Abstract:
A method and program prevents a user from bypassing a limit placed on a specified operating life of a sensor by disconnecting and reconnecting the sensor. The present invention checks a characteristic of the sensor to see if the sensor is used prior to the connection of the sensor, and rejects the sensor if the sensor is determined to have been used before. The process of checking the characteristic of the sensor involves performing an Electrochemical Impedance Spectroscopy (EIS) procedure and calculating an impedance value. The impedance value can be compared to various threshold values for a variety of purposes including the determination of age, condition, hydration, and stabilization of the sensor.

Description:
RELATED APPLICATIONS  
       [0001]     This application is a continuation-in-part of both U.S. patent application Ser. No. 11/322,977, entitled “Method of and System for Stabilization of Sensors” filed on Dec. 30, 2005, and U.S. patent application Ser. No. 11/323,242, entitled “Methods and Systems for Detecting the Hydration of Sensors” filed on Dec. 30, 2005, both of which are herein incorporated by reference. 
     
    
     FIELD OF THE INVENTION  
       [0002]     Embodiments of this invention relate generally to methods and systems of using continuous glucose monitors to measure glucose values. More particularly, embodiments of this invention relate to systems and methods for determining whether the sensor is ready for use, whether the displayed reading is reliable, and whether the sensor has been used past its specified life time.  
       BACKGROUND OF THE INVENTION  
       [0003]     Subjects and medical personnel wish to monitor readings of physiological conditions within the subject&#39;s body. Illustratively, subjects wish to monitor blood glucose levels in a subject&#39;s body on a continuing basis. Presently, a patient can measure his/her blood glucose (BG) using a BG measurement device (i.e. glucose meter), such as a test strip meter, a continuous glucose measurement system (or a continuous glucose monitor), or a hospital hemacue. BG measurement devices use various methods to measure the BG level of a patient, such as a sample of the patient&#39;s blood, a sensor in contact with a bodily fluid, an optical sensor, an enzymatic sensor, or a fluorescent sensor. When the BG measurement device has generated a BG measurement, the measurement is displayed on the BG measurement device.  
         [0004]     Current continuous glucose measurement systems include subcutaneous (or short-term) sensors and implantable (or long-term) sensors. For each of the short-term sensors and the long-term sensors, a patient has to wait a certain amount of time in order for the continuous glucose sensor to stabilize and to provide accurate readings. In many continuous glucose sensors, the subject must wait three hours for the continuous glucose sensor to stabilize before any glucose measurements are utilized. This is an inconvenience for the patient and in some cases may cause the patient not to utilize a continuous glucose measurement system.  
         [0005]     Further, when a glucose sensor is first inserted into a patient&#39;s skin or subcutaneous layer, the glucose sensor does not operate in a stable state. The electrical readings from the sensor, which represent the glucose level of the patient, vary over a wide range of readings. In the past, sensor stabilization used to take several hours. A technique for sensor stabilization is detailed in U.S. Pat. No. 6,809,653, (“the &#39;653 patent”), application Ser. No. 09/465,715, filed Dec. 19, 1999, issued Oct. 26, 2004, to Mann et al., assigned to Medtronic Minimed, Inc., which is incorporated herein by reference. In the &#39;653 patent, the initialization process for sensor stabilization may be reduced to approximately one hour. A high voltage (e.g., 1.0-1.2 volts) may be applied for 1 to 2 minutes to allow the sensor to stabilize and then a low voltage (e.g., between 0.5-0.6 volts) may be applied for the remainder of the initialization process (e.g., 58 minutes or so). Thus, even with this procedure, sensor stabilization still requires a large amount of time.  
         [0006]     It is also desirable to allow electrodes of the sensor to be sufficiently “wetted” or hydrated before utilization of the electrodes of the sensor. If the electrodes of the sensor are not sufficiently hydrated, the result may be inaccurate readings of the patient&#39;s physiological condition. A user of current blood glucose sensors is instructed to not power up the sensors immediately. If they are utilized too early, current blood glucose sensors do not operate in an optimal or efficient fashion. No automatic procedure or measuring technique is utilized to determine when to power on the sensor. This manual process is inconvenient and places too much responsibility on the patient, who may forget to apply or turn on the power source.  
         [0007]     Besides the stabilization and wetting problems during the initial sensor life, there can be additional issues at the end of the specified sensor&#39;s life. For instance, all sensors are pre-set with a specified operating life. For example, in current short-term sensors on the market today, the sensors are typically good for 3 to 5 days. Although sensors may continue to function and deliver a signal after the pre-set operating life of the sensor, the sensor readings eventually become less consistent and thus less reliable after the pre-set operating life of the sensor has passed. The exact sensor life of each individual sensor varies from sensor to sensor, but all sensors have been approved for at least the pre-set operating life of the sensor. Therefore, manufacturers have required the users of the sensors replace the sensors after the pre-set operating life has passed. Although the continuous glucose measurement system can monitor the length of time since the sensor was inserted and indicate the end of the operating life of a sensor to warn the user to replace the sensor, it does not have enough safeguards to prevent the sensor from being used beyond the operating life. Even though the characteristic monitors can simply stop functioning once the operating life of the sensor is reached and a new sensor is replaced into the system, a patient may bypass these safeguards by simply disconnecting and re-connecting the same sensor. Thus, there is a loophole in the system where a user can keep the sensors active longer than recommended and thus compromising the accuracy of the blood glucose values returned by the glucose monitor. This problem is similar to the disposable contact lens wearer keeping their contacts beyond the recommended amount of time. In the present art, there is no mechanism to determine whether the patient has replaced the sensor or is using the same sensor.  
       SUMMARY OF THE INVENTION  
       [0008]     According to an embodiment of the invention, a method and program of detecting whether a sensor is aged beyond a specified sensor life is described. In the preferred embodiments, the present invention performs an EIS procedure between at least two electrodes of the sensor, calculates an impedance value between the electrodes, and compares the impedance value against a threshold to determine if the sensor has aged beyond the specified sensor life. In specific embodiments, the EIS procedure applies a combination of a DC bias and an AC voltage of varying frequencies wherein the impedance detected by performing the EIS procedure is mapped on a Nyquist plot, and an inflection point in the Nyquist plot approximates a sum of polarization resistance and solution resistance which can then be used to compare against the threshold.  
         [0009]     In further embodiments of the present invention, the EIS procedure is used for additional purposes. An initial EIS procedure can be performed during the sensor initialization stage to determine whether additional initialization of the sensor is required or during the sensor hydration stage to determine whether hydration assist is required. In addition, the EIS procedure can be performed regularly at fixed intervals during the specified sensor life to detect when a sensor is failing.  
     
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0010]     A detailed description of embodiments of the invention will be made with reference to the accompanying drawings, wherein like numerals designate corresponding parts in the figures.  
         [0011]      FIG. 1  is a perspective view of a subcutaneous sensor insertion set and block diagram of a sensor electronics device according to an embodiment of the invention;  
         [0012]      FIG. 2 ( a ) illustrates a substrate having two sides, a first side which contains an electrode configuration and a second side which contains electronic circuitry;  
         [0013]      FIG. 2 ( b ) illustrates a general block diagram of an electronic circuit for sensing an output of a sensor;  
         [0014]      FIG. 3  illustrates a block diagram of a sensor electronics device and a sensor including a plurality of electrodes according to an embodiment of the invention;  
         [0015]      FIG. 4  illustrates an alternative embodiment of the invention including a sensor and a sensor electronics device according to an embodiment of the present invention;  
         [0016]      FIG. 5  illustrates an electronic block diagram of the sensor electrodes and a voltage being applied to the sensor electrodes according to an embodiment of the present invention;  
         [0017]      FIG. 6 ( a ) illustrates a method of applying pulses during stabilization timeframe in order to reduce the stabilization timeframe according to an embodiment of the present invention;  
         [0018]      FIG. 6 ( b ) illustrates a method of stabilizing sensors according to an embodiment of the present invention;  
         [0019]      FIG. 6 ( c ) illustrates utilization of feedback in stabilizing the sensors according to an embodiment of the present invention;  
         [0020]      FIG. 7  illustrates an effect of stabilizing a sensor according to an embodiment of the invention;  
         [0021]      FIG. 8  illustrates a block diagram of a sensor electronics device and a sensor including a voltage generation device according to an embodiment of the invention;  
         [0022]      FIG. 8 ( b ) illustrates a voltage generation device to implement this embodiment of the invention;  
         [0023]      FIG. 8 ( c ) illustrates a voltage generation device to generate two voltage values according in a sensor electronics device according to implement this embodiment of the invention;  
         [0024]      FIG. 9  illustrates a sensor electronics device including a microcontroller for generating voltage pulses according to an embodiment of the present invention;  
         [0025]      FIG. 9 ( b ) illustrates a sensor electronics device including an analyzation module according to an embodiment of the present invention;  
         [0026]      FIG. 10  illustrates a block diagram of a sensor system including hydration electronics according to an embodiment of the present invention;  
         [0027]      FIG. 11  illustrates an embodiment of the invention including a mechanical switch to assist in determining a hydration time;  
         [0028]      FIG. 12  illustrates an electrical detection of detecting hydration according to an embodiment of the invention;  
         [0029]      FIG. 13 ( a ) illustrates a method of hydrating a sensor according to an embodiment of the present invention;  
         [0030]      FIG. 13 ( b ) illustrates an additional method for verifying hydration of a sensor according to an embodiment of the present invention;  
         [0031]     FIGS.  14 ( a ) and ( b ) illustrate methods of combining hydrating of a sensor with stabilizing a sensor according to an embodiment of the present invention; and  
         [0032]      FIG. 14 ( c ) illustrates an alternative embodiment of the invention where the stabilization method and hydration method are combined.  
