethylene terephthalate and the thickness of cover  33  is about 0.075 millimeters. 
         [0073]    Substrate  31 , spacer  32  and cover  33  constituting sensor  22  can each be formed by dividing a parent substrate of a fixed measure into several pieces. These substrate  31 , spacer  32  and cover  33  that are divided are regular hexagons and, consequently, can be aligned in the parent substrates without space. Accordingly, these materials are each efficiently scribed in the parent substrate, which cuts waste, is economical and contributes to resource saving. 
         [0074]      FIG. 13  is a cross-sectional view in the vicinity of blood guiding part  34  of sensor  22  and  FIG. 14  is a plan view of blood guiding part  34 . In  FIG. 13  and  FIG. 14 , diameter  31   g  of substrate hole  31   a  formed in substrate  31  and diameter  32   g  of spacer hole  32   a  formed in spacer  32  are about 1.750 millimeters, and diameter  33   g  of cover hole  33   a  formed in cover  33  is 1.500 millimeters. The centers of substrate hole  31   a  and spacer hole  32   a  are on the same line, and the center of cover hole  33   a  is in a direction slightly apart from the supply channel  35  side. Further, opposite side  34   e  of supply channel  35  in substrate hole  31   a,  spacer hole  32   a  and cover hole  33   a  are on the same plane. 
         [0075]    According to this configuration, projecting part  33   c  projecting from supply channel  35  toward the center of blood guiding part  34  is formed in blood guiding part  34 . The dimensions of projection of this projecting part  33   c  is 0.250 millimeters and is 0.100 millimeters greater than the sum, 0.150 millimeters, of the thicknesses of substrate  31  and spacer  32 . 
         [0076]    Further, opposite side  34   e  of supply channel  35  in blood guiding part  34  is formed on the same plane. That is, there are the centers of substrate hole  31   a  and spacer hole  32   a  in the center of blood guiding part  34  and the center of cover hole  33   a  on the opposite side of supply channel  35 . The relationship between diameters  31   g,    32   g  and  33   g  of these holes are that diameter  31   g  of substrate hole  31   a  and diameter  32   g  of spacer hole  32   a  are equal and diameter  33   g  of cover hole  33   a  is smaller than diameter  32   g  of spacer hole  32   a.    
         [0077]    The operation of sensor  22  constituted as described above will be explained below. As shown in  FIG. 15 , when skin  7  inside blood guiding part  34  is punctured, blood  8  flows out from punctured hole  7   a  by this puncturing to form blood drop  8   a . As shown in  FIG. 16 , this blood drop  8   a  increasingly grows, and abuts on the tip of projecting part  33   c  (shown by the dotted line). Further, before blood drop  8   a  grows to reach contact point  31   j  with skin  7  on the supply channel  35  side, as shown in  FIG. 17 , blood drop  8   a  flows into detecting section  37  through supply channel  35 , at a burst, in a rate-controlled state, thanks to the capillary action produced by projecting part  33   c  and skin  7 . 
         [0078]    In this way, the capillary action produced in the space between cover  33  and skin  7  becomes strong on the supply channel side, so that it is possible to allow blood  8  to flow into detecting section  37  through supply channel  35  in a reliable manner, before blood  8  fills blood guiding part  34 . Consequently, it is possible to reduce the amount of blood left in blood guiding part  34 . That is, the amount of blood  8  to sample decreases accordingly, so that it is possible to alleviate the burden upon patients. 
         [0079]      FIG. 18(A)  and  FIG. 18(B)  are a cross-sectional view of sensor unit  17  mounting another example of sensor  22 - 2  and a perspective plan view showing sensor unit  17  from above. 
         [0080]    Sensor  22 - 2  has a square shape, and blood guiding part  34  is provided in the longitudinal direction of the side surface of the square. 
         [0081]    In this way, as shown in  FIG. 7(A)  to  FIG. 7(C) , blood guiding part  34  is not necessarily provided in the center part of the sensor and the essential requirement is that blood guiding part  34  is provided in the vicinity of the position to puncture. Further, sensor  22 - 2  of a square shape shown in  FIG. 18(B)  may be flexibly arranged at any angle around blood guiding part  34  (i.e. the position to puncture). 
         [0082]      FIG. 19(A)  and  FIG. 19(B)  are a cross-sectional view of sensor unit  17  mounting another example of sensor  22 - 3  and a perspective plan view showing sensor unit  17  from above. Sensor  22 - 3  has a square shape, and is the same as in the case of the sensor unit mounting sensor  22 - 2  described in  FIG. 18(A)  and  FIG. 18(B)  except for blood guiding part  34  that is provided in the lateral direction of the side surface of the square. 
         [0083]      FIG. 20(A)  and  FIG. 20(B)  are a cross-sectional view of sensor unit  17  mounting another example of sensor  22 - 4  and a perspective plan view showing sensor unit  17  from above. 
