Abstract:
A method for analyzing an analyte in tissue fluid is disclosed. The method comprises: placing a collecting member in contact with the skin of a subject, wherein the collecting member is configured to collect and retain tissue fluid containing the analyte from the subject; collecting tissue fluid from the subject into the collecting member; detaching the collecting member from the skin of the subject; causing the analyte in the tissue fluid collected by the collecting member to diffuse in a liquid by supplying the collecting member with the liquid; and detecting the analyte diffused in the liquid. 
     An analyzer for analyzing an analyte in tissue fluid, and cartridge and kit for use in the analyzing method are also disclosed.

Description:
FIELD OF THE INVENTION 
       [0001]    The present invention relates to a method for collecting tissue fluid containing an analyte from a subject and analyzing the analyte in the collected tissue fluid, an analyzer for analyzing an analyte in tissue fluid, and a cartridge and kit for use in the analyzing method. 
       BACKGROUND 
       [0002]    There are known conventional methods for collecting tissue fluid from the skin of a living body, and measuring the glucose in the collected tissue fluid. 
         [0003]    The analyzing method disclosed in WO95/02357 uses a reservoir configured by a two-sided adhesive layer for adhering to the skin of a patient and a cellophane plastic cover adhered to the two-sided adhesive in which a hole is formed, and a measuring unit for measuring the concentration of the glucose collected by a collection medium. The reservoir is adhered to the skin of the patient and water is injected through the hole of the reservoir using a syringe in the analyzing method disclosed in WO95/02357. When a predetermined time elapses, the water injected into the reservoir is periodically collected via the syringe and the collected water is discharged to the measuring unit, which measures the concentration of the glucose contained in the water. 
         [0004]    United States Patent Application 2005-0169799 discloses a living body component analyzer provided with a living body component extraction cartridge for extracting a living body component, and an analyzing unit capable of detachably holding the living body component extraction cartridge. The living body component extraction cartridge is provided with an extraction chamber configured by an extraction concavity having an opening on the bottom surface thereof, and a sealing film that covers part of the extraction concavity, and further has a reaction section that communicates with the extraction chamber through a flow path. The reaction section is provided with a sensor member containing an enzyme that is a catalyst for glucose. The analyzing unit is provided with a syringe pump for introducing physiological saline solution into the extraction chamber disposed in the cartridge. 
         [0005]    The living body component analyzer performs glucose analysis as follows. The cartridge is first loaded in the analyzing unit, and the living body component analyzer is attached to the skin so that the sealing film on the bottom surface of the cartridge is in contact with the skin of the subject. A space enclosed by the extraction cartridge on the skin of the subject is thus formed. Physiological saline introduced from the syringe pump fills the enclosed space, and glucose is extracted from the skin to the physiological saline. The saline filling the extraction chamber flows through the flow path to the reaction section, and the glucose in the physiological saline reacts with the enzyme in the reaction chamber. The analyzing unit outputs signals based on the reaction product of the glucose and the enzyme, and the amount of glucose is calculated. 
       SUMMARY OF THE INVENTION 
       [0006]    The scope of the invention is defined solely by the appended claims, and is not affected to any degree by the statements within this summary. 
         [0007]    A first aspect of present invention is a method for analyzing an analyte in tissue fluid, comprising: placing a collecting member in contact with a skin of a subject, wherein the collecting member is configured to collect and retain tissue fluid containing an analyte from the subject; collecting tissue fluid from the subject into the collecting member; detaching the collecting member from the skin of the subject; causing the analyte in the tissue fluid collected by the collecting member to diffuse in a liquid by supplying the collecting member with the liquid; and detecting the analyte diffused in the liquid. 
         [0008]    A second aspect of present invention is an analyzing apparatus for analyzing an analyte in tissue fluid, comprising: an accommodating part configured to accommodate a collecting member containing tissue fluid collected from a subject; a reservoir configured to retain liquid, wherein the reservoir is arranged in communication with the accommodating part; a liquid transporter configured to transport liquid to the accommodating part and to transport liquid to the reservoir from the accommodating part; and a detector for detecting an analyte in the liquid transported into the reservoir by the liquid transporter. 
         [0009]    A third aspect of present invention is a cartridge configured to be detachably installed in an analyzing apparatus for analyzing an analyte in tissue fluid, the cartridge comprising: an accommodating part configured to accommodate liquid supplied from the apparatus and a collecting member containing tissue fluid collected from a subject so that the collecting member is in contact with the liquid; and a reservoir arranged in communication with the accommodating part, wherein the reservoir is configured to retain liquid transferred from the accommodating part. 
         [0010]    A fourth aspect of present invention is an analyzing kit for analyzing an analyte in tissue fluid, comprising: a collecting member for collecting and retaining tissue fluid collected from a subject; and the cartridge. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0011]      FIG. 1  is an external perspective view of an embodiment of the analyzing apparatus; 
           [0012]      FIG. 2  is a schematic view showing the structure of the liquid transporter; 
           [0013]      FIG. 3  is a schematic view showing the structure of the liquid discharger; 
           [0014]      FIG. 4  is a block diagram of the controller; 
           [0015]      FIG. 5  is an external perspective view of the analyzing cartridge; 
           [0016]      FIG. 6A  is a top view of the collecting member  50 ; 
           [0017]      FIG. 6B  is a section view of the collecting member  50 ; 
           [0018]      FIG. 7  is a top view showing the structure of the analyzing cartridge body; 
           [0019]      FIG. 8  is a top view showing the structure of the bottom surface of the analyzing cartridge body; 
           [0020]      FIG. 9  is a flow chart illustrating the method of analyzing the analyte in the tissue fluid using the analyzing apparatus of the present embodiment; 
           [0021]      FIG. 10  is a flow chart illustrating the process of step S 7  in  FIG. 9 ; 
           [0022]      FIGS. 11A through 11G  are schematic views illustrating the operation of the analyzing apparatus of the present embodiment; 
           [0023]      FIG. 12  is a schematic view illustrating the blood glucose AUC measurement principle; 
           [0024]      FIG. 13  is a schematic view illustrating the blood glucose AUC measurement principle; 
           [0025]      FIG. 14  is a top view showing a modification of the analyzing cartridge; and 
           [0026]      FIG. 15  is a schematic view showing a modification of the apparatus body. 
       
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
       [0027]    Hereinafter, an embodiment of a blood analyzer of the present invention will be described in detail with reference to the accompanying drawings. 