         [0033]      FIG. 15  illustrates some examples of applied voltage between working and reference electrodes using the EIS technique in accordance with embodiments of the present invention.  
         [0034]      FIG. 16  illustrates an example of a Nyquist plot where the selected frequencies, from 0.1 Hz to 1000 Mhz AC voltages plus a DC voltage (DC bias) are applied to the working electrode in accordance with embodiments of the present invention.  
         [0035]      FIG. 17  illustrates the changing Nyquist plot of sensor impedance as the sensor ages in accordance with embodiments of the present invention.  
         [0036]      FIG. 18  illustrates methods of applying EIS technique in stabilizing and detecting the age of the sensor in accordance with embodiments of the present invention.  
     
    
     DETAILED DESCRIPTION OF THE INVENTION  
       [0037]     In the following description, reference is made to the accompanying drawings which form a part hereof and which illustrate several embodiments of the present inventions. It is understood that other embodiments may be utilized and structural and operational changes may be made without departing from the scope of the present inventions.  
         [0038]     The present invention described below with reference to flowchart illustrations of methods, apparatus, and computer program products. It will be understood that each block of the flowchart illustrations, and combinations of blocks in the flowchart illustrations, can be implemented by computer program instructions (as can any menu screens described in the Figures). These computer program instructions may be loaded onto a computer or other programmable data processing apparatus (such as a controller, microcontroller, or processor in a sensor electronics device to produce a machine, such that the instructions which execute on the computer or other programmable data processing apparatus create instructions for implementing the functions specified in the flowchart block or blocks. These computer program instructions may also be stored in a computer-readable memory that can direct a computer or other programmable data processing apparatus to function in a particular manner, such that the instructions stored in the computer-readable memory produce an article of manufacture including instructions which implement the function specified in the flowchart block or blocks. The computer program instructions may also be loaded onto a computer or other programmable data processing apparatus to cause a series of operational steps to be performed on the computer or other programmable apparatus to produce a computer implemented process such that the instructions which execute on the computer or other programmable apparatus provide steps for implementing the functions specified in the flowchart block or blocks, and/or menus presented herein.  
         [0039]      FIG. 1  is a perspective view of a subcutaneous sensor insertion set and a block diagram of a sensor electronics device according to an embodiment of the invention. As illustrated in  FIG. 1 , a subcutaneous sensor set  10  is provided for subcutaneous placement of an active portion of a flexible sensor  12  (see  FIG. 2 ), or the like, at a selected site in the body of a user. The subcutaneous or percutaneous portion of the sensor set  10  includes a hollow, slotted insertion needle  14 , and a cannula  16 . The needle  14  is used to facilitate quick and easy subcutaneous placement of the cannula  16  at the subcutaneous insertion site. Inside the cannula  16  is a sensing portion  18  of the sensor  12  to expose one or more sensor electrodes  20  to the user&#39;s bodily fluids through a window  22  formed in the cannula  16 . In an embodiment of the invention, the one or more sensor electrodes  20  may include a counter electrode, a working electrode, and a reference electrode. After insertion, the insertion needle  14  is withdrawn to leave the cannula  16  with the sensing portion  18  and the sensor electrodes  20  in place at the selected insertion site.  
         [0040]     In particular embodiments, the subcutaneous sensor set  10  facilitates accurate placement of a flexible thin film electrochemical sensor  12  of the type used for monitoring specific blood parameters representative of a user&#39;s condition. The sensor  12  monitors glucose levels in the body, and may be used in conjunction with automated or semi-automated medication infusion pumps of the external or implantable type as described in U.S. Pat. Nos. 4,562,751; 4,678,408; 4,685,903 or 4,573,994, to control delivery of insulin to a diabetic patient.  
         [0041]     Particular embodiments of the flexible electrochemical sensor  12  are constructed in accordance with thin film mask techniques to include elongated thin film conductors embedded or encased between layers of a selected insulative material such as polyimide film or sheet, and membranes. The sensor electrodes  20  at a tip end of the sensing portion  18  are exposed through one of the insulative layers for direct contact with patient blood or other body fluids, when the sensing portion  18  (or active portion) of the sensor  12  is subcutaneously placed at an insertion site. The sensing portion  18  is joined to a connection portion  24  that terminates in conductive contact pads, or the like, which are also exposed through one of the insulative layers. In alternative embodiments, other types of implantable sensors, such as chemical based, optical based, or the like, may be used.  
         [0042]     As is known in the art, the connection portion  24  and the contact pads are generally adapted for a direct wired electrical connection to a suitable monitor or sensor electronics device  100  for monitoring a user&#39;s condition in response to signals derived from the sensor electrodes  20 . Further description of flexible thin film sensors of this general type are be found in U.S. Pat. No. 5,391,250, entitled METHOD OF FABRICATING THIN FILM SENSORS, which is herein incorporated by reference. The connection portion  24  may be conveniently connected electrically to the monitor or sensor electronics device  100  or by a connector block  28  (or the like) as shown and described in U.S. Pat. No. 5,482,473, entitled FLEX CIRCUIT CONNECTOR, which is also herein incorporated by reference. Thus, in accordance with embodiments of the present invention, subcutaneous sensor sets  10  may be configured or formed to work with either a wired or a wireless characteristic monitor system.  
         [0043]     The sensor electrodes  10  may be used in a variety of sensing applications and may be configured in a variety of ways. For example, the sensor electrodes  10  may be used in physiological parameter sensing applications in which some type of biomolecule is used as a catalytic agent. For example, the sensor electrodes  10  may be used in a glucose and oxygen sensor having a glucose oxidase enzyme catalyzing a reaction with the sensor electrodes  20 . The sensor electrodes  10 , along with a biomolecule or some other catalytic agent, may be placed in a human body in a vascular or non-vascular environment. For example, the sensor electrodes  20  and biomolecule may be placed in a vein and be subjected to a blood stream, or may be placed in a subcutaneous or peritoneal region of the human body.  
         [0044]     The monitor  100  may also be referred to as a sensor electronics device  100 . The monitor  100  may include a power source  110 , a sensor interface  122 , processing electronics  124 , and data formatting electronics  128 . The monitor  100  may be coupled to the sensor set  10  by a cable  102  through a connector that is electrically coupled to the connector block  28  of the connection portion  24 . In an alternative embodiment, the cable may be omitted. In this embodiment of the invention, the monitor  100  may include an appropriate connector for direct connection to the connection portion  104  of the sensor set  10 . The sensor set  10  may be modified to have the connector portion  104  positioned at a different location, e.g., on top of the sensor set to facilitate placement of the monitor  100  over the sensor set.  
         [0045]     In embodiments of the invention, the sensor interface  122 , the processing electronics  124 , and the data formatting electronics  128  are formed as separate semiconductor chips, however alternative embodiments may combine the various semiconductor chips into a single or multiple customized semiconductor chips. The sensor interface  122  connects with the cable  102  that is connected with the sensor set  10 .  
         [0046]     The power source  110  may be a battery. The battery can include three series silver oxide  357  battery cells. In alternative embodiments, different battery chemistries may be utilized, such as lithium based chemistries, alkaline batteries, nickel metalhydride, or the like, and different number of batteries may used. The monitor  100  provides power, through the power source  110 , provides power, through the cable  102  and cable connector  104  to the sensor set. In an embodiment of the invention, the power is a voltage provided to the sensor set  10 . In an embodiment of the invention, the power is a current provided to the sensor set  10 . In an embodiment of the invention, the power is a voltage provided at a specific voltage to the sensor set  10 .  
         [0047]     FIGS.  2 ( a ) and  2 ( b ) illustrates an implantable sensor and electronics for driving the implantable sensor according to an embodiment of the present invention.  FIG. 2 ( a ) shows a substrate  220  having two sides, a first side  222  of which contains an electrode configuration and a second side  224  of which contains electronic circuitry. As may be seen in  FIG. 2 ( a ), a first side  222  of the substrate comprises two counter electrode-working electrode pairs  240 ,  242 ,  244 ,  246  on opposite sides of a reference electrode  248 . A second side  224  of the substrate comprises electronic circuitry. As shown, the electronic circuitry may be enclosed in a hermetically sealed casing  226 , providing a protective housing for the electronic circuitry. This allows the sensor substrate  220  to be inserted into a vascular environment or other environment which may subject the electronic circuitry to fluids. By sealing the electronic circuitry in a hermetically sealed casing  226 , the electronic circuitry may operate without risk of short circuiting by the surrounding fluids. Also shown in  FIG. 2 ( a ) are pads  228  to which the input and output lines of the electronic circuitry may be connected. The electronic circuitry itself may be fabricated in a variety of ways. According to an embodiment of the present invention, the electronic circuitry may be fabricated as an integrated circuit using techniques common in the industry.  