         [0084]    Although sensor  22 - 4  has a square shape similar to sensor  22 - 3  and the location of blood guiding part  34  is the same as in sensor  22 - 3 , the dimensions of sensor  22 - 4  greater than sensor  22 - 3  are secured such that sensor  22 - 4  protrudes from the side surface of sensor unit  17 . Compared to the case of sensor  22 - 3 , the operability of attaching sensor  22 - 4  is good even while the puncturing unit is kept attached. It naturally follows that, in this case, space is provided in the side surface of holder  17   a  to let in and let out sensor  22 - 4 . 
         [0085]    Next,  FIG. 21  is a cross-sectional view when the puncturing unit (an example of a needle-puncturing apparatus) mounting sensor unit  17  shown in  FIG. 7 ,  FIG. 18  and  FIG. 19 , is attached to blood test apparatus  11 . 
         [0086]    In  FIG. 21 , housing  12  is made of a resinic material and is provided with cylindrical body  12   b  of a cylindrical shape that has puncturing opening part  12   a . Laser emitting apparatus  13  is attached inside this cylindrical body  12   b . Further, vacuuming means  14  continuing to vacuuming passage  14   a  is attached to cylindrical body  12   b . Further, electrical circuit section  15  is provided next to cylindrical body  12   b . Electric battery  16  is accommodated replacably at one end of housing  12  at the other end of which puncturing opening part  12   a  is located. 
         [0087]    Sensor unit  17  is attached detachably to puncturing opening part  12   a . In virtually the center of sensor unit  17 , blood guiding part  34  that punctures and guides blood  8  (not shown) is formed. 
         [0088]    Further, sensor unit  17  can mount any type of hexagonal or square sensor  22  meeting the blood guiding part in virtually the center of the sensor, square sensor  22 - 2  meeting the blood guiding part in the longitudinal side of the square sensor and square sensor  22 - 3  meeting the blood guiding part in the lateral side of the square sensor. 
         [0089]    Puncturing unit  18  performs puncturing by means of a puncturing needle and is attached detachably between puncturing opening part  12   a  and sensor unit  17 . That is, upper part  18   a  of puncturing unit  18  is attached detachably to puncturing opening part  12   a  of blood test apparatus  11  and sensor unit  17  is attached detachably to lower part  18   b  of puncturing unit  18 . 
         [0090]    Consequently, it is possible to selectively perform puncturing by attaching sensor unit  17  directly to puncturing opening part  12   a  and using laser emitting apparatus  13 , and puncturing by attaching puncturing unit  18  to puncturing opening part  12   a  and sensor unit  17  to puncturing unit  18  and using a needle-puncturing apparatus. 
         [0091]    That is, in case where puncturing unit  18  is used, puncturing is performed by means of a puncturing needle, so that it is possible to perform puncturing without using electric battery  16 . Consequently, even when electric battery  16  is consumed and its remaining power is decreased, it is possible to measure the blood sugar level. Accordingly, it is possible to adequately prevent the disease from worsening. 
         [0092]    Further, laser emitting apparatus  13  and puncturing unit  18  both perform puncturing by means of laser light and a puncturing needle that pass near blood guiding part  34 , so that it is possible to test blood  8  using same sensor  22 . Accordingly, for example, another sensor needs not to be prepared and, even when a puncturing means changes, the burden on the user decreases. Further, the puncturing unit and the sensor unit have vacuuming passages and can apply negative pressures to the vicinity of the blood guiding part prior to puncturing. 
         [0093]      FIG. 22  is a cross-sectional view in the case where the puncturing unit mounting sensor unit  17  shown in  FIG. 20  is attached in blood test apparatus  11 . 
         [0094]      FIG. 22  and  FIG. 21  are the same except for sensor unit  17 . Sensor unit  17  shown in  FIG. 22  has sensor  22 - 4  meeting blood guiding part  34  in the lateral direction of the side surface of the square of sensor  22 - 4 , and has space for sensor  22 - 4  because sensor  22 - 4  has a shape protruding from holder  17   a.    
         [0095]    Further, puncturing is performed in the vicinity of blood guiding part  34  using laser emitting apparatus  13  and puncturing unit  18  built in blood test apparatus  11 . That is, the same position can be punctured using one of both methods, so that the operability is maintained and the reliability is also secured. 
         [0096]      FIG. 23  is a cross-sectional view of laser emitting apparatus  13 . Laser emitting apparatus  13  is constituted by oscillating tube  13   a  and cylindrical body  13   b  of a cylindrical shape coupled to the front of this oscillating tube  13   a . Oscillating tube  13   a  accommodates Er:YAG (yttrium aluminum garnet) laser crystal  13   c  and flash light source  13   d . Partial transmission mirror  13   e  of about one percent transmittance is attached to one end of oscillating tube  13   a , and total reflection mirror  13   f  is attached to the other end. Convex lens  13   g  is attached inside cylindrical body  13   b  ahead of partial transmittance mirror  13   e  and is set to adjust the focus of laser light  13   h  under the skin of the patient. 