         [0028]      FIG. 1  is an external perspective view of an embodiment of the analyzing apparatus. The analyzing apparatus  1  of the present embodiment is configured by an apparatus body  10  and analyzing kit  20 , as shown in  FIG. 1 . The analyzing kit  20  is configured by an analyzing cartridge  30  and collecting member  50 . The analyzing apparatus  1  obtains a value corresponding to the blood glucose concentration AUC (area under the curve) by collecting tissue fluid from a subject via the collecting member, and obtaining the concentration of analytes (glucose and sodium ions) in the tissue fluid in the collecting member. More specifically, the analyzing apparatus  1  is used in the manner described below. Micropores are first formed in the skin of the subject, and the collecting member  50  is adhered to the skin where the micropores have been formed. The collecting member  50  is then removed from the skin of the subject and adhered to the analyzing cartridge  30 , whereupon the analyzing cartridge  30  is installed in the cartridge holder  12  of the apparatus body  10 , as indicated by the dashed line in  FIG. 1 . The apparatus body  10  executes predetermined analysis processing of the collecting member adhered to the analyzing cartridge installed in the cartridge holder  12 , obtains the glucose concentration in the tissue fluid collected in the collecting member  50 , and obtains a value corresponding to the blood glucose AUC. 
         [0029]    The structure of the apparatus body  10  is described below with reference to  FIG. 1 . As shown in  FIG. 1 , the apparatus body  10  is a thick rectangular housing with a concavity  11  formed in the sheet on the top surface of the housing. The cartridge holder  12  is configured by a concavity that is deeper than the concavity  11 , and is disposed within the concavity  11 . A cover  13  has the same thickness as the height of the side wall of the concavity  11 , and is coupled to the concavity  11 . The cover  13  is coupled to the side wall of the concavity  11  by a support shaft  131  extending horizontally from the side wall of the cover  13  and fitted into the side walls of the concavity  11 . The cover  13  becomes housed within the concavity  11  when rotated on the support shaft  131  from the state shown in  FIG. 1 . The cover  13  also becomes unhoused when rotated on the support shaft  131  from the housed state in the concavity  11  to the upright state shown in  FIG. 1 . The cartridge holder  12  is of sufficient size to be capable of housing the analysis cartridge  30  to be described later. 
         [0030]    The cover  13  is supported on the support shaft so as to be forced in the direction of being housed in the concavity  11 . The analyzing cartridge  30  disposed in the cartridge holder  12  therefore can be held from above by the cover  13 . An injection nipple  141  and discharge nipple  151  provided so as to protrude from the bottom surface of the cartridge holder  12  are flexible members (to be described later) and thus function as cushioning members when pressed by the cover  13 . Concern of leakage is reduced since the adhesion of the nipples and induction port and discharge port formed in the analyzing cartridge  30  is made more rigid because the cover  13  presses the analyzing cartridge  30  from above. 
         [0031]    The apparatus body  10  has an internal liquid transporter  14  and liquid discharger  15 . The liquid transporter  14  is a mechanism for delivering a liquid to the analyzing cartridge  30  loaded in the cartridge holder  12 . The liquid discharger  15  is a mechanism for discharging effluent that has been delivered to the analyzing cartridge by the liquid transporter  14 . 
         [0032]      FIG. 2  is a schematic view showing the structure of the liquid transporter. As shown in  FIG. 2 , the liquid transporter  14  has an injection nipple  141 , pump  142 , and collection liquid tank  144 . 
         [0033]    The pump  142  and collection liquid tank  144  are connected by an upstream flow path  143 . The collection liquid tank  144  and injection nipple  141  are connected by a downstream flow path  126 . The pump  142  and injection nipple  141  are connected by a detour flow path  146  that detours around the collection liquid tank  144 . A solenoid valve V 1  is provided at the connection point between the upstream flow path  143  and the detour flow path  146 . A solenoid valve V 2  is provided at the connection point between the downstream flow path  145  and the detour flow path  146 . A solenoid valve V 3  is provided in the downstream flow path  145  on the downstream side from the connection point of the detour flow path  146 . The flow path between the solenoid valves V 2  and V 3  is a discharge flow path  147  that extends to a discharge tank  153  of the discharger  15  to be described later. 
         [0034]    The injection nipple  141  protrudes upward from the cartridge holder  12 , and supports the analyzing cartridge  40  from below together with the discharge nipple  151  (to be described later) when the analyzing cartridge  30  is installed in the cartridge holder  12 . The analyzing cartridge  30  loaded in the cartridge holder  12  receives injected liquid through the injection nipple  141 . The injection nipple  141  is formed of a flexible member such as rubber or the like. The discharge nipple  151  (described later) is similarly formed. Thus, there is no leakage of liquid because the induction port and discharge port formed in the analyzing cartridge  30  are in gapless contact when the analyzing cartridge  30  is loaded in the cartridge holder  12 . 
         [0035]    The pump  142  delivers air into the flow path via the operation of a motor that is not shown in the drawing. 
         [0036]    The collection liquid tank  144  retains the collection liquid injected into the analyzing cartridge  30 . Note that consideration is given to the influence of impurities in the collection liquid on the detection of glucose and sodium ions. Therefore, it is preferable that the collection liquid is substantially free of impurities. From this perspective, pure water is retained as the collection liquid in the liquid collection tank  123  in the present embodiment. 
         [0037]    Note that, although not shown in the drawing, the collection liquid tank  144  is configured to be removable from the outside of the apparatus body  10 , and replacement of the collection liquid is performed by replacing the collection liquid tank  144 . 
         [0038]    The solenoid valve V 1  operates a valve to switch the connection between the upstream flow path  143  and the collection liquid tank  144 , and the connection between the upstream flow path  143  and the detour flow path  146 . The solenoid valve V 2  operates a valve to switch the connection between the downstream flow path  145  and the collection liquid tank  144 , and the connection between the downstream flow path  147  and the detour flow path  146 . The solenoid valve V 3  operates a valve to switch the operation of the downstream flow path  145 . 
         [0000]    The liquid transporter  14  delivers a predetermined amount of the collection liquid retained in the collection liquid tank  144  to the analyzing cartridge  30  by pumping air from the pump  141  via the configuration described above. The specific operation of the liquid transporter  14  will be described later. 
         [0039]      FIG. 3  is a schematic view showing the structure of the liquid discharger  15 . As shown in  FIG. 3 , the discharger  15  has a discharge nipple  151 , flow path  152 , and liquid discharge tank  153 . 
         [0000]    The discharge nipple  151  protrudes upward from the cartridge holder  12 , and supports the analyzing cartridge  30  from below together with the previously mentioned injection nipple  141  when the analyzing cartridge  30  is installed in the cartridge holder  12 . The collection liquid delivered to the analyzing cartridge  30  by the liquid transporter  14  is taken through the discharge nipple  151 . 
         [0040]    The liquid discharge tank  153  is connected to the discharge nipple  151  through the flow path  152 , and retains the collection liquid (effluent) taken from the discharge nipple  151 . Note that, although not shown in the drawing, the liquid discharge tank  153  is configured to be connectable outside the apparatus body  10  so as to discharge the effluent outside the apparatus body  10 . 
         [0041]    The apparatus body  10  is further configured by a glucose detector  21 , sodium detector  22 , display part  23 , operation part  24 , and controller  25 . 
