Abstract:
An apparatus comprising a substrate, the substrate having supported thereon:
       plural collectors each for collecting a bodily fluid from the surface of a body part placed adjacent thereto;   an analyser for analysing each collected bodily fluid; and   a display for displaying an indication of a result of each analysis.

Description:
CROSS REFERENCE TO RELATED APPLICATIONS 
     The present application is a U.S. National Phase Application pursuant to 35 U.S.C. §371 of International Application No. PCT/EP2012/055256 filed Mar. 22, 2012, which claims priority to European Patent Application No. 11159864.5 filed Mar. 25, 2011. The entire disclosure contents of these applications are herewith incorporated by reference into the present application. 
     FIELD OF INVENTION 
     This invention relates to a bodily fluid analysis device. 
     BACKGROUND 
     Many people are required to perform regular tests on their blood or other bodily fluid in order to monitor a disease and adjust medication appropriately. For example, diabetes sufferers may be provided with quantities of insulin, for instance by injection, sometimes a number of times daily. The quantity of insulin that is appropriate depends on the person&#39;s blood glucose level, so blood glucose level measurement can also occur a number of times daily. 
     Blood glucose level measurement typically is a multi stage process requiring a number of separate pieces of equipment. A user may be required to carry around a bulky electronic blood glucose meter as well as a supply of test strips and lancet. After lancing the skin to elicit a blood sample, a user must transfer the blood to the test strip, activate the meter and present or insert the test strip into the meter in order to obtain a measurement. 
     U.S. Pat. No. 7,378,007 B2 discloses a device having a lancet and electrochemical sensor for measuring a blood glucose level. In particular, this document discloses (see column 8) that the sensor and display of the device are disposed on or within a main housing of the device. Separate from the main housing of the device is a sensor disk supporting a plurality of radially arranged sensors. The sensor disk is secured to a spacer ring which is in connection with the main housing via a cam ring. The cam ring may be secured to the main housing by a screw or similar fastening. Thus U.S. Pat. No. 7,378,007 B2 discloses a complex, multi-part device in which various components of the device are supported on separate substrates which are then assembled together. 
     U.S. Pat. No. 7,641,857 discloses a measuring apparatus having a test element containing an analyte. Adjacent to the test element is a detector for detecting for detecting, optically or electrochemically, a change in the test field and generating an electrical signal. This electrical signal is used to form a measurement result. This document discloses no other detectors or electrical signals. 
     SUMMARY 
     A first aspect of the invention provides an apparatus comprising a substrate, the substrate having supported thereon: 
     plural collectors each for collecting a bodily fluid from the surface of a body part placed adjacent thereto; 
     at least two pairs of electrodes integral with each of the collectors; 
     an analyser for analysing each collected bodily fluid, wherein the analyser comprises a controller, wherein each of the at least two pairs of electrodes are connected to the analyser and wherein the analyser is configured to analyse at least one electrical signal received via a first pair of the at least two pairs of electrodes; and 
     a display for displaying an indication of a result of each analysis, wherein the apparatus is configured to activate the analyser in response to a predetermined electrical signal received via a second pair of the at least two pairs of electrodes. 
     A bodily fluid collecting end of each of the collectors may be covered by a removable seal. Each removable seal may provide a fluid impermeable barrier around the bodily fluid collecting end of the respective collector. 
     The apparatus may be configured to activate the display in response to a predetermined electrical signal received via the second pair of electrodes. Alternatively, the apparatus may be configured to activate the display in response to a predetermined electrical signal received via a third pair of the at least one pair of electrodes integral with each collector. 
     Each second pair of electrodes may be located further from a bodily fluid collecting end of the respective collector than each first pair of electrodes. Each third pair of electrodes may be located closer to a bodily fluid collecting end of each collector than each first pair of electrodes. 
     The apparatus may further comprise an adjustable calibration resistor. The substrate may be disc shaped and the plural collectors may be arranged generally radially on the substrate. The apparatus may further comprise a cover plate and a glue layer disposed between the substrate and the cover plate, wherein the glue layer is structured so as to define a maximum extent of each of the collectors. The cover plate may have a plurality of notches in an outer edge of the cover plate, each notch being aligned with a respective collector. 