         [0048]      FIG. 2 ( b ) illustrates a general block diagram of an electronic circuit for sensing an output of a sensor according to an embodiment of the present invention. At least one pair of sensor electrodes  310  may interface to a data converter  312 , the output of which may interface to a counter  314 . The counter  314  may be controlled by control logic  316 . The output of the counter  314  may connect to a line interface  318 . The line interface  318  may be connected to input and output lines  320  and may also connect to the control logic  316 . The input and output lines  320  may also be connected to a power rectifier  322 .  
         [0049]     The sensor electrodes  310  may be used in a variety of sensing applications and may be configured in a variety of ways. For example, the sensor electrodes  310  may be used in physiological parameter sensing applications in which some type of biomolecule is used as a catalytic agent. For example, the sensor electrodes  310  may be used in a glucose and oxygen sensor having a glucose oxidase enzyme catalyzing a reaction with the sensor electrodes  310 . The sensor electrodes  310 , along with a biomolecule or some other catalytic agent, may be placed in a human body in a vascular or non-vascular environment. For example, the sensor electrodes  310  and biomolecule may be placed in a vein and be subjected to a blood stream.  
         [0050]      FIG. 3  illustrates a block diagram of a sensor electronics device and a sensor including a plurality of electrodes according to an embodiment of the invention. The sensor set or system  350  includes a sensor  355  and a sensor electronics device  360 . The sensor  355  includes a counter electrode  365 , a reference electrode  370 , and a working electrode  375 . The sensor electronics device  360  includes a power supply  380 , a regulator  385 , a signal processor  390 , a measurement processor  395 , and a display/transmission module  397 . The power supply  380  provides power (in the form of either a voltage, a current, or a voltage including a current) to the regulator  385 . The regulator  385  transmits a regulated voltage to the sensor  355 . In an embodiment of the invention, the regulator  385  transmits a voltage to the counter electrode  365  of the sensor  355 .  
         [0051]     The sensor  355  creates a sensor signal indicative of a concentration of a physiological characteristic being measured. For example, the sensor signal may be indicative of a blood glucose reading. In an embodiment of the invention utilizing subcutaneous sensors, the sensor signal may represent a level of hydrogen peroxide in a subject. In an embodiment of the invention where blood or cranial sensors are utilized, the amount of oxygen is being measured by the sensor and is represented by the sensor signal. In an embodiment of the invention utilizing implantable or long-term sensors, the sensor signal may represent a level of oxygen in the subject. The sensor signal is measured at the working electrode  375 . In an embodiment of the invention, the sensor signal may be a current measured at the working electrode. In an embodiment of the invention, the sensor signal may be a voltage measured at the working electrode.  
         [0052]     The signal processor  390  receives the sensor signal (e.g., a measured current or voltage) after the sensor signal is measured at the sensor  355  (e.g., the working electrode). The signal processor  390  processes the sensor signal and generates a processed sensor signal. The measurement processor  395  receives the processed sensor signal and calibrates the processed sensor signal utilizing reference values. In an embodiment of the invention, the reference values are stored in a reference memory and provided to the measurement processor  395 . The measurement processor  395  generates sensor measurements. The sensor measurements may be stored in a measurement memory (not pictured). The sensor measurements may be sent to a display/transmission device to be either displayed on a display in a housing with the sensor electronics or to be transmitted to an external device.  
         [0053]     The sensor electronics device  350  may be a monitor which includes a display to display physiological characteristics readings. The sensor electronics device  350  may also be installed in a desktop computer, a pager, a television including communications capabilities, a laptop computer, a server, a network computer, a personal digital assistant (PDA), a portable telephone including computer functions, an infusion pump including a display, a glucose sensor including a display, and or a combination infusion pump/glucose sensor. The sensor electronics device  350 may be housed in a blackberry, a network device, a home network device, or an appliance connected to a home network.  
         [0054]      FIG. 4  illustrates an alternative embodiment of the invention including a sensor and a sensor electronics device according to an embodiment of the present invention. The sensor set or sensor system  400  includes a sensor electronics device  360  and a sensor  355 . The sensor includes a counter electrode  365 , a reference electrode  370 , and a working electrode  375 . The sensor electronics device  360  includes a microcontroller  410  and a digital-to-analog converter (DAC)  420 . The sensor electronics device  360  may also include a current-to-frequency converter (I/F converter)  430 .  
         [0055]     The microcontroller  410  includes software program code, which when executed, or programmable logic which, causes the microcontroller  410  to transmit a signal to the DAC  420 , where the signal is representative of a voltage level or value that is to be applied to the sensor  355 . The DAC  420  receives the signal and generates the voltage value at the level instructed by the microcontroller  410 . In embodiments of the invention, the microcontroller  410  may change the representation of the voltage level in the signal frequently or infrequently. Illustratively, the signal from the microcontroller  410  may instruct the DAC  420  to apply a first voltage value for one second and a second voltage value for two seconds.  
         [0056]     The sensor  355  may receive the voltage level or value. In an embodiment of the invention, the counter electrode  365  may receive the output of an operational amplifier which has as inputs the reference voltage and the voltage value from the DAC  420 . The application of the voltage level causes the sensor  355  to create a sensor signal indicative of a concentration of a physiological characteristic being measured. In an embodiment of the invention, the microcontroller  410  may measure the sensor signal (e.g., a current value) from the working electrode. Illustratively, a sensor signal measurement circuit  431  may measure the sensor signal. In an embodiment of the invention, the sensor signal measurement circuit  431  may include a resistor and the current may be passed through the resistor to measure the value of the sensor signal. In an embodiment of the invention, the sensor signal may be a current level signal and the sensor signal measurement circuit  431  may be a current-to-frequency (I/F) converter  430 . The current-to-frequency converter  430  may measure the sensor signal in terms of a current reading, convert it to a frequency-based sensor signal, and transmit the frequency-based sensor signal to the microcontroller  410 . In embodiments of the invention, the microcontroller  410  may be able to receive frequency-based sensor signals easier than non-frequency-based sensor signals. The microcontroller  410  receives the sensor signal, whether frequency-based or non frequency-based, and determines a value for the physiological characteristic of a subject, such as a blood glucose level. The microcontroller  410  may include program code, which when executed or run, is able to receive the sensor signal and convert the sensor signal to a physiological characteristic value. In an embodiment of the invention, the microcontroller  410  may convert the sensor signal to a blood glucose level. In an embodiment of the invention, the microcontroller  410  may utilize measurements stored within an internal memory in order to determine the blood glucose level of the subject. In an embodiment of the invention, the microcontroller  410  may utilize measurements stored within a memory external to the microcontroller  410  to assist in determining the blood glucose level of the subject.  
         [0057]     After the physiological characteristic value is determined by the microcontroller  410 , the microcontroller  410  may store measurements of the physiological characteristic values for a number of time periods. For example, a blood glucose value may be sent to the microcontroller  410  from the sensor every second or five seconds, and the microcontroller may save sensor measurements for five minutes or ten minutes of BG readings. The microcontroller  410  may transfer the measurements of the physiological characteristic values to a display on the sensor electronics device  450 . For example, the sensor electronics device  450  may be a monitor which includes a display that provides a blood glucose reading for a subject. In an embodiment of the invention, the microcontroller  410  may transfer the measurements of the physiological characteristic values to an output interface of the microcontroller  410 . The output interface of the microcontroller  410  may transfer the measurements of the physiological characteristic values, e.g., blood glucose values, to an external device, e.g., such as an infusion pump, a combined infusion pump/glucose meter, a computer, a personal digital assistant, a pager, a network appliance, a server, a cellular phone, or any computing device.  
         [0058]      FIG. 5  illustrates an electronic block diagram of the sensor electrodes and a voltage being applied to the sensor electrodes according to an embodiment of the present invention. In the embodiment of the invention illustrated in  FIG. 5 , an op amp  530  or other servo controlled device may connect to sensor electrodes  510  through a circuit/electrode interface  538 . The op amp  530 , utilizing feedback through the sensor electrodes, attempts to maintain a prescribed voltage (what the DAC may desire the applied voltage to be) between a reference electrode  532  and a working electrode  534  by adjusting the voltage at a counter electrode  536 . Current may then flow from a counter electrode  536  to a working electrode  534 . Such current may be measured to ascertain the electrochemical reaction between the sensor electrodes  510  and the biomolecule of a sensor that has been placed in the vicinity of the sensor electrodes  510  and used as a catalyzing agent. The circuitry disclosed in  FIG. 5  may be utilized in a long-term or implantable sensor or may be utilized in a short-term or subcutaneous sensor.  