         [0042]    The glucose detector  21  is disposed on the back surface of the cover  13 . That is, the glucose detector  21  is provided on the surface of the cover  13  that faces the cartridge holder  12  when the cover  13  is housed in the concavity  11 . The glucose detector  21  has a light source  211  for emitting illumination light, and a light receiver  212  for receiving the reflected light emitted from the light source  211 . Thus, the glucose detector  21  is configured to irradiate light on the analyzing cartridge  30  installed in the cartridge holder  12 , and receive the reflected light from the irradiated analyzing cartridge  30 . The analyzing cartridge  30  includes a glucose reactor  330  that changes color through chemical reaction with the glucose in the tissue fluid collected from a living body in a manner to be described later. The glucose detector  21  detects the change in the light absorbance of the glucose based on the reflected light, and quantifies the glucose from the obtained reflected light. 
         [0043]    The sodium detector  22  is disposed on the bottom surface of the cartridge holder  12 . The sodium detector  22  has a rectangular plate-like member on the bottom surface of the cartridge holder  12 , and a pair of electrodes for measuring sodium ion concentration disposed in the approximate center of the plate-like member. The sodium ion concentration measuring electrodes include sodium ion selective electrode formed of silver/silver chloride and provided with a sodium ion selective film, and an opposed electrode formed of silver/silver chloride. The surface of the plate-like member is covered by a flexible material that functions as a cushion member when the analyzing cartridge  30  installed in the cartridge holder  12  is pressed by the cover  13 . The plate-like member forms a space by enclosing the concavity on the bottom surface of the analyzing cartridge  30  (first connecting flow path, sodium detection retainer, second connecting flow path (refer to FIGS.  7  and  8 )), and this space functions as a flow path for the passage of the liquid. From the perspective of preventing liquid leakage, it is therefore desirable that the analyzing cartridge  30  and plate-like member make gapless contact. In the present embodiment, the adhesion between the analyzing cartridge  30  and the plate-like member is improved by coating the surface of the plate-like member the flexible material, and pressing down on the analyzing cartridge  30  from above via the cover  13 . 
         [0044]    The display part  23  is provided on the top surface of the apparatus body  10 , and includes a liquid crystal panel. The display part  23  functions to display an operation screen for the user performing operations, and display measurement results when measurements have been completed. 
         [0045]    The operation part  24  is disposed on the top surface of the housing of the apparatus body  10 , and includes a plurality of buttons. A user specifies the start of a measurement, shutdown and the like to the controller  25  by performing operations via these buttons. 
         [0046]    The controller  25  is provided within the apparatus body  10 .  FIG. 4  is a block diagram indicating configuration of controller  25  of the present embodiment. Controller  25  comprises CPU  251 , ROM  252 , RAM  253  and input/output interface  254 . These components are respectively connected to each other via bass  256 . Controller  25  is connected to each of the mechanisms (operation part  24 , display part  23 , glucose detector  21 , sodium detector  22  and liquid transporter  14 ). The CPU controls the operations of the mechanisms by reading and executing programs stored in the ROM  252 . The RAM  253  is used as a program development area when executing the programs stored in the ROM  252 . 
         [0047]    The structure of the analyzing kit  20  is described below. As shown in  FIG. 1 , the analyzing kit  20  of the present embodiment is configured by the analyzing cartridge  30 , and collecting member  50  adhered to the analyzing cartridge  30 . The analyzing kit  50  provides the collecting member  50  and analyzing cartridge  30  as separate bodies before use in analysis, and the collecting member  50  is adhered to the analyzing cartridge  30  when to be used for analysis. 
         [0048]      FIG. 5 , is a perspective view showing the collecting member  50  adhered to the analyzing cartridge  30 . As shown in  FIG. 5 , the analyzing cartridge  30  mainly has a cartridge body  310  and glucose reactor  330 . Note that the structural details of the cartridge body  310  are omitted in  FIG. 5 . 
         [0049]    The collecting member  50  is described below with reference to  FIG. 6 , and the analyzing cartridge  30  is described below with reference to  FIGS. 5 ,  7 , and  8 . 
         [0050]      FIG. 6A  is a top view showing the structure of the collecting member  50 . In  FIG. 6A , the bottom surface of the collecting member  50  (the surface in contact with the skin in  FIG. 1 ) is exposed. In the following description, the surface of the collecting member  50  contacting the skin is the bottom surface and the back panel is the top surface. 
         [0051]    The collecting member  50  has a gel  501  and adhesive film  502 , and is configured so that the gel  501  is maintained in the approximate center of the adhesive film  502 . 
         [0052]    While the gel  501  is maintained in this state, the gel has water retention characteristics and is capable of retaining the tissue fluid collected from the skin of the subject. The gel  501  collects the tissue fluid that contains analytes (glucose and sodium ions) from the living body. Thus, the gel  501  does not substantially contain either glucose or sodium ions among its constituents. In the present embodiment, the gel  501  is polyvinyl alcohol. The gel  501  of the present embodiment is formed in an approximate rectangular shape measuring 12 mm (length)×7 mm (width)×0.7 mm (thickness). 
         [0053]    The adhesive film  502  is a member that does not transmit moisture and has a bottom surface with adhesive and a top surface without adhesive. The adhesive film  502  is an approximate square shape measuring 28 (28 mm. The bottom surface with the adhesive is adhered to the skin of the subject and the cartridge body  310 . The gel  501  is maintained in the approximate center of the adhesive film  502  by the adhesion to the bottom surface of the adhesive film  502 . 
         [0054]    The adhesive film  502  can be adhered to the skin while maintaining the gel  501  via the surface with the adhesive characteristics. Evaporation of the moisture collected by the gel  501  can be prevented by the material of the adhesive film that does not transmit moisture. Hence, the gel  501  prevents a change in the surface area in contact with the skin and evaporation while the gel  501  collects the tissue fluid, thus preventing fluctuation in the tissue fluid collection efficiency. Via its size, the adhesive film  502  seals the opening so as to prevent leakage of liquid from the opening in the gel accommodating part  311  (refer to  FIG. 7 ) when the cartridge body  310  is positioned on the gel accommodating part  311 . 
         [0055]      FIG. 6B  is a sectional view showing the collecting member  50  prior to use. The adhesive film  502  is adhered to a peelable sheet  503  in the pre-use state, and the adhesive surface and gel  501  are exposed by peeling the peelable sheet  503  for use. 
         [0056]    The analyzing cartridge  30  is described below. As shown in  FIG. 5 , the analyzing cartridge  30  is mainly configured by a glucose reactor body  330 , and cartridge body  310 . 
         [0057]    The glucose reactor body  330  contains reagents, including an enzyme (glucose oxydase (GOD)) catalyst for the glucose, an enzyme (peroxidase (POD)) catalyst for hydrogen peroxide (H 2 O 2 ) generated from the glucose via the presence of GOD, and color-producing agent tetramethylbenzidine (3,3′,5,5′-tetramethylbenzidine) for reacting with the activated oxygen ( 0 *) generated from the H 2 O 2  via the presence of POD. The glucose reactor body  330  is of sufficient shape and size as to be capable of fitting in the reagent holder  314  provided in the cartridge body  310  to be described later. 