     A second aspect of the invention provides a method for analysing a bodily fluid sample, comprising: 
     a bodily fluid analysis device receiving a bodily fluid sample at one of a plurality of bodily fluid collectors formed therewith; 
     the bodily fluid analysis device detecting a predetermined electrical signal received via a second pair of at least two pairs of electrodes integral with each bodily fluid collector; 
     in response to detecting the predetermined signal, activating a controller and analysing the collected bodily fluid sample using the controller by analysing at least one electrical signal received via a first pair of the at least two pairs of electrodes; and 
     the bodily fluid analysis device displaying an indication of a result of the analysis. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       Embodiments will now be described, by way of example only, with reference to the accompanying drawings, in which: 
         FIG. 1  is a side-on view of a first embodiment of a bodily fluid analysis device according to the invention; 
         FIG. 2  is a plan view of the bodily fluid analysis device of  FIG. 1 ; 
         FIG. 3  is a schematic illustration of some of the components of the bodily fluid analysis device of  FIGS. 1 and 2 ; 
         FIG. 4  shows a view of the underside of a cover plate forming part of the bodily fluid analysis device of  FIGS. 1 ,  2  and  3 ; 
         FIG. 5  shows detail of a cross-section of a portion of the bodily fluid analysis device of  FIGS. 1 to 3 ; 
         FIG. 6  is a view of the upper side of a substrate forming part of the bodily fluid analysis device of  FIGS. 1 to 3  and shows detail of some of the components formed thereon; 
         FIGS. 7A and 7B  show schematic illustrations of embodiments of the invention containing activation electrodes; 
         FIGS. 8A-D  show the bodily fluid analysis device of  FIGS. 1 to 3  in an exemplary operation;  FIG. 9  is a flow chart illustrating an exemplary operation of the bodily fluid analysis device of  FIGS. 1 to 3 . 
     
    
    
     DETAILED DESCRIPTION 
     Referring firstly to  FIGS. 1 and 2 , a side-on view and a plan view respectively of a bodily fluid analysis device  100  are shown. The analysis device  100  has a layered structure. The bottom layer comprises a substrate  102  in the form of a generally circular or disc-shaped sheet material. Formed on top of the substrate  102  are a number of electronic components that are described in detail below with reference to  FIG. 3 . The top layer of the device  100  comprises at least one cover plate  104  which covers and protects the components formed on top of the substrate  102 . Between the substrate  102  and the cover plate  104  is a glue layer  106 . 
     Disposed around the outer edge of the bodily fluid analysis device  100  and on top of the substrate  102  are a number of bodily fluid collection and testing segments  108 . Each collection and testing segment  108  has a region of absorbent material  110  extending inwardly from the edge of the bodily fluid analysis device  100 . The regions of absorbent material  110  are substantially rectangular in shape, although other shapes are possible. Each region of absorbent material  110  is formed directly onto the substrate  102 . The extent of the absorbent material  110  is illustrated by the dashed lines in  FIG. 2 . Each segment  108  also has at least one pair of electrodes, as described in greater detail below with reference to  FIG. 3 . 
     Notches  112  in the form of V-shaped indentations are provided in the outer edge of cover plate  104  at the position of each segment  108 . Vent holes  114  are provided in the cover plate  104  at positions coincident with an innermost extent of each region of absorbent material  110 . The substrate  102  also supports a display  116 . The display  116  is located at or near the centre of the bodily fluid analysis device  100 . The bodily fluid analysis device  100  also has removable seals  118  covering each notch  112  and the exposed ends of the regions of absorbent material  110 . The removable seals  118  are attached to the underside of the substrate  102 , to the upper face of cover plate  104  and to the outer edge of the bodily fluid analysis device  100 . 
     In the view of  FIG. 1 , only a single exposed collection and testing segment  108  is shown for clarity. The notch  112  and edge of the region of absorbent material  110  of this segment  108  can be seen. However, in reality several segments  108  are visible when the device  100  is viewed edge on. If these segments  108  have had their removable seals  118  removed then the notches  112  and edge of absorbent material  110  is visible. If the removable seal  118  has not been removed, then only the removable seal is visible. 
     The substrate  102  is formed of a non absorbent material. For example, the substrate  102  may be a plastic material or any other suitable material such as silicon. The substrate is preferably rigid. The cover plate  104  may be formed of any suitable material, for example a rigid or flexible plastic material. 