         [0059]     In a long-term sensor embodiment, where a glucose oxidase enzyme is used as a catalytic agent in a sensor, current may flow from the counter electrode  536  to a working electrode  534  only if there is oxygen in the vicinity of the enzyme and the sensor electrodes  10 . Illustratively, if the voltage set at the reference electrode  532  is maintained at about 0.5 volts, the amount of current flowing from a counter electrode  536  to a working electrode  534  has a fairly linear relationship with unity slope to the amount of oxygen present in the area surrounding the enzyme and the electrodes. Thus, increased accuracy in determining an amount of oxygen in the blood may be achieved by maintaining the reference electrode  532  at about  0 . 5  volts and utilizing this region of the current-voltage curve for varying levels of blood oxygen. Different embodiments of the present invention may utilize different sensors having biomolecules other than a glucose oxidase enzyme and may, therefore, have voltages other than 0.5 volts set at the reference electrode.  
         [0060]     As discussed above, during initial implantation or insertion of the sensor  510 , a sensor  510  may provide inaccurate readings due to the adjusting of the subject to the sensor and also electrochemical byproducts caused by the catalyst utilized in the sensor. A stabilization period is needed for many sensors in order for the sensor  510  to provide accurate readings of the physiological parameter of the subject. During the stabilization period, the sensor  510  does not provide accurate blood glucose measurements. Users and manufacturers of the sensors may desire to improve the stabilization timeframe for the sensor so that the sensors can be utilized quickly after insertion into the subject&#39;s body or a subcutaneous layer of the subject.  
         [0061]     In previous sensor electrode systems, the stabilization period or timeframe was one hour to three hours. In order to decrease the stabilization period or timeframe and increase the timeliness of accuracy of the sensor, a sensor (or electrodes of a sensor) may be subjected to a number of pulses rather than the application of one pulse followed by the application of another voltage.  FIG. 6 ( a ) illustrates a method of applying pulses during stabilization timeframe in order to reduce the stabilization timeframe according to an embodiment of the present invention. In this embodiment of the invention, a voltage application device applies  600  a first voltage to an electrode for a first time or time period. In an embodiment of the invention, the first voltage may be a DC constant voltage. This results in an anodic current being generated. In an alternative embodiment of the invention, a digital-to-analog converter or another voltage source may supply the voltage to the electrode for a first time period. The anodic current means that electrons are being driven away from electrode to which the voltage is applied. In an embodiment of the invention, an application device may apply a current instead of a voltage. In an embodiment of the invention where a voltage is applied to a sensor, after the application of the first voltage to the electrode, the voltage regulator may not apply  605  a voltage for a second time, timeframe, or time period. In other words, the voltage application device waits until a second time period elapses. The non-application of voltage results in a cathodic current, which results in the gaining of electrons by the electrode to which the voltage is not applied. The application of the first voltage to the electrode for a first time period followed by the non-application of voltage for a second time period is repeated  610  for a number of iterations. This may be referred to as an anodic and cathodic cycle. In an embodiment of the invention, the number of total iterations of the stabilization method is three, i.e., three applications of the voltage for the first time period, each followed by no application of the voltage three times for the second time period. In an embodiment of the invention, the first voltage may be 1.07 volts. In an embodiment of the invention, the first voltage may be 0.535 volts. In an embodiment of the invention, the first voltage may be approximately 0.7 volts.  
         [0062]     The result of the repeated application of the voltage and the non-application of the voltage results in the sensor (and thus the electrodes) being subjected to an anodic—cathodic cycle. The anodic—cathodic cycle results in the reduction of electrochemical byproducts which are generated by a patient&#39;s body reacting to the insertion of the sensor or the implanting of the sensor. In an embodiment of the invention, the electrochemical byproducts cause generation of a background current, which results in inaccurate measurements of the physiological parameter of the subject. In an embodiment of the invention, the electrochemical byproduct may be eliminated. Under other operating conditions, the electrochemical byproducts may be reduced or significantly reduced. A successful stabilization method results in the anodic-cathodic cycle reaching equilibrium, electrochemical byproducts being significantly reduced, and background current being minimized.  
         [0063]     In an embodiment of the invention, the first voltage being applied to the electrode of the sensor may be a positive voltage. In an embodiment of the invention, the first voltage being applied may be a negative voltage. In an embodiment of the invention, the first voltage may be applied to a working electrode. In an embodiment of the invention, the first voltage may be applied to the counter electrode or the reference electrode.  
         [0064]     In embodiments of the invention, the duration of the voltage pulse and the no application of voltage may be equal, e.g., such as three minutes each. In embodiments of the invention, the duration of the voltage application or voltage pulse may be different values, e.g., the first time and the second time may be different. In an embodiment of the invention, the first time period may be five minutes and the waiting period may be two minutes. In an embodiment of the invention, the first time period may be two minutes and the waiting period (or second timeframe) may be five minutes. In other words, the duration for the application of the first voltage may be two minutes and there may be no voltage applied for five minutes. This timeframe is only meant to be illustrative and should not be limiting. For example, a first timeframe may be two, three, five or ten minutes and the second timeframe may be five minutes, ten minutes, twenty minutes, or the like. The timeframes (e.g., the first time and the second time) may depend on unique characteristics of different electrodes, the sensors, and/or the patient&#39;s physiological characteristics.  
         [0065]     In embodiments of the invention, more or less than three pulses may be utilized to stabilize the glucose sensor. In other words, the number of iterations may be greater than 3 or less than three. For example, four voltage pulses (e.g., a high voltage followed by no voltage) may be applied to one of the electrodes or six voltage pulses may be applied to one of the electrodes.  
         [0066]     Illustratively, three consecutive pulses of 1.07 volts (followed by three pulses of no volts) may be sufficient for a sensor implanted subcutaneously. In an embodiment of the invention, three consecutive voltage pulses of 0.7 volts may be utilized. The three consecutive pulses may have a higher or lower voltage value, either negative or positive, for a sensor implanted in blood or cranial fluid, e.g., the long-term or permanent sensors. In addition, more than three pulses (e.g., five, eight, twelve) may be utilized to create the anodic-cathodic cycling between anodic and cathodic currents in any of the subcutaneous, blood, or cranial fluid sensors.  
         [0067]      FIG. 6 ( b ) illustrates a method of stabilizing sensors according to an embodiment of the present invention. In the embodiment of the invention illustrated in  FIG. 6 ( b ), a voltage application device may apply  630  a first voltage to the sensor for a first time to initiate an anodic cycle at an electrode of the sensor. The voltage application device may be a DC power supply, a digital-to-analog converter, or a voltage regulator. After the first time period has elapsed, a second voltage is applied  635  to the sensor for a second time to initiate an cathodic cycle at an electrode of the sensor. Illustratively, rather than no voltage being applied, as is illustrated in the method of  FIG. 6 ( a ), a different voltage (from the first voltage) is applied to the sensor during the second timeframe. In an embodiment of the invention, the application of the first voltage for the first time and the application of the second voltage for the second time are applied  640  for a number of iterations. In an embodiment of the invention, the application of the first voltage for the first time and the application of the second voltage for the second time may each be applied for a stabilization timeframe, e.g., 10 minutes, 15 minutes, or 20 minutes rather than for a number of iterations. This stabilization timeframe is the entire timeframe for the stabilization sequence, e.g., until the sensor (and electrodes) are stabilized. The benefit of this stabilization methodology is a faster run-in of the sensors, less background current (in other words a suppression of some the background current), and a better glucose response.  
         [0068]     In an embodiment of the invention, the first voltage may be 0.535 volts applied for five minutes, the second voltage may be 1.070 volts applied for two minutes, the first voltage of 0.535 volts may be applied for five minutes, the second voltage of 1.070 volts may be applied for two minutes, the first voltage of 0.535 volts may be applied for five minutes, and the second voltage of 1.070 volts may be applied for two minutes. In other words, in this embodiment, there are three iterations of the voltage pulsing scheme. The pulsing methodology may be changed in that the second timeframe, e.g., the timeframe of the application of the second voltage may be lengthened from two minutes to five minutes, ten minutes, fifteen minutes, or twenty minutes. In addition, after the three iterations are applied in this embodiment of the invention, a nominal working voltage of 0.535 volts may be applied.  