         [0058]    The cartridge body  310  is configured by a rectangular acrylic plate measuring 24 mm (width)×56 mm (length)×3 mm (thickness), the surface of which is provided with a concavity (reagent holder  314 , refer to  FIG. 7 ) into which the glucose reactor body fits. The gel  501  is adhered to the surface of the collecting member  50  disposed in the concavity (gel accommodating part  311 , refer to  FIG. 7 ) formed in the surface of the cartridge body  310  as will be described later. In the following description, the surface of the cartridge body  310  on which the collecting member  50  is adhered (exposed surface in  FIG. 5 ) is the top surface, and the opposite surface is the bottom surface. The structure of the cartridge body  310  is described in detail below with reference to  FIGS. 7 and 8 . 
         [0059]      FIGS. 7 and 8  are top plan views of the cartridge body  310 . In  FIG. 7 , the structure of the top surface of the cartridge body  310  is indicated by a solid line, whereas the structure of the bottom surface is indicated by a dashed line. In  FIG. 8 , the structure of the bottom surface of the cartridge body  310  is indicated by a solid line, whereas the structure of the top surface is indicated by a dashed line. 
         [0060]    As shown in  FIGS. 7 and 8 , the cartridge body  310  is structurally configured by a gel accommodating part  311 , induction port  312 , upstream connection port  313 , reagent holder  314 , glucose detection reservoir  317 , downstream connection port  315 , and discharge port  316 , as viewed from the top. The cartridge body  310  also structurally has a first connection flow path  321 , sodium detection reservoir  322 , and second connection path  323 , as viewed from the bottom. These structures can be entirely obtained by depressions or pass-throughs. Hence, the cartridge body  310  of the present embodiment can be manufactured as an integrated single unit using well known and simple methods such as injection molding. 
         [0061]    According to this structure, the cartridge body  310  forms a single flow path from the induction port  312  to the discharge port  316  when the cartridge body  310  is installed in the cartridge holder  12  of the apparatus body  10 . 
         [0062]    The structure of the cartridge body  310  along the fluid flow is described below. 
         [0063]    The induction port  312  is a 0.7 mm diameter hole through the cartridge body from the top surface to the bottom surface. The induction port  312  is disposed so that the injection nipple of the cartridge holder  12  is directly therebelow in a vertical direction when the cartridge body  310  is installed in the cartridge holder  12  of the apparatus body  10 . Thus, the collection liquid is injected from the injection nipple  141  and through the induction port  312  into the gel accommodating part  311  when the cartridge body  310  is loaded in the cartridge holder  12 . 
         [0064]    The gel accommodating part  311  is a rectangular concavity measuring 14 mm (large side)×9 mm (narrow side) formed on the top surface of the cartridge body  310 . The previously mentioned induction port  312  is provided on the bottom surface of the gel accommodating part  311 . The gel accommodating part  311  accommodates the gel  501  measuring 12 mm (large side)×7 mm (narrow side)×0.7 mm (thickness) maintained on the previously mentioned collecting member  50  via the above described size. 
         [0065]    The gel accommodating part  311  accommodates the gel  501  maintained on the collecting member  50 . Specifically, the adhesive film  502  of the collecting member  50  is adhered to the margin of the gel accommodating part  311 , and the maintained gel  501  is suspended on the gel accommodating part  311  when the collecting member  50  is disposed in the gel accommodating part  311 . 
         [0066]    A step  318  configured by a depression deeper than the bottom surface of the gel accommodating part  311 , and the upstream connection port  313  are disposed at positions on a diagonal line of the induction port  312  on the bottom surface of the gel accommodating part  311 . The upstream connection port  313  is a 1.5 mm diameter hole passing through the cartridge body  310  from the top surface to the bottom surface. 
         [0067]    As shown in  FIG. 8 , the upstream connection port  313  is an opening on the bottom surface of the first connection flow path  321  configured by a channel having a depth of approximately 0.5 mm formed on the bottom surface. The first connection flow path  321  extends horizontally in the longitudinal direction of the cartridge body  310 , and connects to the sodium detection reservoir  322  formed in the approximate center of the bottom surface of the cartridge body  310 . 
         [0068]    The sodium detection reservoir  322  is a circular channel having an approximate depth of 1.5 mm. The sodium detection reservoir  322  is provided to be positioned in a vertical direction directly above the sodium detector  22  provided on the bottom surface of the cartridge holder  12  when the analyzing cartridge  30  is loaded in the cartridge holder  12  of the apparatus body  10 . More specifically, the sodium detection reservoir  322  is disposed such that the sodium selective electrode of the sodium detector  22  is positioned in the space circumscribed by the plate-like member and the sodium detection reservoir  322 . 
         [0069]    The sodium detection reservoir  322  connects to the second connection path  323  which is configured by a channel having an approximate depth of 0.5 mm. The second connection path  323  extends horizontally from the starting point of the sodium detection reservoir  322  through the step in the latitudinal direction of the cartridge body  310 , then changes direction 90 degrees and extends horizontally in the longitudinal direction, and subsequently changes direction 45 degrees and extends horizontally to the interior side. 
         [0070]    The downstream connection port  315  is formed on the base of the terminal end of the second connection path  323 . The downstream connection port  315  is a 1.7 mm diameter hole passing through the cartridge body  310  from the top surface to the bottom surface. 
         [0071]    Returning to  FIG. 7 , a reagent holder  314  is provided on the top surface of the cartridge body  310 . The reagent holder  314  is configured by a concavity having an approximate depth of 1 mm formed on the top surface of the cartridge body  310 . The reagent holder  314  has an approximate rectangular shape extending on the longitudinal direction of the cartridge body  310 . 
         [0072]    The reagent holder  314  is provided with a discharge path  317  configured by a channel deeper than the reagent holder  314 . The downstream connection port  315  is open to the bottom surface of the discharge path  317 . The discharge path  317  is configured by a channel having an approximate depth of 1.5 mm from the bottom surface of the reagent holder  314 . The discharge path  317  extends horizontally from the starting point of the position of the open downstream connection port  315  latitudinal direction of the cartridge body  310 , then changes direction 90 degrees and extends horizontally in the longitudinal direction, and subsequently changes direction 90 degrees and extends horizontally to the latitudinal direction, whereupon the direction again changes 90 degrees and extends horizontally in the longitudinal direction. A discharge port  316  is formed at the terminal end of the discharge path  317 . The discharge port  316  is a 0.7 mm diameter circular hole passing through the cartridge body  310  from the top surface to the bottom surface. The discharge port  316  is disposed so that the discharge nipple  151  of the cartridge holder  12  is positioned directly therebelow in a vertical direction when the cartridge body  310  is installed in the cartridge holder  12  of the apparatus body  10 . Thus, the discharge nipple  151  discharges collection liquid through the discharge port  316  when the cartridge body  310  is installed in the cartridge holder  12 . 