     Each of the segments  108  is arranged radially on the bodily fluid analysis device  100 . The entire outer edge/circumference of the bodily fluid analysis device  100  may support collection and testing segments  108 . Alternatively, the segments  108  may be arranged into two or more groups supported on different parts of the outer edge/circumference of the bodily fluid analysis device  100 . The bodily fluid analysis device  100  may support between 15 and 50, preferably between 25 and 35 collection and testing segments  108 . Each of the segments  108  contains a region of absorbent material  110  which is also arranged radially on the bodily fluid analysis device  100  such that a first end of the absorbent material  110  is coincident with an outer edge or circumference of the bodily fluid analysis device  100 . This first end of the absorbent material  110  is the bodily fluid collecting end and is exposed at the circumference of the bodily fluid analysis device  100  as shown in  FIG. 1 . The absorbent material  110  may be formed directly onto the substrate  102  or may be glued or otherwise secured to the substrate  102 . The absorbent material  110  may be disposed within the glue layer  106 , such that it is abutted on either side by the glue layer  106 . The notches  112  are formed in the cover plate  104  directly above the location where each region of absorbent material  110  meets the outer edge or circumference of the bodily fluid analysis device  100 . The notches  112  extend through the whole thickness of the cover plate  104  such that a portion of the top surface of the absorbent material  110  is exposed. 
     The absorbent material  110  may be a wicking material having a capillary structure. The absorbent material  110  may be a sheet material. Fluid applied to the exposed part of the absorbent material  110  is drawn into the body of the absorbent material  110  by capillary action. The vent holes  114  extend through the whole thickness of the cover plate  104  such that they contact each region of absorbent material  110  at an end of the absorbent material  110  opposed to the outer, exposed edge. The vent holes  114  facilitate the capillary action by allowing air within the absorbent material  110  to be displaced by fluid. 
     The absorbent material  110  may contain a chemical substance such as an enzyme. The absorbent material  110  may be doped with the chemical substance during manufacture. When bodily fluid is absorbed into the material  110 , it reacts with the chemical substance to create an electrical signal. The chemical substance present in the absorbent material  110  may be selected to react with specific target substance in the bodily fluid or to catalyze a reaction involving a target substance in the bodily fluid. For example, the bodily fluid may be blood and the target substance may be blood glucose. The blood glucose may react with a mediator in the absorbent material  110 . For example, the mediator may oxidize the glucose and may subsequently be reoxidised at the anode to produce electrical charge, and—with a corresponding redox-reaction at the cathode—a current. The mediator may be any suitable substance, for example Ferricyanide/Ferrocyanide. An enzyme, for example glucose oxidase, may be involved in the oxidation and reduction of the glucose. The target substance may be another component of blood, for example glycated haemoglobin (HbA1c) or a ketone. 
     The chemical substance may be present throughout the absorbent material  110  or it may only be present in a portion of the absorbent material  110 . In some embodiments, the absorbent material  110  is configured to absorb a predetermined amount of fluid. Depending on the bodily fluid which is being absorbed, the property of the fluid which is to be measured and the method by which the measurement is to be taken, the volume of fluid present in the absorbent material  110  may affect the measurement. Configuration of the absorbent material  110  to absorb a predetermined amount of fluid helps to improve measurement accuracy. 
     The display  116  may be a Liquid Crystal Display (LCD), comprising an LCD fill (not shown) and a LCD cover plate (not shown). The display  116  may alternatively be another type of suitable electronic display. The display  116  is configured to display a result of a measurement of a target substance in the bodily fluid. 
     The removable seals  118  may be made of a metal foil and may be impermeable to gas and/or liquid. A removable seal may be secured to the bodily fluid analysis device  100  so as to cover the notch  112 , exposed parts of the region of absorbent material  110  and the vent hole  114  such that no fluid is able to enter or leave the absorbent material  110  before the seal  118  is removed. Thus, the humidity (or absence of humidity) within the absorbent material  110  at manufacture is maintained until the time of use of the respective collection and testing segment  108 . The removable seals  118  may be secured to the surface of the bodily fluid analysis device  100  by an adhesive. The removable seals  118  may each have an unsecured portion or lip which can be grasped by a user of the bodily fluid analysis device  100  and pulled in order to remove the seal  118 . Each collection and testing segment  108  has its own removable seal  118  such that the removal of one seal  118  does not cause any exposure of the absorbent material  110  of another segment  108 . 