         [0097]    The operation of laser emitting apparatus  13  constituted as described above will be explained below. Puncturing button  13   j  (see  FIG. 24 ) is pressed. Then, flash light source  13   d  is excited, and the light source emitted from this flash light source  13   d  enters Er:YAG laser crystal  13   c  and is reflected between total reflection mirror  13   f , YAG laser crystal  13   c  and partial transmission mirror  13   e  to oscillate and amplify. Part of this amplified laser light passes partial transmission mirror  16   e  by stimulated emission. Laser light  13   h  that has passed this partial transmission mirror  13   e  passes lens  13   g  to pass sensor  22  and adjust its focus inside skin  7 . Preferably, the depth of the focus to which laser light punctures skin is between 0.1 millimeters and 1.5 millimeters from skin  7 , and is 0.5 millimeters with the present embodiment. 
         [0098]    Blood  8  flows out from punctured skin  7 . Blood  8  that has flowed out is taken inside sensor  22  and chemically reacts with reagent  30  in this sensor  22 . Information about blood  8  that has chemically reacted with reagent  30  is transmitted to electrical circuit section  15  through connectors  53   a  to  53   g  and the blood sugar level and the like is calculated in electrical circuit section  15 . Further, details of this will be explained later. 
         [0099]    With the present embodiment, laser emitting apparatus  13  that enables puncturing without contacting skin  7  of the patient is used as the main puncturing means, so that, in the normal state of use, a puncturing needle needs not to be changed and preparation prior to puncturing becomes simple compared to puncturing apparatuses using a puncturing needle. Further, skin  7  and laser emitting apparatus  13  do not contact, which is sanitary. Furthermore, there are no movable components, and technical malfunction decreases. Moreover, the structure of blood test apparatus  11  can be made water-proof, so that the apparatus can be washed entirely. Further, the puncturing voltage for this laser light  13   h  is about 300 volts. Accordingly, patients suffer from little pain. 
         [0100]      FIG. 24  is a block diagram of electrical circuit section  15 . In  FIG. 24 , connection electrodes  41   a  to  45   a  and reference electrode  43   c  of sensor  22  are connected with switching circuit  60  through connectors  53   a  to  53   g . The output of this switching circuit  60  is connected with the input of current/voltage converter  61 . The output of current/voltage converter  61  is connected with the input of calculating section  63  through analogue/digital converter  62  (hereinafter “A/D converter”). The output of this calculating section  63  is connected with display section  64  formed with liquid crystal and transmitting section  67 . Further, reference voltage source  65  is connected with switching circuit  60 . This reference voltage source  65  may be a ground potential. 
         [0101]    Controlling section  66  controls the entire operation of the blood test apparatus according to the present invention. The output of this controlling section  66  is connected with laser emitting apparatus  13 , the controlling terminal of switching circuit  60 , calculating section  63 , transmitting section  67  and vacuuming means  14 . Further, the input of controlling section  66  is connected with puncturing button  13   j  for performing puncturing by laser emitting apparatus  13 , switch  13   k  that switches between laser puncturing and needle-puncturing, voltage detecting section  16   a  that detects the voltage of electric battery  16 , skin detecting sensors  17   d , timer  68  and detecting sensor  18   y  that detects attachment of needle unit  19 . It may also be possible to connect and use a vacuum button that is manually pressed, instead of using skin detecting sensors  17   j.    
         [0102]    Next, the operation of electrical circuit section  15  will be explained. First, to which connectors  53   a  to  53   f  connection electrodes  41   a  to  45   a  and reference electrode  43   c  of sensor  22  and detecting sensor  18   y  are connected is detected. That is, according to a command from controlling section  66 , a connector having zero electrical resistance with respect to the adjacent connectors is found among connectors  53   a  to  53   f . Then, when the connector having zero electrical resistance is found, the connector is determined as connector  53  to be connected with reference electrode  43   c . It is determined based on connector  53  connected with this reference electrode  43   c  that connectors  53  (i.e. starting with any of connectors  53   a  to  53   f ) are connected with connection electrodes  44   a ,  45   a ,  41   a,    42   a  and  43   a , respectively. In this way, connectors  53   a  to  53   g  respectively connected with connection electrodes  41   a  to  45   a , reference electrode  43   c  and detecting sensor  18   y  are determined and then blood  8  is measured. Further, signals from detecting sensor  18   y  are connected to controlling section  66  through switching circuit  60 . 