         [0073]    As can be clearly understood from the above description, the induction port  312  and the upstream connection port  313  are connected within the gel accommodating part  311 . The upstream connection port  313  and downstream connection port  315  are connected through the first connection path  321 , sodium detection reservoir  322 , and second connection path  323 . More specifically, the upstream connection port  313  and downstream connection port  315  are connected by a series of channels having a width and depth that allows the passage of the liquid between the horizontal surface and the bottom surface of the cartridge body  310  when the cartridge body  310  is disposed on the horizontal surface. The downstream connection port  315  and the discharge port  316  are connected through the discharge path  317 . 
         [0074]    Hence, the cartridge body  310  configures a single flow path from the induction port  312  to the discharge port  316  when placed on the horizontal surface. 
         [0075]    The function of the analyzing cartridge  30  of the present embodiment is described below in conjunction with the operation of the apparatus body  10 . 
         [0076]      FIG. 9  is a flow chart illustrating the method of analyzing analyte in tissue fluid using the analyzing apparatus of the present embodiment. 
         [0077]    In step S 1 , the subject performs preprocessing operation on the region from which tissue fluid is to be collected, that is, the subject washes the region with alcohol. Material (sweat, dirt and the like) adhered to the skin that might interfere with analysis is thus removed. 
         [0078]    In step S 2 , micropores are formed in the collection region that was washed with alcohol. Micropores are holes piercing through the stratum corneum of the skin and into the dermis to the boundary of the corium, but not extending so far as the deep dermis. The process of forming micropores can be performed using the micropore forming apparatus disclosed in US Patent Application Publication No. 2007-0233011. Tissue fluid is this collected from the subdermal tissue without extracting blood. 
         [0079]    In step S 3 , the collecting member  50  is adhered to the collection region in which the micropores are formed. More specifically, the gel  501  in the collecting member  50  is disposed relative to the skin so as to cover the region in which micropores are formed, and the adhesive film  502  holding the gel  501  is adhered to the margin of the region in which micropores are formed. The collecting member  50  is maintained thusly adhered to the skin for a predetermined time, for example 120 minutes or more, and tissue fluid flows from the skin through the micropores and is collected in the gel  501 . 
         [0080]    After the elapse of the predetermined time during which the collecting member  50  has been adhered to the skin, the process advances to step S 4  and the collecting member  50  is removed from the skin. 
         [0081]    In step S 5 , the collecting member that has been removed from the skin is adhered to the analyzing cartridge  30 . Details of adhering the collecting member  50  to the analyzing cartridge  30  have been described previously. 
         [0082]    In step S 6 , the analyzing cartridge  30  to which the collecting member  50  has been adhered is installed in the cartridge holder  12  of the apparatus body  10 . At this time, the analyzing cartridge  30  is disposed so that the sodium detection reservoir  322  is opposite the bottom surface of the cartridge holder  12 . 
         [0083]    After the analyzing cartridge  30  is installed in the apparatus body  10 , the cover  13  is closed on the apparatus body  10 . The analyzing cartridge  30  installed in the cartridge holder  12  is interposed between the injection nipple  141 , discharge nipple  151 , and sodium detector  12  and cover  13  and pressed from above by the cover  13  which exerts a force in the direction of closure. 
         [0084]    In step S 7 , the analytes in the collected tissue fluid are analyzed. Specifically, with the analyzing cartridge  30  installed in the cartridge holder  12 , the user operates the operation unit  24  of the apparatus body  10  to instruct the controller  25  to start the analysis. The controller  25  receives the instruction and performs analysis of the living body components by executing a predetermined program. The analysis includes obtaining the glucose concentration via cooperation between the controller  25  and glucose detector  21 , and obtaining the sodium ion concentration via cooperation between the controller  25  and the sodium detector  22 . This process is described later. 
         [0085]    When the analysis is completed by the apparatus body  10 , the analysis results are displayed on the display unit  23 . The subject confirms the displayed analysis results in step S 8 , and the series of operation ends. 
         [0086]      FIG. 10  is a flow chart illustrating the process of step S 7  in  FIG. 9 . Programs for executing the processes described above are stored in the ROM of the controller  25 , and the CPU of the controller  25  executes the processes shown in the flow chart by executing the programs stored in the ROM. 
         [0087]      FIGS. 11A through 11G  are schematic cross sectional views illustrating the operation of the analyzing apparatus of the present embodiment, and the time course of the flow of the collection fluid is indicated in the sequence A through G. Note that in  FIGS. 11A through 11G  the analyzing cartridge  30  is shown installed in the cartridge holder  12 , and the flow of air delivered by the pump  142  is indicated by the arrow while the flow of the collection fluid is indicated by the diagonal lines. The following description pertains to the operation of the analyzing apparatus  1  with reference to  FIGS. 11A through 11G . 
         [0088]    In step S 71 , the controller  25  determines whether a user-issued analysis start instruction has been received. When the controller  25  determines that an analysis start instruction has been received (step S 71 : YES), the process continues to step S 72 . When the controller  25  determines that an analysis start instruction has not been received (step S 71 : NO), the process returns to step S 71 . 
         [0089]    In step S 72 , the controller  25  executes a process for injecting collection liquid to collect the analyte in the tissue fluid collected in the gel  501 . Specifically, the controller  25  executes processes to connect the upstream path  143  and the pump  142  by controlling the solenoid valve V 1 , connect the pump  142  and the downstream path  145  by controlling the solenoid valve V 2 , and closes the connection between the downstream path  145  and the injection nipple  141  by controlling the solenoid valve V 3 . The controller  25  then executes a process to pump air to the flow path by actuating the pump  142  via a motor not shown in the drawings. Thus, the collection liquid reserved in the collection liquid tank  144  is pushed to the downstream path  145  and the discharge path  147 , and the collection liquid fills the flow path from the solenoid valve V 2  to the solenoid valve V 3  via the pushed collection liquid. 
         [0000]    The controller  25  then stops the actuation of the pump  142 , and subsequently executes processes to connect the upstream path  143  and detour path  146  by controlling the solenoid valve V 1 , connecting the detour path  146  and the downstream path  145  by controlling the solenoid valve V 2 , and opening the connection between the downstream path  145  and the injection nipple  141  by controlling the solenoid valve V 3 . Thus, a continuous flow path is formed from the pump  142  to the injection nipple  141  through the detour path  146 . The controller  25  then executes a process to reactuate the pump  142  and pump air into the flow path. Thus, the air pumped by the pump  142  is driven toward the injection nipple  141  through the upstream path  143 , detour path  146 , and downstream path  145 . At the point in time of switching the open/closed state of the solenoid valves V 2  and V 3 , the flow path from the solenoid valve V 2  to the solenoid valve V 3  is filled with a predetermined amount of collection liquid. The predetermined amount of collection liquid retained between the solenoid valves V 2  and V 3  is pushed toward the injection nipple  141  by the air pumped by the pump  142 , and the collection liquid in the discharge path  147  is pushed toward the discharge liquid tank  153  (refer to  FIG. 11C ). 