         [0069]     The 1.08 and 0.535 volts are illustrative values. Other voltage values may be selected based on a variety of factors. These factors may include the type of enzyme utilized in the sensor, the membranes utilized in the sensor, the operating period of the sensor, the length of the pulse, and/or the magnitude of the pulse. Under certain operating conditions, the first voltage may be in a range of 1.00 to 1.09 volts and the second voltage may be in a range of 0.510 to 0.565 volts. In other operating embodiments, the ranges that bracket the first voltage and the second voltage may have a higher range, e.g., 0.3 volts, 0.6 volts, 0.9 volts, depending on the voltage sensitivity of the electrode in the sensor. Under other operating conditions, the voltage may be in a range of 0.8 volts to 1.34 volts and the other voltage may be in a range of 0.335 to 0.735. Under other operating conditions, the range of the higher voltage may be smaller than the range of the lower voltage. Illustratively, the higher voltage may be in a range of 0.9 to 1.09 volts and the lower voltage may be in a range of 0.235 to 0.835.  
         [0070]     In an embodiment of the invention, the first voltage and the second voltage may be positive voltages, or alternatively in other embodiments of the invention, negative voltages. In an embodiment of the invention, the first voltage may be positive and the second voltage may be negative, or alternatively, the first voltage may be negative and the second voltage may be positive. The first voltage may be different voltage levels for each of the iterations. In an embodiment of the invention, the first voltage may be a D.C. constant voltage. In other embodiments of the invention, the first voltage may be a ramp voltage, a sinusoid-shaped voltage, a stepped voltage, or other commonly utilized voltage waveforms. In an embodiment of the invention, the second voltage may be a D.C. constant voltage, a ramp voltage, a sinusoid-shaped voltage, a stepped voltage, or other commonly utilized voltage waveforms. In an embodiment of the invention, the first voltage or the second voltage may be an AC signal riding on a DC waveform. In an embodiment of the invention, the first voltage may be one type of voltage, e.g., a ramp voltage, and the second voltage may be a second type of voltage, e.g., a sinusoid-shaped voltage. In an embodiment of the invention, the first voltage (or the second voltage) may have different waveform shapes for each of the iterations. For example, if there are three cycles in a stabilization method, in a first cycle, the first voltage may be a ramp voltage, in the second cycle, the first voltage may be a constant voltage, and in the third cycle, the first voltage may be a sinusoidal voltage.  
         [0071]     In an embodiment of the invention, a duration of the first timeframe and a duration of the second timeframe may have the same value, or alternatively, the duration of the first timeframe and the second timeframe may have different values. For example, the duration of the first timeframe may be two minutes and the duration of the second timeframe may be five minutes and the number of iterations may be three. As discussed above, the stabilization method may include a number of iterations. In embodiments of the invention, during different iterations of the stabilization method, the duration of each of the first timeframes may change and the duration of each of the second timeframes may change. Illustratively, during the first iteration of the anodic-cathodic cycling, the first timeframe may be 2 minutes and the second timeframe may be 5 minutes. During the second iteration, the first timeframe may be 1 minute and the second timeframe may be 3 minutes. During the third iteration, the first timeframe may be 3 minutes and the second timeframe may be 10 minutes.  
         [0072]     In an embodiment of the invention, a first voltage of 0.535 volts is applied to an electrode in a sensor for two minutes to initiate an anodic cycle, then a second voltage of 1.07 volts is applied to the electrode to the sensor for five minutes to initiate a cathodic cycle. The first voltage of 0.535 volts is then applied again for two minutes to initiate the anodic cycle and a second voltage of 1.07 volts is applied to the sensor for five minutes. In a third iteration, 0.535 volts is applied for two minutes to initiate the anodic cycle and then 1.07 volts is applied for five minutes. The voltage applied to the sensor is then 0.535 during the actual working timeframe of the sensor, e.g., when the sensor provides readings of a physiological characteristic of a subject.  
         [0073]     Shorter duration voltage pulses may be utilized in the embodiment of FIGS.  6 ( a ) and  6 ( b ). The shorter duration voltage pulses may be utilized to apply the first voltage, the second voltage, or both. In an embodiment of the present invention, the magnitude of the shorter duration voltage pulse for the first voltage is −1.07 volts and the magnitude of the shorter duration voltage pulse for the second voltage is approximately half of the high magnitude, e.g.,−0.535 volts. Alternatively, the magnitude of the shorter duration pulse for the first voltage may be 0.535 volts and the magnitude of the shorter duration pulse for the second voltage is 1.07 volts.  
         [0074]     In embodiments of the invention utilizing short duration pulses, the voltage may not be applied continuously for the entire first time period. Instead, in the first time period, the voltage application device may transmit a number of short duration pulses during the first time period. In other words, a number of mini-width or short duration voltage pulses may be applied to the electrodes of the sensors over the first time period. Each mini-width or short duration pulse may a width of a number of milliseconds. Illustratively, this pulse width may be 30 milliseconds, 50 milliseconds, 70 milliseconds or 200 milliseconds. These values are meant to be illustrative and not limiting. In an embodiment of the invention, such as the embodiment illustrated in  FIG. 6 ( a ), these short duration pulses are applied to the sensor (electrode) for the first time period and then no voltage is applied for the second time period.  
         [0075]     In an embodiment of the invention, each short duration pulse may have the same time duration within the first time period. For example, each short duration voltage pulse may have a time width of 50 milliseconds and each pulse delay between the pulses may be 950 milliseconds. In this example, if two minutes is the measured time for the first timeframe, then 120 short duration voltage pulses may be applied to the sensor. In an embodiment of the invention, each of the short duration voltage pulses may have different time durations. In an embodiment of the invention, each of the short duration voltage pulses may have the same amplitude values. In an embodiment of the invention, each of the short duration voltage pulses may have different amplitude values. By utilizing short duration voltage pulses rather than a continuous application of voltage to the sensors, the same anodic and cathodic cycling may occur and the sensor (e.g., electrodes) is subjected to less total energy or charge over time. The use of short duration voltage pulses utilizes less power as compared to the application of continuous voltage to the electrodes because there is less energy applied to the sensors (and thus the electrodes).  
         [0076]      FIG. 6 ( c ) illustrates utilization of feedback in stabilizing the sensors according to an embodiment of the present invention. The sensor system may include a feedback mechanism to determine if additional pulses are needed to stabilize a sensor. In an embodiment of the invention, a sensor signal generated by an electrode (e.g., a working electrode) may be analyzed to determine is the sensor signal is stabilized. A first voltage is applied  630  to an electrode for a first timeframe to initiate an anodic cycle. A second voltage is applied  635  to an electrode for a second timeframe to initiate a cathodic cycle. In an embodiment of the invention, an analyzation module may analyze a sensor signal (e.g., the current emitted by the sensor signal, a resistance at a specific point in the sensor, an impedance at a specific node in the sensor) and determine if a threshold measurement has been reached  637  (e.g., determining if the sensor is providing accurate readings by comparing against the threshold measurement). If the sensor readings are determined to be accurate, which represents that the electrode (and thus the sensor) is stabilized  642  , no additional application of the first voltage and/or the second voltage may be generated. If the stability was not achieved, in an embodiment of the invention, then an additional anodic/cathodic cycle is initiated by the application  630  of a first voltage to an electrode for a first time period and then the application  635  of the second voltage to the electrode for a second time period.  
         [0077]     In embodiments of the invention, the analyzation module may be employed after an anodic/cathodic cycle of three applications of the first voltage and the second voltage to an electrode of the sensor. In an embodiment of the invention, an analyzation module may be employed after one application of the first voltage and the second voltage, as is illustrated in  FIG. 6 ( c ).  
         [0078]     In an embodiment of the invention, the analyzation module may be utilized to measure a voltage emitted after a current has been introduced across an electrode or across two electrodes. The analyzation module may monitor a voltage level at the electrode or at the receiving level. In an embodiment of the invention, if the voltage level is above a certain threshold, this may mean that the sensor is stabilized. In an embodiment of the invention, if the voltage level falls below a threshold level, this may indicate that the sensor is stabilized and ready to provide readings. In an embodiment of the invention, a current may be introduced to an electrode or across a couple of electrodes. The analyzation module may monitor a current level emitted from the electrode. In this embodiment of the invention, the analyzation module may be able to monitor the current if the current is different by an order of magnitude from the sensor signal current. If the current is above or below a current threshold, this may signify that the sensor is stabilized.  
         [0079]     In an embodiment of the invention, the analyzation module may measure an impedance between two electrodes of the sensor. The analyzation module may compare the impedance against a threshold or target impedance value and if the measured impedance is lower than the target or threshold impedance, the sensor (and hence the sensor signal) may be stabilized. In an embodiment of the invention, the analyzation module may measure a resistance between two electrodes of the sensor. In this embodiment of the invention, if the analyzation module compares the resistance against a threshold or target resistance value and the measured resistance value is less than the threshold or target resistance value, then the analyzation module may determine that the sensor is stabilized and that the sensor signal may be utilized.  