         [0103]    In the measurement operation, switching circuit  60  is switched first to connect detection electrode  41  (see  FIG. 11 ), which serves as an active electrode for measuring the amount of blood components, with current/voltage converter  61 . Further, detection electrode  42 , which serves as a sensing electrode for sensing the inflow of blood  8 , is connected with reference voltage source  65 . Then, a certain voltage is applied between detection electrode  41  and detection electrode  42 . In this state, when blood  8  flows in, a current flows between detection electrode  41  and detection electrode  42 . This current is converted into a voltage by current/voltage converter  61  and this voltage value is converted into a digital value in A/D converter  62 . The digital value is outputted to calculating section  63 . Calculating section  63  detects based on the digital value that sufficient blood  8  has flowed in. At this point, the operation of vacuuming means  14  is turned off. 
         [0104]    Next, glucose, which is a blood component, is measured. To measure the amount of glucose components, according to a command from controlling section  66 , switching circuit  60  is switched, and detection electrode  41 , which serves as an active electrode for measuring the amount of blood components, is connected with current/voltage converter  61 . Further, detection electrode  43 , which serves as a counter electrode for measuring the amount of glucose components, is connected with reference voltage source  65 . 
         [0105]    While, for example, the glucose in blood and its oxidation-reduction enzyme are reacted for a certain period, current/voltage converter  61  and reference voltage source  65  are stopped. Further, after a certain reaction period (one to ten seconds) passes, a voltage (0.2 to 0.5 volts) is applied between detection electrodes  41  and  43  according to a command from controlling section  66 . Then, a current flows between detection electrodes  41  and  43 . This current is converted into the voltage in current/voltage converter  61 , and the voltage value is converted into a digital value in A/D converter  62  and is outputted to calculating section  63 . Calculating section  63  converts this digital value into an amount of glucose components. 
         [0106]    Next, after the amount of glucose components is measured, the Hct (hematocrit) value is measured. The Hct value is measured as follows. First, switch circuit  60  is switched according to a command from controlling section  66 . Then, detection electrode  45 , which serves as an active electrode for measuring the Hct value, is connected with current/voltage converter  61 . Further, detection electrode  41 , which serves as the counter electrode for measuring the Hct value, is connected with reference voltage source  65 . 
         [0107]    Next, according to a command from controlling section  66 , a certain voltage (2 to 3 volts) is applied between detection electrodes  45  and  41  from current/voltage converter  61  and reference voltage source  65 . The current that is applied between detection electrodes  45  and  41  is converted into a voltage in current/voltage converter  61  and the voltage value is converted into a digital value in A/D converter  62 . The digital value is outputted to calculating section  63 . Calculating section  63  converts the digital value into an Hct value. 
         [0108]    Using the Hct value and amount of glucose components acquired in this measurement, the amount of glucose components is corrected by the Hct value with reference to a calibration curve or calibration curve table determined in advance, and the correction result is displayed in display section  64 . Further, the correction result may be transmitted from transmitting section  67  to the injection apparatus that injects insulin. Although a radio wave may be used for this transmission, transmission is preferably performed by optical communication that does not interfere with medical equipment. 
         [0109]    By transmitting measurement data corrected in this way from transmitting section  67  to automatically set the dose of insulin to administer in the injection apparatus, the patient needs not to set the dose of insulin to administer, so that annoyance of setting the dose of insulin to administer is eliminated. Further, the dose of insulin can be set in the injection apparatus without artificial means, so that it is possible to prevent setting errors. 
         [0110]    Although measurement of glucose is explained as an example, by replacing sensor  22 , the present invention is also effective to measure other blood components such as the lactate acid level, and cholesterol, in addition to glucose. 
         [0111]    Next, the operation of blood test apparatus  11  will be explained using  FIG. 25 . When the power switch (not shown) is turned on, power is supplied to electrical circuit section  15 . When power is supplied, the flow proceeds to step  71  and blood test apparatus  11  can detect the voltage of electric battery  16  in voltage detecting section  16   a . This voltage detecting section  16   a  transmits the detection level and the result of detecting whether or not the voltage is a predetermined voltage level that allows laser puncturing. 
         [0112]    When controlling section  66  decides that laser puncturing is possible, the flow proceeds to step  72 . At this time, according to the detection level of voltage detecting section  16   a , it is also possible to provide a plurality of selection modes in advance and automatically or manually switch between the laser emitting apparatus and the needle-puncturing apparatus according to the selected mode. 