         [0090]    The injection nipple  141  is disposed so as to communicate with the induction port  312  of the analyzing cartridge  30  installed in the cartridge holder  12 , and the collection liquid moving toward the injection nipple  141  is injected into the gel accommodating part  311  through the injection nipple  141  and the induction port  312 . 
         [0091]    When injecting the collection liquid into the gel accommodating part  311 , the gel accommodating part  311  is filled with the injected collection liquid. Note that although the collection liquid injected into the gel accommodating part  311  moves the shortest distance from the induction port  312  toward the upstream connection port  313 , the collection liquid is maintained, via surface tension, at the step  318  before leaking from the upstream connection port  313  because the margin of the upstream connection port  313  is circumscribed by the step  318  which is one level higher than the opening of the upstream connection port  313 . Hence, the injected collection liquid spreads to the entirety of the gel accommodating part  311  without leakage from the upstream connection port  313  because the collection liquid is subjected to pressure in a direction to disperse to the entirety of the gel accommodating part and away from the direction of leaking from the upstream connection port  313  insofar as the pressure is not increased above the level of the surface tension by the effect of the step  318 . (Refer to  FIG. 11C ). Thus, it is possible to prevent a decrease in analysis precision caused by insufficient filling of the collection liquid in the gel accommodating part  311 . 
         [0092]    When the predetermined amount of collection liquid is injected into the gel accommodating part  311 , the gel  501  is embedded in the collection liquid (refer to  FIG. 11C ). The controller  25  temporarily stops the actuation of the pump  142  at the moment of completing the injection of the predetermined amount of collection liquid. Even though the actuation of the pump  142  is stopped, the collection liquid does not reverse flow from the induction port  312  due to the effect of the air pressure from below on the liquid at the surface of the induction port  312 . Since the flow path maintains constant air pressure by stopping the actuation of the pump  142 , the collection liquid that has filled the gel accommodating part  311  does not leak from the upstream connection port  313  and is maintained within the gel accommodating part  311 . 
         [0093]    In step S 73 , the controller  25  determines whether a predetermined time (for example, 10 minutes) has elapsed since the end of the injection of the collection liquid. When the controller  25  determines that the predetermined time has elapsed (step S 73 : YES), the process continues to step S 74 , whereas the process returns when the controller  25  determines that the predetermined time has not elapsed (step S 73 : NO), and the process of step S 74  is repeated until the predetermined time has elapsed. 
         [0094]    The tissue fluid collected in the gel  501  moves (disperses) into the collection liquid when the gel  501  is maintained in the embedded state in the collection liquid for the predetermined time. 
         [0095]    In step S 74 , the controller  25  executes a process to move the collection liquid retained in the gel accommodating part  311  to the sodium detection reservoir  322  and the glucose detection reservoir  314 . Specifically, the controller  25  controls the pump  124  so as to pump air of the same volume as the gel accommodating part  311  into the gel accommodating part  311 . When air is pumped into the gel accommodating part  311 , the pressure increases above the surface tension of the liquid on the surface of the upstream connection port  313 , and the collection liquid retained in the gel accommodating part  311  flows through the upstream connection port  313  to the first connection flow path  321 . 
         [0096]    When air is pumped to the gel accommodating part  311 , the collection liquid that flowed to the first connection path  321  arrives at the sodium detection reservoir  322  and fills the sodium detection reservoir  322 . When air is pumped into the gel accommodating part  311 , the collection liquid also arrives at the glucose detection reservoir  317  through the downstream connection port  315 . The collection liquid pumped to the glucose detection reservoir  317  comes into contact with the glucose reactor  330  maintained in the reagent holder  314  (refer to  FIG. 11E ). 
         [0097]    The collection liquid is thus mixed by the configuration in which the collection liquid retained in the gel accommodating part  311  is delivered to a different position in the gel accommodating part  311 . Hence, the concentration of the analyte in the collection liquid becomes uniform via the mixing of the collection liquid even though the analyte moved to the gel accommodating part  311  was unevenly diffused in the collection liquid. 
         [0098]    In step S 75 , the controller  25  executes processes for stopping the actuation of the pump  141 , and measuring the sodium concentration. 
         [0000]    As shown in  FIG. 11E , the sodium detector  22  provided on the bottom surface of the cartridge holder  12  is configured by an enclosed space with the sodium detection reservoir provided on the bottom surface of the analyzing cartridge  30 . The sodium detection reservoir  322  has a sodium ion concentration measuring electrode disposed so as to be exposed on the surface. The sodium ion concentration measuring electrode is completely immersed in the retained collection liquid when the collection liquid is retained in the sodium detection reservoir  322 . In this state, the controller  25  applies a constant current to the sodium ion concentration measuring electrode and obtains a voltage value, then obtains the sodium ion concentration CNa based on the obtained voltage value and a calibration curve prestored in the controller  25 . 
         [0099]    In step S 76 , the controller  25  executes a process for measuring the glucose concentration. 
         [0100]    The light source  121  and light receiver  122  are provided on the surface opposite the cover  13  of the analyzing cartridge  30 . As shown in  FIG. 11E , the glucose reactor  330  is held by the reagent holder  314  of the cartridge body  310 , and the glucose reactor  330  is immersed in the collecting liquid. The glucose that moved to the collection liquid produces chemical reactions described below via the GOD, H2O2, POD, and color-producing agent contained in the glucose reactor, and as a result the glucose reactor  330  changes color. 
         [0000]      Glucose+O2+H2O→(catalyst via GOD)→gluconic acid+H2O2 
         [0000]      H2O2+Color-producing agent→(catalyst via POD)→2H2O+color-producing agent (oxidation+color change) 
         [0101]    As can be understood from the chemical reaction equations above, the degree of coloration produced by the color-producing agent is proportional to the amount of glucose. Thus, the glucose concentration can be obtained by optically detecting the degree of color change of the color-producing agent. 
         [0102]    The present embodiment is configured so that light of a wavelength efficiently absorbed by the color following the color change of the color-producing agent is emitted from the light source  121  and irradiates the glucose reactor  330 . The light receiver  122  is configured to receive the reflected light of the light emitted from the light source  121 . The controller  25  obtains the glucose concentration CGlc based on the amount of received light by the light receiver  122  prior to the color change of the color-producing agent and the amount of light received by the light receiver after the color change of the color-producing agent. 
         [0103]    In step S 77 , the controller  25  executes a process for feeding the collection liquid retained in the analyzing cartridge  30  to the liquid discharger  15 . Specifically, the controller  25  executes a process for pumping air to the sodium detection reservoir  322  and the glucose detection reservoir  317  by reactuating the pump  142 . The pumped air pushes the collection liquid through the discharge nipple  151  toward the flow path  152  (refer to  FIG. 11F ), and the emitted collection liquid is collected retained in the discharge liquid tank  153  via the flow path  152 . 