         [0080]      FIG. 7  illustrates an effect of stabilizing a sensor according to an embodiment of the invention. Line  705  represents blood glucose sensor readings for a glucose sensor where a previous single pulse stabilization method was utilized. Line  710  represents blood glucose readings for a glucose sensor where three voltage pulses are applied (e.g., 3 voltage pulses having a duration of 2 minutes each followed by 5 minutes of no voltage being applied). The x-axis  715  represents an amount of time. The dots  720   725   730  and  735  represent measured glucose readings, taken utilizing a fingerstick and then input into a glucose meter. As illustrated by the graph, the previous single pulse stabilization method took approximately 1 hour and 30 minutes in order to stabilize to the desired glucose reading, e.g., 100 units. In contrast, the three pulse stabilization method took only approximately 15 minutes to stabilize the glucose sensor and results in a drastically improved stabilization timeframe.  
         [0081]      FIG. 8  illustrates a block diagram of a sensor electronics device and a sensor including a voltage generation device according to an embodiment of the invention. The voltage generation or application device  810  includes electronics, logic, or circuits which generate voltage pulses. The sensor electronics device  360  may also include a input device  820  to receive reference values and other useful data. In an embodiment of the invention, the sensor electronics device may include a measurement memory  830  to store sensor measurements. In this embodiment of the invention, the power supply  380  may supply power to the sensor electronics device. The power supply  380  may supply power to a regulator  385 , which supplies a regulated voltage to the voltage generation or application device  810 . The connection terminals  811  represent that in the illustrated embodiment of the invention, the connection terminal couples or connects the sensor  355  to the sensor electronics device  360 .  
         [0082]     In an embodiment of the invention illustrated in  FIG. 8 , the voltage generation or application device  810  supplies a voltage, e.g., the first voltage or the second voltage, to an input terminal of an operational amplifier  840 . The voltage generation or application device  810  may also supply the voltage to a working electrode  375  of the sensor  355 . Another input terminal of the operational amplifier  840  is coupled to the reference electrode  370  of the sensor. The application of the voltage from the voltage generation or application device  810  to the operational amplifier  840  drives a voltage measured at the counter electrode  365  to be close to or equal the voltage applied at the working electrode  375 . In an embodiment of the invention, the voltage generation or application device  810  could be utilized to apply the desired voltage between the counter electrode and the working electrode. This may occur by the application of the fixed voltage to the counter electrode directly.  
         [0083]     In an embodiment of the invention as illustrated in FIGS.  6 ( a ) and  6 ( b ), the voltage generation device  810  generates a first voltage that is to be applied to the sensor during a first timeframe. The voltage generation device  810  transmits this first voltage to an op amp  840  which drives the voltage at a counter electrode  365  of the sensor  355  to the first voltage. In an embodiment of the invention, the voltage generation device  810  also could transmit the first voltage directly to the counter electrode  365  of the sensor  355 . In the embodiment of the invention illustrated in  FIG. 6 ( a ), the voltage generation device  810  then does not transmit the first voltage to the sensor  355  for a second timeframe. In other words, the voltage generation device  810  is turned off or switched off. The voltage generation device  810  may be programmed to continue cycling between applying the first voltage and not applying a voltage for either a number of iterations or for a stabilization timeframe, e.g., for twenty minutes.  FIG. 8 ( b ) illustrates a voltage generation device to implement this embodiment of the invention. The voltage regulator  385  transfers the regulated voltage to the voltage generation device  810 . A control circuit  860  controls the closing and opening of a switch  850 . If the switch  850  is closed, the voltage is applied. If the switch  850  is opened, the voltage is not applied. The timer  865  provides a signal to the control circuit  860  to instruct the control circuit  860  to turn on and off the switch  850 . The control circuit  860  includes logic which can instruct the circuit to open and close the switch  850  a number of times (to match the necessary iterations). In an embodiment of the invention, the timer  865  may also transmit a stabilization signal to identify that the stabilization sequence is completed, i.e. that a stabilization timeframe has elapsed.  
         [0084]     In an embodiment of the invention, the voltage generation device generates a first voltage for a first timeframe and generates a second voltage for a second timeframe.  FIG. 8 ( c ) illustrates a voltage generation device to generate two voltage values according in a sensor electronics device according to implement this embodiment of the invention. In this embodiment of the invention, a two position switch  870  is utilized. Illustratively, if the first switch position  871  is turned on or closed by the timer  865  instructing the control circuit  860 , then the voltage generation device  810  generates a first voltage for the first timeframe. After the first voltage has been applied for the first timeframe, timer sends a signal to the control circuit  860  indicating the first timeframe has elapsed and the control circuit  860  directs the switch  870  to move to the second position  872 . When the switch  870  is at the second position  872 , the regulated voltage is directed to a voltage step-down or buck converter  880  to reduce the regulated voltage to a lesser value. The lesser value is then delivered to the op amp  840  for the second timeframe. After the timer  865  has sent a signal to the control circuit  860  that the second timeframe has elapsed, then the control circuit  860  moves the switch  870  back to the first position. This continues until the desired number of iterations has been completed or the stabilization timeframe has elapsed. In an embodiment of the invention, after the sensor stabilization timeframe has elapsed, the sensor transmits a sensor signal  350  to the signal processor  390 .  
         [0085]      FIG. 8 ( d ) illustrates a voltage application device  810  utilized to perform more complex applications of voltage to the sensor. The voltage application device  810  may include a control device  860 , a switch  890 , a sinusoid generation device  891 , a ramp voltage generation device  892 , and a constant voltage generation device  893 . In other embodiments of the invention, the voltage application may generate an AC wave on top of a DC signal or other various voltage pulse waveforms. In the embodiment of the invention illustrated in  FIG. 8 ( d ), the control device  860  may cause the switch to move to one of the three voltage generation systems  891  (sinusoid),  892  (ramp),  893  (constant DC). This results in each of the voltage regulation systems generating the identified voltage waveform. Under certain operating conditions, e.g., where a sinusoidal pulse is to be applied for three pulses, the control device  860  may cause the switch  890  to connect the voltage from the voltage regulator  385  to the sinusoid voltage generator  891  in order for the voltage application device  810  to generate a sinusoidal voltage. Under other operating conditions, e.g., when a ramp voltage is applied to the sensor as the first voltage for a first pulse of three pulses, a sinusoid voltage is applied to the sensor as the first voltage for a second pulse of the three pulses, and a constant DC voltage is applied to the sensor as the first voltage for a third pulse of the three pulses, the control device  860  may cause the switch  890 , during the first timeframes in the anodic/cathodic cycles, to move between connecting the voltage from the voltage generation or application device  810  to the ramp voltage generation system  891 , then to the sinusoidal voltage generation system  892 , and then to the constant DC voltage generation system  893 . In this embodiment of the invention, the control device  860  may also be directing or controlling the switch to connect certain ones of the voltage generation subsystems to the voltage from the regulator  385  during the second timeframe, e.g., during application of the second voltage.  
         [0086]      FIG. 9  illustrates a sensor electronics device including a microcontroller for generating voltage pulses according to an embodiment of the present invention. The advanced sensor electronics device may include a microcontroller  410  (see  FIG. 4 ), a digital-to-analog converter (DAC)  420 , an op amp  840 , and a sensor signal measurement circuit  431 . In an embodiment of the invention, the sensor signal measurement circuit may be a current-to-frequency (I/F) converter  430 . In the embodiment of the invention illustrated in  FIG. 9 , software or programmable logic in the microcontroller  410  provides instructions to transmit signals to the DAC  420 , which in turn instructs the DAC  420  to output a specific voltage to the operational amplifier  840 . The microcontroller  510  may also be instructed to output a specific voltage to the working electrode  375 , as is illustrated by line  911  in  FIG. 9 . As discussed above, the application of the specific voltage to operational amplifier  840  and the working electrode  375  may drive the voltage measured at the counter electrode to the specific voltage magnitude. In other words, the microcontroller  410  outputs a signal which is indicative of a voltage or a voltage waveform that is to be applied to the sensor  355  (e.g., the operational amplifier  840  coupled to the sensor  355 ). In an alternative embodiment of the invention, a fixed voltage may be set by applying a voltage directly from the DAC  420  between the reference electrode and the working electrode  375 . A similar result may also be obtained by applying voltages to each of the electrodes with the difference equal to the fixed voltage applied between the reference and working electrode. In addition, the fixed voltage may be set by applying a voltage between the reference and the counter electrode. Under certain operating conditions, the microcontroller  410  may generates a pulse of a specific magnitude which the DAC  420  understands represents that a voltage of a specific magnitude is to be applied to the sensor. After a first timeframe, the microcontroller  410  (via the program or programmable logic) outputs a second signal which either instructs the DAC  420  to output no voltage (for a sensor electronics device  360  operating according to the method described in  FIG. 6 ( a )) or to output a second voltage (for a sensor electronics device  360  operating according to the method described in  FIG. 6 ( b )). The microcontroller  410 , after the second timeframe has elapsed, then repeats the cycle of sending the signal indicative of a first voltage to apply, (for the first timeframe) and then sending the signal to instruct no voltage is to be applied or that a second voltage is to be applied (for the second timeframe).  