         [0113]    For example, as detection levels in the voltage detecting section, there are three selection modes based on a plurality of setting values of the remaining power of the electric battery and voltage determined in advance. Controlling section  66  selects between the following three modes based on the detection level in voltage detecting section  16   a  and the setting value of the selection mode set in advance. In the first selection mode, the detection level is equal to or more than the first setting value and the laser emitting apparatus is automatically selected. In the second selection mode, the detection level is equal to or more than a second setting value and less than the first setting value, and either the laser emitting apparatus or the needle-puncturing apparatus can be selected by the user. In the third selection mode, the detection level is less than the second setting value and the needle-puncturing apparatus is automatically selected. Further, the second selection mode (i.e. mode where the user can select either the laser emitting apparatus or the needle-puncturing apparatus) can be switched automatically or manually in advance. In case where either the laser emitting apparatus or the needle-puncturing apparatus is selected automatically, by making a setup in advance as to whether to select laser emitting apparatus  13  or needle-puncturing apparatus  14 , the puncturing means is automatically switched without waiting for user to select when the mode switches to the second selection mode. At this time, when needle-puncturing apparatus  14  is selected as the puncturing means, use of laser emitting apparatus  13  built in the blood test apparatus is automatically prevented. That is, power supply to laser emitting apparatus  13  from electric battery  16  and control signals to laser emitting apparatus  13  are stopped or blocked by controlling section  66 . 
         [0114]    Then, in step  72 , whether switch  13   k  is set to laser puncturing or needle-puncturing is detected. Further, as described above, in case where a setup is made such that puncturing means is selected automatically, the setup state is decided. 
         [0115]    When the puncturing means is set to laser puncturing, the flow proceeds to step  73 , and the blood test apparatus waits until sensor unit  17  is attached and shows a display that suggests attaching sensor unit  17 . Further, attachment of this sensor unit  17  is detected when reference electrode  43   c  is detected. When sensor unit  17  is not attached, display section  64  shows a display that suggests attaching sensor unit  17 . If puncturing unit  18  is attached and sensor unit  17  is not attached, sensor unit  17  is not electrically connected with reference electrode  43   c , that is, sensor unit  17  is not electrically conducted with reference electrode  43   c , so that electrical circuit section  15  built in the blood test apparatus can decide that sensor unit  17  is not attached. It naturally follows that the same applies when neither puncturing unit  18  nor sensor unit  17  is attached. 
         [0116]    In a case where the voltage does not allow laser puncturing in step  71  and in a case where, even though the voltage allows laser puncturing, switch  13   k  is set to the needle-puncturing side in step  72 , the flow proceeds to step  74  and display section  64  shows a display that suggests attaching puncturing unit  18 , and then the flow proceeds to step  75 . Further, whether or not puncturing unit  18  is attached is decided based on the output from detecting sensor  18   y  provided in puncturing unit  18 . In this step  75 , the blood test apparatus waits until puncturing unit  18  is attached. Here, when puncturing unit  18  is not attached after a predetermined time passes (this time is measured by timer  68 ), a warning means can make a warning. 
         [0117]    When puncturing unit  18  is attached, the flow proceeds to step  76 . Further, the display in step  74  that suggests attaching puncturing unit  18  is turned off, and the flow proceeds to step  73 . 
         [0118]    When attachment of sensor unit  17  is detected in step  73 , the flow proceeds to step  77 . In step  77 , detection electrodes  41  to  45  are specified based on detected reference electrode  43   c  of sensor  22 . Further, at the time reference electrode  43   c  is detected, the display in step  73  that suggests attaching sensor unit  17  is turned off. 
         [0119]    Then, the blood test apparatus waits in step  78  until the blood test apparatus abuts on skin  7  to sample blood from. When skin detecting sensors  17   d  in sensor unit  17  detect skin  7 , the flow proceeds to step  79  and vacuuming means  14  is operated. Then, this vacuuming means  14  applies a negative pressure to vacuuming chamber  14   b  (the vicinity of sensor  22 ). A vacuum button (not shown) may be connected with controlling section  66  and be pressed instead of using skin detecting sensors  23   j.    
         [0120]    When the current in the vacuum pump forming vacuuming means  14  changes or the time determined in advance in timer  68  passes, it is decided that skin  7  inside blood guiding part  34  is sufficiently lifted up, and the flow proceeds to step  80 . In step  80 , display section  64  displays that puncturing is possible. In step  81 , when switch  13   k  selects the laser puncturing side, pressing of puncturing button  13   j  of laser emitting apparatus  13  is commanded in this display. Then, the flow proceeds to step  82  and laser emitting apparatus  13  waits until puncturing button  13   j  is pressed. When puncturing button  13   j  is pressed, the flow proceeds to step  83 . 
         [0121]    Further, when switch  13   k  selects the needle-puncturing side in step  81 , pressing of puncturing button  18   r  of puncturing unit  18  is commanded in this display. Then, the flow proceeds to step  84  and puncturing unit  18  waits until puncturing button  18   r  is pressed. When puncturing button  18   r  is pressed, the flow proceeds to step  83 . 
         [0122]    In step  83 , by pressing puncturing button  13   j  or puncturing button  18 r, laser light  13   h  or puncturing needle  19   a  punctures skin  7 . Blood  8  flows out as a result of puncturing skin  7 . This blood  8  is taken in detecting section  37  of sensor  22 . Then, in step  85 , the blood sugar level of blood  8  is measured. 