     Referring now to  FIG. 3 , a schematic view is shown in which electronic components supported on the substrate  102  are illustrated. In  FIG. 3 , the upper surface of the substrate  102  is shown. The substrate supports a controller  120 , display electronics  116  and batteries  122 . Each collection and testing segment  108  has a pair of measurement electrodes  124 . The controller  108  is connected to each pair of measurement electrodes  124  via conductive paths  126 . Each pair of measurement electrodes  124  overlaps with a respective region of absorbent material  110 , the extent of which is illustrated by the dashed line. The display  116 , controller  120  and batteries  122  are all located at or near the centre of the bodily fluid analysis device  100 . A calibration resistor  128  is disposed on a conductive path linking the controller  120  to one of the measurement electrodes  124 . The controller  120  is also connected to the display  116  via one or more conductive paths. The batteries  122  are disposed on a conductive path which begins and ends at the controller  120 . 
     The controller  120  is configured to receive electrical signals from the measurement electrodes  124  and to send control signals to the display  116 . The measurement electrodes  124  may be made of any conductive material, for example carbon or a metal. 
     The controller  120  may be a microcontroller or integrated circuit of any suitable type. The controller  120  may store software or algorithms in flash memory (not shown) and may have volatile memory such as RAM (not shown) for executing the software. The controller  120  is connected to each pair of measurement electrodes  124  in order to measure a property of the bodily fluid sample absorbed in the respective region of absorbent material  110 . 
     The batteries  122  are configured to provide power to the controller  120  and the display  116 . In some embodiments, the batteries  122  have an energy storage capacity which is sufficient only to power the controller  120  and to power the display  116  for a reasonable time, e.g. up to one hour. As the device  100  requires only a small amount of power, the batteries  122  may be replaced with another source of power such as a capacitor able to collect energy from radio frequency signals emitted by a mobile transmitting device such as a mobile phone. Thus a user of the device  100  may be able to power or charge the device  100  using an application on their mobile phone or the device  100  may charge by being in close proximity to the user&#39;s mobile phone for a short time. The device  100  may also be able to collect energy from ambient electromagnetic radiation. In some embodiments, the batteries  122  are replaced with means for collecting energy from a user of the device  100 . For example the device  100  may have an area which the user compresses between their fingers to impart energy to the device  100 . Alternatively the device  100  may contain both batteries  122  and other means for collecting energy. 
     The measurement electrodes  124  are disposed directly onto the substrate  102  and overlap with at least a portion of the absorbent material  110 . The absorbent material  110  may be applied to the substrate  102  after the measurement electrodes  124 . The measurement electrodes  124  may comprise a pair of electrodes spaced apart. The space between the electrodes  124  is at least partially occupied by absorbent material  110 . The measurement electrodes  124  are configured to transmit electrical signals generated by the reaction of bodily fluid with a chemical substance present in the absorbent material  110  to the controller  120  so that a property of the bodily fluid can be measured. This property may be a concentration of a specific substance present in the bodily fluid. 
     Each resistor  128  is disposed on a conductive path linking the controller  120  to one of the measurement electrodes  124 . This allows the electrical resistance of the circuit path formed by the controller  120 , measurement electrodes  124  and absorbent material  110  to be predetermined. The controller  120  may rely on having an accurate value for the resistance of this circuit path in order to produce an accurate measurement. The resistors  128  may be printed circuit resistors and may be printed on the substrate  102  with a carbon containing ink, for example. 
     The resistors  128  may be used for calibration, for example to adjust a lot to lot manufacturing accuracy of the device  100 . For example, after determining a calibration value of a lot of bodily fluid analysis devices  100  during production, the resistance of the resistor  128  may be adjusted by laser cutting or by modifying the printing process of resistor  128 . The resistance of resistor  128  may be used during use of device  100  as a calibration value to adjust a measurement result. 
     In alternative embodiments, a single resistor  128  is disposed on a conductive path that begins and ends at the controller  120  and does not incorporate any of the pairs of measurement electrodes  124 . 