         [0087]     Under other operating conditions, the microcontroller  410  may generate a signal to the DAC  420  which instructs the DAC to output a ramp voltage. Under other operating conditions, the microcontroller  410  may generate a signal to the DAC  420  which instructs the DAC  420  to output a voltage simulating a sinusoidal voltage. These signals could be incorporated into any of the pulsing methodologies discussed above in the preceding paragraph or earlier in the application. In an embodiment of the invention, the microcontroller  410  may generate a sequence of instructions and/or pulses, which the DAC  420  receives and understands to mean that a certain sequence of pulses is to be applied. For example, the microcontroller  410  may transmit a sequence of instructions (via signals and/or pulses) that instruct the DAC  420  to generate a constant voltage for a first iteration of a first timeframe, a ramp voltage for a first iteration of a second timeframe, a sinusoidal voltage for a second iteration of a first timeframe, and a squarewave having two values for a second iteration of the second timeframe.  
         [0088]     The microcontroller  410  may include programmable logic or a program to continue this cycling for a stabilization timeframe or for a number of iterations. Illustratively, the microcontroller  410  may include counting logic to identify when the first timeframe or the second timeframe has elapsed. Additionally, the microcontroller  410  may include counting logic to identify that a stabilization timeframe has elapsed. After any of the preceding timeframes have elapsed, the counting logic may instruct the microcontroller to either send a new signal or to stop transmission of a signal to the DAC  420 .  
         [0089]     The use of the microcontroller  410  allows a variety of voltage magnitudes to be applied in a number of sequences for a number of time durations. In an embodiment of the invention, the microcontroller  410  may include control logic or a program to instruct the digital-to-analog converter  420  to transmit a voltage pulse having a magnitude of approximately 1.0 volt for a first time period of 1 minute, to then transmit a voltage pulse having a magnitude of approximately 0.5 volts for a second time period of 4 minutes, and to repeat this cycle for four iterations. In an embodiment of the invention, the microcontroller  420  may be programmed to transmit a signal to cause the DAC  420  to apply the same magnitude voltage pulse for each first voltage in each of the iterations. In an embodiment of the invention, the microcontroller  410  may be programmed to transmit a signal to cause the DAC to apply a different magnitude voltage pulse for each first voltage in each of the iterations. In this embodiment of the invention, the microcontroller  410  may also be programmed to transmit a signal to cause the DAC  420  to apply a different magnitude voltage pulse for each second voltage in each of the iterations. Illustratively, the microcontroller  410  may be programmed to transmit a signal to cause the DAC  420  to apply a first voltage pulse of approximately one volt in the first iteration, to apply a second voltage pulse of approximately 0.5 volts in the first iteration, to apply a first voltage of 0.7 volts and a second voltage of 0.4 volts in the second iteration, and to apply a first voltage of 1.2 and a second voltage of 0.8 in the third iteration.  
         [0090]     The microcontroller  410  may also be programmed to instruct the DAC  420  to provide a number of short duration voltage pulses for a first timeframe. In this embodiment of the invention, rather than one voltage being applied for the entire first timeframe (e.g., two minutes), a number of shorter duration pulses may be applied to the sensor. In this embodiment, the microcontroller  410  may also be programmed to program the DAC  420  to provide a number of short duration voltage pulses for the second timeframe to the sensor. Illustratively, the microcontroller  410  may send a signal to cause the DAC to apply a number of short duration voltage pulses where the short duration is 50 milliseconds or 100 milliseconds. In between these short duration pulses the DAC may apply no voltage or the DAC may apply a minimal voltage. The DAC  420  may cause the microcontroller to apply the short duration voltage pulses for the first timeframe, e.g., two minutes. The microcontroller  410  may then send a signal to cause the DAC to either not apply any voltage or to apply the short duration voltage pulses at a magnitude of a second voltage for a second timeframe to the sensor, e.g., the second voltage may be 0.75 volts and the second timeframe may be 5 minutes. In an embodiment of the invention, the microcontroller  410  may send a signal to the DAC  420  to cause the DAC  420  to apply a different magnitude voltage for each of short duration pulses in the first timeframe and/or in the second timeframe. In an embodiment of the invention, the microcontroller  410  may send a signal to the DAC  420  to cause the DAC  420  to apply a pattern of voltage magnitudes to the short durations voltage pulses for the first timeframe or the second timeframe. For example, the microcontroller may transmit a signal or pulses instructing the DAC  420  to apply thirty 20 millisecond pulses to the sensor during the first timeframe. Each of the thirty 20 millisecond pulses may have the same magnitude or may have a different magnitude. In this embodiment of the invention, the microcontroller  410  may instruct the DAC  420  to apply short duration pulses during the second timeframe or may instruct the DAC  420  to apply another voltage waveform during the second timeframe.  
         [0091]     Although the disclosures in  FIGS. 6-8  disclose the application of a voltage, a current may also be applied to the sensor to initiate the stabilization process. Illustratively, in the embodiment of the invention illustrated in  FIG. 6 ( b ), a first current may be applied during a first timeframe to initiate an anodic or cathodic response and a second current may be applied during a second timeframe to initiate the opposite anodic or cathodic response. The application of the first current and the second current may continue for a number of iterations or may continue for a stabilization timeframe. In an embodiment of the invention, a first current may be applied during a first timeframe and a first voltage may be applied during a second timeframe. In other words, one of the anodic or cathodic cycles may be triggered by a current being applied to the sensor and the other of the anodic or cathodic cycles may be triggered by a voltage being applied to the sensor. As described above, a current applied may be a constant current, a ramp current, a stepped pulse current, or a sinusoidal current. Under certain operating conditions, the current may be applied as a sequence of short duration pulses during the first timeframe.  
         [0092]      FIG. 9 ( b ) illustrates a sensor and sensor electronics utilizing an analyzation module for feedback in a stabilization period according to an embodiment of the present invention.  FIG. 9 ( b ) introduces an analyzation module  950  to the sensor electronics device  360 . The analyzation module  950  utilizes feedback from the sensor to determine whether or not the sensor is stabilized. In an embodiment of the invention, the microcontroller  410  may include instructions or commands to control the DAC  420  so that the DAC  420  applies a voltage or current to a part of the sensor  355 .  FIG. 9 ( b ) illustrates that a voltage or current could be applied between a reference electrode  370  and a working electrode  375 . However, the voltage or current can be applied in between electrodes or directly to one of the electrodes and the invention should not be limited by the embodiment illustrated in  FIG. 9 ( b ). The application of the voltage or current is illustrated by dotted line  955 . The analyzation module  950  may measure a voltage, a current, a resistance, or an impedance in the sensor  355 .  FIG. 9 ( b ) illustrates that the measurement occurs at the working electrode  375 , but this should not be limit the invention because other embodiments of the invention may measure a voltage, a current, a resistance, or an impedance in between electrodes of the sensor or direct at either the reference electrode  370  or the counter electrode  365 . The analyzation module  950  may receive the measured voltage, current, resistance, or impedance and may compare the measurement to a stored value (e.g., a threshold value). Dotted line  956  represents the analyzation module  950  reading or taking a measurement of the voltage, current, resistance, or impedance. Under certain operating conditions, if the measured voltage, current, resistance, or impedance is above the threshold, the sensor is stabilized and the sensor signal is providing accurate readings of a physiological condition of a patient. Under other operating conditions, if the measured voltage, current, resistance, or impedance is below the threshold, the sensor is stabilized. Under other operating conditions, the analyzation module  950  may verify that the measured voltage, current, resistance, or impedance is stable for a specific timeframe, e.g., one minute or two minutes. This may represent that the sensor  355  is stabilized and that the sensor signal is transmitting accurate measurements of a subject&#39;s physiological parameter, e.g., blood glucose level. After the analyzation module  950  has determined that the sensor is stabilized and the sensor signal is providing accurate measurements, the analyzation module  950  may transmit a signal (e.g., a sensor stabilization signal) to the microcontroller  410  indicating that the sensor is stabilized and that the microcontroller  410  can start using or receiving the sensor signal from the sensor  355 . This is represented by dotted line  957 .  
         [0093]      FIG. 10  illustrates a block diagram of a sensor system including hydration electronics according to an embodiment of the present invention. The sensor system includes a connector  1010 , a sensor  1012 , and a monitor or sensor electronics device  1025 . The sensor  1010  includes electrodes  1020  and a connection portion  1024 . In an embodiment of the invention, the sensor  1012  may be connected to the sensor electronics device  1025  via a connector  1010  and a cable. In other embodiments of the invention, the sensor  1012  may be directly connected to the sensor electronics device  1025 . In other embodiments of the invention, the sensor  1012  may be incorporated into the same physical device as the sensor electronics device  1025 . The monitor or sensor electronics device  1025  may include a power supply  1030 , a regulator  1035 , a signal processor  1040 , a measurement processor  1045 , and a processor  1050 . The monitor or sensor electronics device  1025  may also include a hydration detection circuit  1060 . The hydration detection circuit  1060  interfaces with the sensor  1012  to determine if the electrodes  1020  of the sensor  1012  are sufficiently hydrated. If the electrodes  1020  are not sufficiently hydrated, the electrodes  1020  do not provide accurate glucose readings, so it is important to know when the electrodes  1020  are sufficiently hydrated. Once the electrodes  1020  are sufficiently hydrated, accurate glucose readings may be obtained.  