         [0123]    After the blood sugar level is measured in step  85 , the flow proceeds to step  86  and the negative pressure from vacuuming means  14  is turned off. Then, the flow proceeds to step  87  and the blood sugar level that is measured is displayed in display section  64   
         [0124]    Further, the display in step  80  to the effect that puncturing is possible, is turned off in step  83 . That is, the display is turned off at the timing blood  8  reaches detection electrode  42  before the blood sugar level is measured in step  85 . Further, the vacuuming may be turned off simultaneously at the timing blood  8  reaches detection electrode  42 . 
       Embodiment 2 
       [0125]      FIG. 26  is a cross-sectional view of blood test apparatus  11   a  according to Embodiment 2. While puncturing unit  18  is attached between puncturing opening part  12   a  and sensor unit  17  with Embodiment 1, puncturing needle part  103  corresponding to puncturing unit  18  is inserted from the oblique direction of housing  102  with Embodiment 2. Accordingly, Embodiment 2 will be explained mainly with this difference. Further, the same components as in Embodiment 1 will be assigned the same reference numerals and explanation thereof will be simplified. 
         [0126]    In  FIG. 26 , housing  102  is made of a resin (corresponding to housing  12  of Embodiment 1), and one end of this housing  102  forms cylindrical body  102   b  of a cylindrical shape that has puncturing opening part  102   a . Laser emitting apparatus  13  is attached inside this cylindrical body  102   b . Further, vacuuming means  14   a  continuing to vacuuming passage  14   a  is attached to cylindrical body  102   b . Further, electrical circuit section  15   a  (corresponding to electrical circuit section  15  of Embodiment 1) is provided next to cylindrical body  102   b . Electric battery  16  is accommodated detachably at the end opposite to the end where puncturing opening part  102   a  is provided. Sensor unit  17  is attached detachably to puncturing opening part  102   a.    
         [0127]    Puncturing needle insertion part  104  is attached obliquely in the side surface of housing  102  and this puncturing needle insertion part  104  and puncturing needle part  103  constitute needle-puncturing apparatus  105 . Puncturing needle part  103  is inserted in puncturing needle insertion part  104 . Puncturing needle part  103  is inserted not to allow the negative pressure to escape from puncturing needle insertion part  104 . A sealing member may be pasted for the same purpose. 
         [0128]    Needle  103   a  attached to the front end of puncturing needle part  103  is provided to incline obliquely with respect to the optical axis of laser light  13   h , and passes the center of blood guiding part  34  provided in the center of sensor  22  and punctures skin  7 . That is, needle  103   a  punctures virtually the same position of skin  7  as the position punctured by laser light  13   h.    
         [0129]    By hitting puncturing needle part  103  in the direction of arrow  104   a , needle  103   a  passes blood guiding part  34  and punctures skin  7 . A little amount of blood  8  flows out from skin  7 , this blood  8  is taken in sensor  22  and the property of this blood  8  is measured.  104   b  are springs that urge puncturing needle part  103  in the direction opposite to arrow  104   a  and functions to pull out puncturing needle  103   a  from skin  7 . 
         [0130]    In the surface (i.e. jointing surface) where cylindrical body  102   b  and puncturing needle insertion part  104  are attached, male screws and female screws are formed and, by rotating puncturing needle insertion part  103  in the direction of arrow  104   d,  it is possible to adjust the degree puncturing needle insertion part  104  intrudes into cylindrical body  102   b . That is, by rotating puncturing needle insertion part  104  in the direction of arrow  104   d  or in the direction opposite to arrow  104   d,  it is possible to adjust the depth the needle punctures skin  7 . Puncturing depth scales  104   e  are marked on the outer surface of puncturing needle insertion part  104 . 
         [0131]    Puncturing needle detecting sensor  104   f  is provided in puncturing needle insertion part  104  (corresponding to detecting sensor  18   y  of Embodiment 1), and the output of this puncturing needle detecting sensor  104   f  that detects insertion of puncturing needle part  103  in puncturing needle insertion part  104 , is connected to electrical circuit section  15   a  (corresponding to electrical circuit section  15  of Embodiment 1). 
         [0132]    Cap  104   g  is coupled to housing  102  with a chain and is provided attachably to rear end  104   h  of puncturing needle insertion part  104 . In case where puncturing needle part  103  is not used, this cap  104   g  seals rear end  104   h  so as not to allow the negative pressure to escape. 
         [0133]    As described above, a simple needle-puncturing apparatus is provided with the present embodiment, so that it is possible to make the puncturing unit small compared to puncturing unit  18  of Embodiment 1. Puncturing is possible by hitting rear end  103   b  of puncturing needle part  103  by the hand. 