     As previously mentioned, the volume of bodily fluid absorbed by the absorbent material  110  may, in some measurement techniques and for some target substances, affect the measurement of that target substance. The absorbent material  110  may therefore be manufactured to absorb a predetermined amount of fluid. This amount may depend on the structure and number of capillaries which form the absorbent material  110 . The concentration of chemical substance embedded in the absorbent material  110  and which reacts with the target substance in the bodily fluid may also affect the measurement of the target substance. Although efforts may be made to ensure that each device  100  is identical and each piece of absorbent material  110  used in these devices  100  is identical, there may be some batch variation in the absorptive capacity and chemical substance concentration within the absorbent material  110 , particularly when the devices are mass produced. Further, variation in the geometry due to manufacturing tolerances may effect the measurement. 
     During manufacture, one device  100  of each batch may be tested after it has been manufactured in order to determine a calibration value for the devices produced in that batch. In order for the device  100  to be able to produce an accurate measurement of a property of absorbed bodily fluid, the electrical resistance of the measurement circuit path may need to be accurate within a small tolerance. This may be achieved by measuring a control solution with an accurate concentration of analyte, such as glucose. In some embodiments, if an adjustment of the electrical resistance of the measurement circuit path is required, the resistors  128  can be trimmed with a laser such that their resistance is decreased. After the laser trimming a detached part of the resistor  128  no longer forms a part of the measurement circuit path. In this manner, batch variation in the properties of the absorbent material  110  can be corrected. 
     In alternative embodiments, a capacitor is used for storing a calibration value on the device  100  instead of a resistor  128 . Modifying the capacitor may be done by laser cutting or the printing process during production. 
     In alternative embodiments, a calibration value may be stored in a non-volatile memory of the device during production, for example in the flash memory. Thus, no dedicated resistor  128  or capacitor may be needed for calibration. 
     The display  116  may be a numerical display configured to display three digits. In some other embodiments the display  116  may be configured to display more than three digits. The best choice of display depends on the range and accuracy of the measured property required. In some embodiments, the display  116  may be configured to display a decimal point before or after the first or second digit. Alternatively the decimal point may be in a fixed location, for example after the second digit. Each digit of the display  116  may comprise a seven-segment display capable of displaying the numbers 0 to 9. Only a single connection between the controller  120  and the display  116  is shown, however there may be several individual connections. There may be a connection between the controller  120  and the display  116  for each digit, or for each segment of each digit, or there may be a multiplexed connection. 
     The device  100  is preferably relatively small in size, for example about 80-120 mm in diameter and less than 15 mm thick. This makes the device  100  easily portable for a user such that it may be easily carried around by the user. Because the functions of a test strip and analysis device are combined in a single device of small size, a user does not need to carry a separate meter, which may be a relatively bulky item. 
     Referring now to  FIG. 4 , a view of the underside of cover plate  104  is shown. Cover plate  104  has a display window  130 , a controller and battery cavity  132  and absorbent material cavities  134 . Notches  112  are provided in the outer edge of the cover plate  104  and are aligned with each absorbent material cavity  134 . The vent holes  114  are provided in the cover plate  104  at the innermost end of each absorbent material cavity  134 . 
     The display window  130 , notches  112  and vent holes  114  are cut out portions which are also visible from the upper side of the cover plate  104 . The controller and battery cavity  132  and absorbent material cavities  134  are recesses in the underside of the cover plate  104  which do not extend through the whole thickness of the cover plate  104  and are not visible from the upper side. The controller and battery cavity  132  provides a space for the controller  120 , batteries  122  and any other electronic components, such as resistors and capacitors, which may form a part of the power and control circuitry. The absorbent material cavities  134  provide a space for the region of absorbent material  110 . The absorbent material cavities  134  may be large enough to allow the region of absorbent material  110  to expand when saturated with fluid. 
     The display window  130  may have a transparent cover, such as a transparent piece of film, in order to protect the display  116  underneath from damage. Alternatively the display  116  may comprise a transparent cover plate (not shown), which may be made of a glass material. 