         [0104]    In step S 78 , the controller  25  obtains the blood glucose AUC using the obtained sodium ion concentration CNa, and glucose concentration CGlc via equation (1) below, and stores the blood glucose AUC in the ROM. 
         [0000]        AUC =( C   Glc   ×E+F )× t /( C   Na   ×G+H )  (1) 
         [0000]    In the equation, t represents the tissue fluid collection time, and t=60 minutes in the present embodiment. E represents a constant. 
         [0105]    The principle of the calculation of the blood glucose AUC is described later. 
         [0106]    In step S 79 , the controller  25  displays, on the display unit  23 , the blood glucose AUC obtained in step S 78 , and the process returns to step S 8 . 
         [0107]    The principle of the blood glucose AUC measurement method is described below with reference to  FIGS. 12 and 13 . 
         [0108]    Generally, the glucose concentration in tissue fluid (IG(t)) is known to closely track the glucose concentration in blood (BG(t)), and there is a known strong correlation between the glucose concentration in tissue fluid (IG(t)) and the glucose concentration in blood (BG(t)). The glucose concentration in tissue fluid (IG(t)) is can be represented by equation (2) below using the constant α. 
         [0000]        BG ( t )=α× IG ( t )  (2) 
         [0109]    As shown in  FIG. 12 , when the gel  501  is adhered to the living body and tissue fluid is collected from the living body through the skin, the amount of glucose collected per unit time can be represented as glucose collection rate Jglc, and the glucose collection rate at a particular time t can be represented as Jglc(t). Jglc(t) at this time is represented as the sum of the glucose permeability Pglc and the tissue fluid glucose concentration IG(t) at time t, as shown in equation (3) below. 
         [0000]        J   glc ( t )= P   glc   ×IG ( t )  (3) 
         [0110]    Note that the glucose permeability Pglc is a coefficient representing the permeability of the glucose relative to the skin, and the larger the glucose permeability Pglc, the greater the amount of glucose collected from the skin per unit time. 
         [0111]    Consider now the case of a collection process performed for just a predetermined time T. On the left side of equation (3), when Jglc(t) is divided across the time T, the integral value becomes the total amount Mglt(t) of the glucose collected in the gel  501  from the living body within time T. The relationship can be expressed as shown in equation (4) below. 
         [0000]        M   glc ( T )=∫ J   glc ( t )  (4) 
         [0000]    For example, when the glucose collection rate Jglc(t)=10 ng/min, the total amount Mglc of the glucose collected in the gel  501  at time T=60 min becomes Mglt=10 ng/min×60 min=600 ng.
 
On the right side of equation (3), when the glucose concentration in tissue fluid IG(t) is divided across time T, the value becomes the area of the figure (crosshatched area) stipulated by the graph of the glucose concentration IG(t) during time T (that is, the area under the curve AUC(IG(t))). The relationship can be expressed as shown in equation (5) below.
 
         [0000]        AUC ( IG ( t ))=∫ IG ( t )  (5) 
         [0112]    As shown in equation (5), IG(t) and BG(t) have are correlated, and there is a further correlation between the area under the curve AUC(IG(t)) and the area under the curve AUC(BG(t)). Accordingly, the relationship between the area under the curve AUC(IG(t)) and the area under the curve AUC(BG(t)) can be expressed by equation (6) below using the constant α. 
         [0000]        AUC ( BG ( t ))=α× AUC ( IG ( t ))  (6) 
         [0113]    When considering the integral at time T, we can derive equation (7) below from equations (3) and (4). 
         [0000]        M   glc ( T )=∫ P   glc   ×IG ( t )  (7) 
         [0114]    Equation (8) below can be derived from equations (5) and (7). 
         [0000]        M   glc ( T )= P   glc   ×AUC ( IG ( T ))  (8) 
         [0115]    Mglc (T) can be expressed by equation (9) below using (BG(T)) via equations (6) and (8). 
         [0000]        M   glc =( P   glc /α) ×AUC ( BG ( T ))  (9) 
         [0116]    That is, using equation (9) we can obtain AUC(BG(T)) from the constant (, total amount Mglc(T) of the glucose accumulated in the gel  501  (refer to  FIG. 12 ) within time T, and the permeability of the glucose relative to the skin at time T (glucose permeability Pglc). Note that (may equal 1 since the blood glucose concentration and tissue fluid glucose concentration are virtually identical. The principle for calculating glucose AUC based on equation (1) is described below. 
         [0117]    The time area under the curve of blood glucose AUC(IG(T)) determined from the tissue fluid glucose can be determined from equation (10) below. 
         [0000]        AUC ( IG ( T ))= Mglc ( T )/ P   glc   (10) 
         [0118]    Mglc(T) is the amount of glucose accumulated in the gel  501  within time T (amount of accumulated glucose). The amount of accumulated glucose is proportional to the glucose concentration Cglc in the collection liquid when the glucose has moved from the gel  501  to the collection liquid if the collection liquid volume is constant. Thus, Mglc(T) can be expressed by equation (11) below using the constants E and F. 
         [0000]        M   glc ( T )= C   glc   ×E+F   (11) 
         [0119]    Pglc represents the ease of collecting the tissue fluid. The amount of collected tissue fluid changes depending on the condition of the skin (ease of collection). The amount of glucose contained in the tissue fluid changes depending on the glucose value. Therefore, the degree of collection of tissue fluid must be comprehended. The concentration of the sodium ions in the body is considered to be constant, unlike glucose. That is, a large amount of sodium ions contained in the collected tissue fluid is considered to indicate a good skin condition for the collection of tissue fluid. On the other hand, a low amount of collected sodium ions is considered to indicate a poor skin condition for the collection of tissue fluid. 
         [0120]    The ease of collecting tissue fluid Pglc can be expressed by equation (12) below using the collection rate J of the sodium ions contained in the tissue fluid. 
         [0000]        P   glc   =J×G+H   (12) 
         [0121]    The collection rate J is expressed by a value obtained by multiplying, by 1/t, the sodium ion concentration CNa of the sodium ions that moved from the gel  501  using the concentration of the sodium ions collected from the living body per unit time. Hence, we derive equation (13) below. 
         [0000]        J=C   Na ×1 /t   (13) 
         [0122]    Equation (14) is derived from equations (10) through (13). 
         [0000]        AUC ( IG ( T ))=( C   glc   ×E+F )/( C   Na ×1 /t )× G+H   (14) 
         [0123]    When the right side of equation (14) is reorganized, 
         [0000]        AUC =( C   Glc   ×E+F )× t /( C   Na   ×G+H )  (1) 
         [0000]    and we derive equation (1). 
         [0124]    Note that the embodiment and reference examples disclosed herein are in all aspects merely examples, and are not intended to be in any way limiting. The scope of the present invention is defined by the scope of the claims and not be the description of the embodiment or the reference examples, and includes all modifications within the scope of the claims and the meanings and equivalences therein. 