       Embodiment 3 
       [0134]      FIG. 27  is a cross-sectional view of blood test apparatus  11   b  according to Embodiment 3. While rear end  103   b  of puncturing needle part  103  constituting needle-puncturing apparatus  105  is hit by the hand with Embodiment 2, hammer unit  106  is attached to rear end  103   b  of puncturing needle part  103  to hit needle-puncturing apparatus  105  with Embodiment 3. Accordingly, Embodiment 3 will be explained mainly with this difference. Further, the same components as in Embodiment 2 will be assigned the same reference numerals and explanation thereof will be simplified. 
         [0135]    In  FIG. 27 ,  106   a  is a cylindrical body made of a resin and handle  106   b  is attached and slides back and forth inside this cylindrical body  106   a . One end of this handle  106   b  is urged by springs  106   c  in the direction of arrow  106   d . Further, the other end of handle  106   b  is held engagably by engaging part  106   e.    
         [0136]    By disengaging engaging part  106   e , handle  106   b  is driven by springs  106   c  and is launched promptly in the direction of arrow  106   d . Then, handle  106   b  hits rear end  103   b  of puncturing needle part  103 . Then, needle  103   a  passes blood guiding part  34  of sensor  22  and punctures skin  7 . 
         [0137]    This cylindrical body  106   a  is attached to puncturing needle insertion part  104  to be rotatable about support point  106   f . Consequently, when hammer unit  106  is not used, this hammer unit  106  can be accommodated in hollow part  102   c  (that is, the state shown by the dotted line) provided in the side surface of housing  102  as shown by the dotted line. Needle-puncturing apparatus  105  and hammer unit  106  constitute needle-puncturing apparatus  107 . Further, when the laser puncturing apparatus switches to needle-puncturing apparatus  105  (including hammer unit  106 ), use of the laser puncturing apparatus is prevented and hammer unit  106  automatically rotates about support point  106   f  from hollow part  102   c  of the blood test apparatus and protrudes from the blood test apparatus. Then, hammer unit  106  is located in a position to drive needle-puncturing apparatus  105  (i.e. the state of  FIG. 27 ). 
         [0138]    As described above, the present embodiment differs from Embodiment 2 in having hammer unit  106 , so that puncturing is possible by hitting puncturing needle part  103  under a certain condition. Further, when hammer unit  106  is not used, hammer unit  106  can be accommodated in hollow part  102   c , which is convenient and not annoying when carrying the blood test apparatus. 
       Embodiment 4 
       [0139]      FIG. 28  is a cross-sectional view of blood test apparatus  11   c  according to Embodiment 4. While puncturing unit  18  is attached between puncturing opening part  12   a  and sensor unit  17  with Embodiment 1, puncturing unit  111 , which is a needle-puncturing apparatus that performs puncturing by means of a puncturing needle, can be attached replacably in the location where laser emitting apparatus  113  (corresponding to laser emitting apparatus  13  of Embodiment 1) is attached with Embodiment 4. Accordingly, Embodiment 4 will be explained mainly with this difference. Further, the same components as in Embodiment 1 will be assigned the same reference numerals and explanation thereof will be simplified. 
         [0140]    In  FIG. 28 , housing  112  is made of a resinic material (corresponding to housing  12  of Embodiment 1) and cylindrical body  112   b  of a cylindrical shape that has puncturing opening part  112   a  is provided with housing  112 . Laser emitting apparatus  113  and any of puncturing unit  111  are attached replacably inside this cylindrical body  112   b . Further, vacuuming means  14  continuing to vacuuming passage  14   a  is attached to cylindrical body  112   b . Further, electrical circuit section  15   b  (corresponding to electrical circuit section  15  of Embodiment 1) is provided next to cylindrical body  112   b . Electric battery  16  is accommodated replacably at the end opposite to the end where puncturing opening part  12   a  is provided. Sensor unit  17  is attached detachably to puncturing opening part  112   a.    
         [0141]    Puncturing unit  111  is constituted by hammer unit  111   a  and needle unit  111   b  attached detachably to this hammer unit  111   a.  Ferromagnetic member  111   c  identifies puncturing unit  111 . 
         [0142]    Ferromagnetic member  113   a  identifies laser emitting apparatus  113 . Detecting sensor  112   c  that detects ferromagnetic member  113   a  adhered to laser emitting apparatus  113  and detecting sensor  112   d  that detects ferromagnetic body  111   c  adhered to puncturing unit  111  are attached inside cylindrical body  112   b , and their outputs are connected to controlling section  66  inside electrical circuit section  15   b . Consequently, electrical circuit section  15   b  can automatically identify whether either laser emitting apparatus  113  or puncturing unit  111  is inserted inside cylindrical body  112   b.    