     Referring now to  FIGS. 5 and 6 ,  FIG. 5  shows a detailed cross-sectional view of the bodily fluid analysis device  100  at a position of one of the collection and testing segments  108 . The notch  112  in the cover plate  104  exposes some of a top surface of the absorbent material  110 . This makes the process of absorption of bodily fluid by the absorbent material  110  more efficient. Measurement electrodes  124  are formed directly onto the substrate  102 . The absorbent material  110  may also be formed directly onto the substrate  102  and may overlie the measurement electrodes  124  as shown in  FIG. 5 .  FIG. 6  shows a detailed view of the top surface of the substrate  102  and some of the components supported by the substrate  102 . The glue layer  106  is omitted from  FIG. 5  for reasons of clarity but is shown in  FIG. 6 . Exemplary positioning of the measurements electrodes  124  is shown in both  FIGS. 5 and 6 , however other electrode arrangements are possible as discussed in greater detail below. The glue layer  106  fills the area on the substrate between each collection and testing segment  108 . The glue layer covers the conductive paths located between each segment  108 . The glue layer  106  secures the cover plate  104  to the substrate  102 , but also separates the segments  108  from one another. This ensures that there are no environmental impacts e.g. increased humidity, on a segment  108  when an adjacent segment is exposed and also helps to ensure that no fluid absorbed in one segment  108  can leak into another. 
     In some embodiments the region of absorbent material  110  may be omitted. The absorbent material  100  may be replaced by a cavity with appropriate dimensions that acts as a capillary. In these embodiments, the glue layer  106  may also perform the function of a spacing layer to ensure that the capillary cavity is of a suitable width. 
     Although only a single pair of electrodes for each collection and testing segment  108  are illustrated in  FIGS. 3 ,  5  and  6 , the device  100  may comprise several pairs of electrodes for each segment  108 .  FIGS. 7A and 7B  show schematic illustrations of embodiments of the invention containing activation electrodes. 
     In  FIG. 7A  a single collection and testing segment  108  is shown on the substrate  102  for clarity. In this embodiment, the device  100  has a pair of measurement electrodes  124  and a pair of activation electrodes  136 . Both the measurement electrodes  124  and the activation electrodes  136  are connected to the controller  120  via conductive paths  126  and overlap the absorbent material  110 . In some embodiments the electrodes may only overlap partially with the absorbent material  110 . The activation electrodes  136  are configured to pass electrical signals generated in the absorbent material  110  to the controller  120 . These signals are used as a trigger for activation of the controller  120  and the display  116 . For example, the controller  120  may be configured to detect only signals above a certain threshold which are received from the activation electrodes  136 . When a signal above the threshold is detected, the controller  120  and display  116  are activated. The measurement electrodes  124  are located closer to the outer edge of the collection and testing segment  108  than the activation electrodes  136 . Therefore, as fluid is absorbed into the absorbent material  110 , the region between the measurement electrodes  124  is first saturated and then, provided enough fluid is available, the region between the activation electrodes  136  is saturated. This arrangement ensures that there is a sufficient quantity of bodily fluid in the region between the measurement electrodes  124  when the controller  120  and display  116  are activated. 
       FIG. 7B  shows another embodiment in which there are two pairs of activation electrodes and one pair of measurement electrodes  124 . In  FIG. 7B  a single collection and testing segment  108  is shown on the substrate  102  for clarity. The two pairs of activation electrodes are controller activation electrodes  138  and display activation electrodes  140 . The controller activation electrodes  138  are located closest to the outer edge of the collection and testing segment  108 . The measurement electrodes  124  are located behind the controller activation electrodes  138 ; further from the outer edge of the segment  108 . The display activation electrodes  140  are located behind the measurement electrodes  124 ; furthest from the outer edge of the segment  108 . In this embodiment, the controller  120  is configured to detect only signals above a certain threshold which are received from the controller activation electrodes  138  and display activation electrodes  140 . When a signal above a threshold value is detected via the controller activation electrodes  138 , the controller  120  is activated. The controller  120  may then begin recording signals received via the measurement electrodes  124 . When a signal above a threshold value is detected via the display activation electrodes  140 , the display  116  is activated. The display  116  may be activated in a standby mode. Since the display activation electrodes  140  are located further from the outer edge of the segment  108  than the controller activation electrodes  138 , the controller  120  is activated before the display  116 . This results in the display  116  being activated for the shortest possible time before a reading is displayed. This reduces the total amount of power required to make a measurement of a property of a bodily fluid and to display the result of the measurement to a user of the device  100  for a given period of time. 
     The signals from display activation electrodes  140  may also be used in the measurement of an analyte in the bodily fluid. For example, by measuring the time when the bodily fluid reaches the display activation electrodes  140 , a measurement of the viscosity or the amount of bodily fluid can be made. 