         [0125]    For example, although the present embodiment has been described by way of example in which a gel is used as the collecting body for collecting the tissue fluid, the present invention is not limited to this example inasmuch as tissue fluid may also be collected by material other than a gel if the material is adhered to the skin and possesses characteristics for holding the tissue fluid itself. For example, water absorbing paper, sponge, absorbent cotton, or a mesh sheet may also be used as the collecting body. 
         [0126]    Although the present embodiment has been described by way of example in which pure water is used as the collection liquid, the present invention is not limited to this example inasmuch as a material other than pure water may also be used if the material is a liquid that is substantially without impurities that may affect detection of the analytes to be detected. When detecting glucose and sodium ion as in the present embodiment, a material may be used that does not affect detection by bonding to the sodium ions, for example a liquid that contains positive ions such as potassium ions. Note that, although the effect of osmotic pressure on the diffusion of the tissue fluid in the gel may be considered, insufficient diffusion efficiency may occur when the osmotic pressure is small due to the difference in concentration of components contained in the tissue fluid. The difference in concentration between the collection liquid and the gel may be increased to facilitate diffusion of the tissue fluid in the gel by adding beforehand a high concentration of material that does not affect the detection in the collection liquid. 
         [0127]    Although the present embodiment has been described by way of example in which the apparatus body  10  and the analyzing cartridge  30  are separate bodies, the present invention is not limited to this example. For example, a structure equivalent to the analyzing cartridge  30  may be incorporated in the apparatus body  10 . 
         [0128]    Although the gel accommodating part  311  for accommodating the gel  501 , and the detectors (glucose detector  21  and sodium ion detector  22 ) for detecting the analytes (sodium ions and glucose) are installed separately in the embodiment, the present invention is not limited to this example. For example, a configuration also may be used in which analytes are detected in the collection liquid retained in the gel accommodating part  311  after the analytes have moved to the collection liquid from the gel held in the gel accommodating part  311  without moving the collection liquid. 
         [0129]    The configuration of the analyzing cartridge  30  of the present embodiment is not limited to the description referring to  FIGS. 7 and 8 , and may be variously modified. For example, a plurality of walls  350  may be provided in the gel accommodating part  311 , as shown in  FIG. 14 . According to this configuration, the collection liquid may unevenly distribute in the gel accommodating part  311 , and air present in the gal accommodating part  311  can be effectively pushed from the gel accommodating part to effectively prevent a mixture of air bubbles. 
         [0130]    Although the above embodiment has been described by way of example in which the glucose detection reservoir and sodium ion detection reservoir are provided as separate reservoirs, the present invention is not limited to this example inasmuch as a single reservoir may be provided in the analyzing cartridge, so as to detect and analyze the glucose and sodium ions present in the liquid retained in this single reservoir. 
         [0131]    Although the above embodiment has been described by way of example in which glucose detector  21  and the sodium detector  22  are stacked in a vertical direction, the present invention is not limited to this example inasmuch as, for example, the glucose detector  22  and the sodium detector  22  may be placed side by side in a horizontal deployment. 
         [0132]    Although the above embodiment has been described by way of example in which the glucose detector  21  optically measures the glucose concentration, the present invention is not limited to this configuration inasmuch as, for example, a configuration may be used in which the glucose concentration is electrically measured. For example, the glucose detector  21  may be provided with an working electrode configured by a GOD enzyme film on a platinum electrode, and a counter electrode configured by a platinum electrode for electrically measuring glucose concentration. When measuring glucose concentration, these electrodes are immersed in the collection liquid retained in the glucose detection reservoir  317 , and a current value is obtained by applying a constant voltage to the electrode. The glucose concentration can be obtained based on the obtained current value because the obtained current value increases dependent on the glucose concentration in the collection liquid oxidized by the GOD enzyme film formed on the platinum electrode. 
         [0133]    Although the above embodiment has been described by way of example in which the liquid feed to the analyzing cartridge  30  is controlled based on the volume of pumped air, the present invention is not limited to this configuration. For example, a sensor may be provided to detect whether the collection liquid has been fed to a predetermined position, so that the actuation of the pump can be stopped when the sensor has detected the liquid. Such an example is shown in  FIG. 15 .  FIG. 15  shows a modification of the analyzing apparatus. This analyzing apparatus is provided with a positive terminal  601  protruding into the downstream path of the solenoid valve V 3  of the downstream flow path  145 , a negative terminal  602  protruding to the pedestal of the sodium detector  22 , and a sensor  600  connected to both terminals. The sensor  600  is configured to apply a current to the positive terminal  601 , and is capable of detecting a short circuit between the positive terminal  601  and the negative terminal  602 . 
         [0134]    As shown in  FIG. 15 , when the collection liquid reaches the first connection path  321  of the analyzing cartridge  30 , the collection liquid short circuits the circuit between the positive terminal  601  and the negative terminal  602 . The sensor  600  detects the short circuited terminals and outputs a detection signal to the controller through a signal line not shown in the drawing, then the controller  25  receives the detection signal and stops the actuation of the pump  142 . 
         [0135]    According to this configuration, the sensor  600  reliably detects the liquid feed to the analyzing cartridge  30 . 
         [0000]    In the above modification, the controller  25  may also output an error when a detection signal is not received from the sensor  600  within a predetermined time after the pump  142  has been actuated. When a detection signal has not been received within a predetermined time after the pump  142  has been actuated, an error may be output to alert the user that an analysis error has occurred because it is thought that the liquid transport  14  is faulty, poor contact between the injection nipple  141  and the induction port  142  or the like. 
         [0136]    Although the above embodiment has been described by way of example in which a gel is used to collect the tissue fluid, the present invention is not limited to this example inasmuch as a material other than a gel may be used if the material is capable of maintaining a configuration that holds the tissue fluid obtained from a living body. 
         [0137]    Although a gel configured by polyvinyl alcohol is used as the gel  501  in the above embodiment, a gel configured by cellulose or polyacrylic acid may also be used as the gel  501 . 
         [0138]    Although the above embodiment has been described by way of example in which the glucose AUC is calculated and output based on the measurement result of measuring the glucose concentration and sodium ion concentration, the present invention is not limited to this example inasmuch as just one of either the glucose concentration or sodium ion concentration may be measured and the measurement result output. 
         [0139]    Although the above embodiment has been described by way of example in which glucose and sodium ions in tissue fluid are measured, the present invention is not limited to this example inasmuch as substances other than glucose and sodium ions contained in tissue fluid may be quantified. For example, biochemical components or drugs administered to the subject may be the substance measured by the present invention. One type of biochemical component are proteins such as albumin, globulin and the like, which may be considered as the chemical component. Biochemical components other than proteins include creatinine, creatine, uric acid, fructose, galactose, pentose, glycogen, lactic acid, pyruvic acid, ketone body and the like. Examples of drugs include digitalis, theophylline, arrhythmia agent, antiepileptics, amino glycoside antibiotic, glycopeptide antibiotic, antithrombotic, immunosuppressant and the like.