         [0143]    In any case, laser light or a puncturing needle passes sensor unit  17  attached to puncturing opening part  112   a  and punctures skin  7 , and, consequently same sensor  22  can be used. Further, puncturing is performed using a puncturing means that is built inside cylindrical body  112   b , so that the blood test apparatus that is used becomes small compared to blood test apparatus  11  used in Embodiment 1. 
         [0144]    Further, a vacuuming passage having the same function as vacuuming passage  18   e  explained in puncturing unit  18  of Embodiment 1 is formed in puncturing unit  111  and continues to the vacuuming means built in housing  112  of blood test apparatus  11   c,  so that it is possible to supply a negative pressure to vacuuming chamber  14   b  formed in sensor unit  17  without leaking the negative pressure. Further, a detecting sensor having the same function as detecting sensor  18   y  explained referring to puncturing unit  18  of Embodiment 1, is provided inside hammer unit  111   a.  Further, it is possible to carry puncturing unit  111  with blood test apparatus  11   c  by attaching puncturing unit  111  to the outer part of blood test apparatus  11   c.    
       Embodiment 5 
       [0145]      FIG. 29  is a cross-sectional view of blood test apparatus  11   d  according to Embodiment 5. While puncturing unit  18  is attached between puncturing opening part  12   a  and sensor unit  17  with Embodiment 1, both laser emitting apparatus  121  (corresponding to laser emitting apparatus  13  of Embodiment 1) and puncturing unit  122  (i.e. needle-puncturing apparatus) that performs puncturing by means of a puncturing needle, are attached inside same housing  123  with Embodiment 5. Accordingly, Embodiment 5 will be explained mainly with this difference. Further, the same components as in Embodiment 1 will be assigned the same reference numerals and explanation thereof will be simplified. 
         [0146]    In  FIG. 29 , housing  123  is made of a resin (corresponding to housing  12  of Embodiment 1) and two cylindrical bodies  123   a  and  123   b  are provided side by side inside housing  123 . Laser emitting apparatus  121  is built inside cylindrical body  123   a  and puncturing unit  122  is built inside cylindrical body  123   b . Puncturing unit  122  is constituted by hammer unit  122   a  and needle unit  122   b  that is attached detachably to this hammer unit  122   a.    
         [0147]    Puncturing opening parts  123   c  and  123   d  of cylindrical bodies  123   a  and  123   b  are formed to allow sensor unit  17  to be detachably attached to puncturing opening parts  123   c  and  123   d , and connectors  53   a  to  53   f  connected with electrical circuit section  15   c  are provided at the front end of puncturing opening parts  123   c  and  123   d . Further, signals from the detecting sensor of the puncturing needle are connected directly to electrical circuit section  15   c . Further, cap  124  can be attached to puncturing opening parts  123   c  and  123   d . Electrically conductive plate  124   a  is pasted in the surface where this cap  124  abuts on puncturing opening part  123   c  or puncturing opening part  123   d . Consequently, electrical circuit section  15   c  can decide whether sensor unit  17  is attached or cap  124  is attached, by detecting the electrically conducting states of adjacent connectors among connectors  53   a  to  53   f.    
         [0148]    Further, vacuuming means  125  (corresponding to vacuuming means  14  of Embodiment 1) continuing to vacuuming passages  125   a  and  125   b  is attached to cylindrical bodies  123   a  and  123   b . Further, electrical circuit section  15   c  (corresponding to electrical circuit section  15  of Embodiment 1) is provided next to cylindrical body  123   b . Electric battery  16  is accommodated replacably at the end opposite to the end where puncturing opening parts  123   a  and  123   d  are provided. 
         [0149]    With blood test apparatus  11   d  according to the present embodiment, laser emitting apparatus  121  and puncturing unit  122  are attached in predetermined locations, so that the user does not leave laser emitting apparatus  121  and puncturing unit  122  when the user goes outside. Further, laser emitting apparatus  121  and puncturing unit  122  are built inside one housing  123  and, consequently, are convenient to carry. Furthermore, both puncturing means can use same sensor unit  17 . 
         [0150]    Further, a vacuuming passage having the same function as vacuuming passage  18   e  explained referring to puncturing unit  18  of Embodiment 1 is formed in puncturing unit  122 , so that it is possible to supply a negative pressure to vacuuming chamber  14   b  formed in sensor unit  17  without leaking the negative pressure. Further, detecting sensor  122   b  having the same function as detecting sensor  18   y  explained referring to puncturing unit  18  of Embodiment 1, is provided inside hammer unit  122   a.    
         [0151]    The disclosure of Japanese Patent Application No. 2007-030017, filed on Feb. 9, 2007, including the specification, drawings and abstract, is incorporated herein by reference in its entirety. 
       INDUSTRIAL APPLICABILITY  
       [0152]    The present invention is applicable to a blood test apparatus that selectively uses a laser emitting apparatus that requires a supply of power and a needle-puncturing apparatus that does not require a supply of power as the puncturing means.