     In these embodiments containing activation electrodes, each of the pairs of electrodes are connected to the controller  108  via separate conductive paths  126  formed on the substrate  102 . The display  116 , batteries  122  and resistor  128  of the device  100  may be substantially the same as when only the measurement electrodes  124  are present. The controller  120  and display  116  only draw power from the batteries  122  when active. When inactive, the current discharge from the batteries  122  is zero or close to zero such that the shelf life of the device  100  is not affected. 
     Regarding the positioning of the pairs of electrodes within each collection and testing segment  108 , in some embodiments, each of the pairs of measurement electrodes  124  and activation electrodes ( 136 ,  138 ,  140 ) are arranged in parallel with a radial line connecting the segment  108  with a centre point of the device  100 , as shown in  FIGS. 3 ,  5  and  6 . In some other embodiments, each pair of electrodes is arranged perpendicularly to this radial line. This second arrangement is shown in  FIGS. 7A and 7B . The electrodes may be contained completely within the region of absorbent material  110 . Alternatively, the electrodes may overlap partially with the absorbent material  110 . 
     In some embodiments, the bodily fluid which is collected by the device  100  is blood and the property of the blood which is measured is the blood glucose level. The process of making a blood glucose level measurement with the device  100  will now be described with reference to  FIGS. 8A-D  and the flow chart of  FIG. 9 . 
     In operation, a user of the device  100  first removes one of the removable seals  118  from its respective collection and testing segment  108 , as shown in  FIG. 8A . To achieve this, a user grasps and pulls an end of the removable seal  118  which is not secured to the device  100 . Removal of the removable seal  118  exposes a notch  112 , a portion of the absorbent material  110  and a vent hole  114 . The removable seals  118  may be printed with numbers to allow the user to more easily monitor their usage of the device  100 . In  FIG. 8A  the user is removing the first of  30  removable seals  118 . 
     After removing the removable seal  118 , the user obtains a blood sample. This can be achieved by the user in any known way, for example by using a lancet or similar to elicit blood from their finger. In  FIG. 8B , the user has elicited a blood sample and is about to present the blood to the exposed end of the region of absorbent material  110 . Printed on the upper surface of the cover plate  104  is a unit in which the subsequent measurement is expressed. This may for example be mg/dl, mmol/l or mol/l. In some other embodiments this unit may instead be printed on a cover plate (not shown) of the display  116  itself. In some other embodiments, the unit of the measurement may be displayed by the display  116  and may only appear when the result of the measurement is shown. 
     In  FIG. 8C , the user has presented the blood to the absorbent material  110  by pressing their finger against the edge of the device  100  at the location of the corresponding notch  112 . The alignment of the notch  112  with the absorbent material makes it easier for the user to ensure that they are providing their blood sample onto the absorbent material  110 . The notch  112  may also be sized and shaped such that it exerts a pressure on a user&#39;s finger at positions either side of the lancing location. This arrangement may aid in expelling blood from the user&#39;s finger. The blood is absorbed into the absorbent material  110  by capillary action. The absorbent material  110  becomes saturated with the blood as indicated by the cross hatching. The blood reacts with an enzyme present in the absorbent material  110  or undergoes a reaction which is catalyzed by an enzyme present in the absorbent material  110 . This reaction produces an electrical charge which may pass as a current through the measurement electrodes  124  and via the conductive paths  126  to the controller  120 . The amount of analyte contained in the bodily fluid determines the magnitude of the electrical signal that reaches the controller  120 . 
     If activation electrodes ( 136 ,  138 ,  140 ) are present, then when an electrical current above a threshold level passes through the respective activation electrodes ( 136 ,  138 ,  140 ), the display  116  and controller  120  and are activated. The controller  120  begins measuring signals received from the measurement electrodes  124 . To achieve this, the controller  120  executes software and/or algorithms with which it has been programmed. The controller  120  is programmed to interpret signals received via the measurement electrodes  124  so as to make a measurement of a property of the bodily fluid. The controller  120  may produce a measurement based on a single signal sample received via the measurement electrodes  124 . Alternatively the controller  120  may record a series of signals received via the measurement electrodes  124 . The controller  120  may compute a measurement based on an analysis of the series of received signals. The property of the electrical signal measured at the controller  120  may be a current and/or voltage of the signal and may involve a time element, for instance by integrating an electrical parameter over time. 
     If the display  116  has been activated, but the measurement is not yet complete, then the display  116  may show a standby state, for example by illuminating the bottom segment of each digit of the display  116 , as shown in  FIG. 8C . 
     In  FIG. 8D , the controller  120  has finished making its measurement of the blood glucose level of the absorbed blood sample. The controller  120  controls the display  116  to display the result of the measurement to the user. The display  116  continues to display the result of the measurement for a predetermined amount of time, for example 60 seconds. 
       FIG. 9  is a flow chart illustrating the process of measuring a blood glucose level using the device  100 . The process begins at step  900 . At step  902  the user removes a removable seal  118  from the device  100 . This step of the process is shown in  FIG. 8A . At step  904  the user presents blood to the device  100  by pressing their finger against the notch  112 . This step of the process is shown in  FIG. 8C . 
     At step  906  the blood is absorbed into the device  100  by capillary action. The capillary action causes the blood to fill all of the absorbent material  110  such that it becomes saturated. At step  908  the blood reacts with a chemical substance embedded in the absorbent material  110 . Specifically, the glucose in the blood reacts with an enzyme, for example glucose oxidase or glucose dehydrogenase. The reaction produces electrical charge which flows as a current through the saturated absorbent material  110  to the measurement electrodes  126 . 
     At step  910 , the controller  120  begins measuring the blood glucose level in the absorbed blood sample. The controller  120  is configured to receive electrical signals produced by the reaction of the blood glucose with the enzyme in the absorbent material  110  via the measurement electrodes  124 . The controller  120  may receive multiple signals in order to make the measurement. The signals may for example be multiple consecutive values of a voltage or a current separated over time. The measurement may involve a time element, for instance integrating the values over time. 
     At step  912  the display  116  is activated. When initially activated the display  116  may be in a standby mode. This standby mode may consist of illuminating at least some of the pixels of the display. This has the added advantage of signalling to a user of the device  100  that the blood sample they have provided is of a sufficient volume and quality and that a measurement is underway. This step of the process is shown in  FIG. 8C . Steps  910  and  912  may occur substantially simultaneously. 
     If the device  100  includes activation electrodes ( 136 ,  138 ,  140 ), then steps  910  and  912  may only begin once it is determined that an electrical signal received at the controller  120  via the activation electrodes is above a threshold level. This determination may be performed in hardware at the controller  120  such that the controller  120  may remain inactive during the determination. The device  100  may be configured such that when the absorbent material  110  is saturated with a blood sample of a sufficient quality, the threshold signal value is exceeded. If, after a time, no measurement result is displayed or the display  116  remains in a standby mode, this may indicate to a user that not enough blood has been absorbed or that the reaction rate is too low. 
     If both controller activation electrodes  138  and display activation electrodes  140  are present then each of steps  910  and  912  may be preceded by separate signal threshold determination steps. 
     At step  914  it is determined if the measurement of the blood glucose level is complete. In some embodiments, the controller  120  may perform the measurement relatively quickly based on a single or a few signals from the measurement electrodes  124 . In some other embodiments the controller  120  may record signals over a short period of time in order to produce a more accurate measurement of the blood glucose level. If the measurement is not complete, the display continues to operate in standby mode at step  912 . Once it is determined that the measurement is complete the process continues at step  916 . 
     At step  916  the display  116  is caused by the controller  120  to display a result of the measurement. The display  116  may continue to display the result of the measurement for a predetermined period of time before deactivating the display  116 . This step of the process is shown in  FIG. 8D . The process ends at step  918 . After the user has used all of the collection and testing segments  108  on the device  100 , the device  100  may be discarded. 
     It will be appreciated that the above described embodiments are purely illustrative and are not limiting on the scope of the invention. Other variations and modifications will be apparent to persons skilled in the art upon reading the present application. For example, although the invention has been described with respect to a blood glucose meter, the teachings herein are applicable to the measurement of parameters of other bodily fluids, such as plasma, tears or saliva. Moreover, the disclosure of the present application should be understood to include any novel features or any novel combination of features either explicitly or implicitly disclosed herein or any generalization thereof and during the prosecution of the present application or of any application derived therefrom, new claims may be formulated to cover any such features and/or combination of such features.