         [0094]     In an embodiment of the invention illustrated in  FIG. 10 , the hydration detection circuit  1060  may include a delay or timer module  1065  and a connection detection module  1070 . In an embodiment of the invention utilizing the short term sensor or the subcutaneous sensor, after the sensor  1012  has been inserted into the subcutaneous tissue, the sensor electronics device or monitor  1025  is connected to the sensor  1012 . The connection detection module  1070  identifies that the sensors electronics device  1025  has been connected to the sensor  1012  and sends a signal to the timer module  1065 . This is illustrated in  FIG. 10  by the arrow  1084  which represents a detector  1083  detecting a connection and sending a signal to the connection detection module  1070  indicating the sensor  1012  has been connected to the sensor electronics device  1025 . In an embodiment of the invention where implantable or long-term sensors are utilized, a connection detection module  1070  identifies that the implantable sensor has been inserted into the body. The timer module  1065  receives the connection signal and waits a set or established hydration time. Illustratively, the hydration time may be two minutes, five minutes, ten minutes, or 20 minutes. These examples are meant to be illustrative and not to be limiting. The timeframe does not have to be a set number of minutes and can include any number of seconds. In an embodiment of the invention, after the timer module  1065  has waited for the set hydration time, the timer module  1065  may notify the processor  1050  that the sensor  1012  is hydrated by sending a hydration signal, which is illustrated by dotted line  1086 .  
         [0095]     In this embodiment of the invention, the processor  1050  may receive the hydration signal and only start utilizing the sensor signal (e.g., sensor measurements) after the hydration signal has been received. In another embodiment of the invention, the hydration detection circuit  1060  may be coupled between the sensor (the sensor electrodes  1020 ) and the signal processor  1040 . In this embodiment of the invention, the hydration detection circuit  1060  may prevent the sensor signal from being sent to signal processor  1040  until the timer module  1065  has notified the hydration detection circuit  1060  that the set hydration time has elapsed. This is illustrated by the dotted lines labeled with reference numerals  1080  and  1081 . Illustratively, the timer module  1065  may transmit a connection signal to a switch (or transistor) to turn on the switch and let the sensor signal proceed to the signal processor  1040 . In an alternative embodiment of the invention, the timer module  1065  may transmit a connection signal to turn on a switch  1088  (or close the switch  1088 ) in the hydration detection circuit  1060  to allow a voltage from the regulator  1035  to be applied to the sensor  1012  after the hydration time has elapsed. In other words, in this embodiment of the invention, the voltage from the regulator  1035  is not applied to the sensor  1012  until after the hydration time has elapsed.  
         [0096]      FIG. 11  illustrates an embodiment of the invention including a mechanical switch to assist in determining a hydration time. In an embodiment of the invention, a single housing may include a sensor assembly  1120  and a sensor electronics device  1125 . In an embodiment of the invention, the sensor assembly  1120  may be in one housing and the sensor electronics device  1125  may be in a separate housing, but the sensor assembly  1120  and the sensor electronics device  1125  may be connected together. In this embodiment of the invention, a connection detection mechanism  1160  may be a mechanical switch. The mechanical switch may detect that the sensor  1120  is physically connected to the sensor electronics device  1125 . In an embodiment of the invention, a timer circuit  1135  may also be activated when the mechanical switch  1160  detects that the sensor  1120  is connected to the sensor electronics device  1125 . In other words, the mechanical switch may close and a signal may be transferred to a timer circuit  1135 . Once a hydration time has elapsed, the timer circuit  1135  transmits a signal to the switch  1140  to allow the regulator  1035  to apply a voltage to the sensor  1120 . In other words, no voltage is applied until the hydration time has elapsed. In an embodiment of the invention, current may replace voltage as what is being applied to the sensor once the hydration time elapses. In an alternative embodiment of the invention, when the mechanical switch  1160  identifies that a sensor  1120  has been physically connected to the sensor electronics device  1125 , power may initially be applied to the sensor  1120 . Power being sent to the sensor  1120  results in a sensor signal being output from the working electrode in the sensor  1120 . The sensor signal may be measured and sent to a processor  1175 . The processor  1175  may include a counter input. Under certain operating conditions, after a set hydration time has elapsed from when the sensor signal was input into the processor  1175 , the processor  1175  may start processing the sensor signal as an accurate measurement of the glucose in a subject&#39;s body. In other words, the processor  1170  has received the sensor signal from the potentiostat circuit  1170  for a certain amount of time, but will not process the signal until receiving an instruction from the counter input of the processor identifying that a hydration time has elapsed. In an embodiment of the invention, the potentiostat circuit  1170  may include a current-to-frequency converter  1180 . In this embodiment of the invention, the current-to-frequency converter  1180 , may receive the sensor signal as a current value and may convert the current value into a frequency value, which is easier for the processor  1175  to handle.  
         [0097]     In an embodiment of the invention, the mechanical switch  1160  may also notify the processor  1170  when the sensor  1120  has been disconnected from the sensor electronics device  1125 . This is represented by dotted line  1176  in  FIG. 11 . This may result in the processor  1170  powering down or reducing power to a number of components, chips, and/or circuits of the sensor electronics device  1125 . If the sensor  1120  is not connected, the battery or power source may be drained if the components or circuits of the sensor electronics device  1125  are in a power on state. Accordingly, if the mechanical switch  1160  detects that the sensor  1120  has been disconnected from the sensor electronics device  1125 , the mechanical switch may indicate this to the processor  1175 , and the processor  1175  may power down or reduce power to one or more of the electronic circuits, chips, or components of the sensor electronics device  1125 .  
         [0098]      FIG. 12  illustrates an electrical method of detection of hydration according to an embodiment of the invention. In an embodiment of the invention, an electrical detecting mechanism for detecting connection of a sensor may be utilized. In this embodiment of the invention, the hydration detection electronics  1250  may include an AC source  1255  and a detection circuit  1260 . The hydration detection electronics  1250  may be located in the sensor electronics device  1225 . The sensor  1220  may include a counter electrode  1221 , a reference electrode  1222 , and a working electrode  1223 . As illustrated in  FIG. 12 , the AC source  1255  is coupled to a voltage setting device  1275 , the reference electrode  1222 , and the detection circuit  1260 . In this embodiment of the invention, an AC signal from the AC source is applied to the reference electrode connection, as illustrated by dotted line  1291  in  FIG. 12 . In an embodiment of the invention, the AC signal is coupled to the sensor  1220  through an impedance and the coupled signal is attenuated significantly if the sensor  1220  is connected to the sensor electronics device  1225 . Thus, a low level AC signal is present at an input to the detection circuit  1260 . This may also be referred to as a highly attenuated signal or a signal with a high level of attenuation. Under certain operating conditions, the voltage level of the AC signal may be Vapplied*(Ccoupling)/(Ccoupling+Csensor). If the detection circuit  1260  detects that the a high level AC signal (lowly attenuated signal) is present at an input terminal of the detection circuit  1260 , no interrupt is sent to the microcontroller  410  because the sensor  1220  has not been sufficiently hydrated or activated. For example, the input of the detection circuit  1260  may be a comparator. If the sensor  1220  is sufficiently hydrated (or wetted), an effective capacitance forms between the counter electrode and the reference electrode, (e.g., capacitance C r-c  in  FIG. 12 ) and an effective capacitance forms between the reference electrode and the working electrode (e.g., capacitance C w-r  in  FIG. 12 ). In other words, an effective capacitance relates to capacitance being formed between two nodes and does not represent that an actual capacitor is placed in a circuit between the two electrodes. In an embodiment of the invention, the AC signal from the AC source  1255  is sufficiently attenuated by capacitances C r-c  and C w-r  and the detection circuit  1260  detects the presence of a low level or highly attenuated AC signal from the AC source  1255  at the input terminal of the detection circuit  1260 . This embodiment of the invention is significant because the utilization of the existing connections between the sensor  1120  and the sensor electronics device  1125  reduces the number of connections to the sensor. In other words, the mechanical switch, disclosed in  FIG. 11 , requires a switch and associated connections between the sensor  1120  and the sensor electronics device  1125 . It is advantageous to eliminate the mechanical switch because the sensor  1120  is continuously shrinking in size and the elimination of components helps achieve this size reduction. In alternative embodiments of the invention, the AC signal may be applied to different electrodes (e.g., the counter electrode or the working electrode) and the invention may operate in a similar fashion.  
         [0099]     As noted above, after the detection circuit  1260  has detected that a low level AC signal is present at the input terminal of the detection circuit  1260 , the detection circuit  1260  may later detect that a high level AC signal, with low attenuation, is present at the input terminal. This represents that the sensor  1220  has been disconnected from the sensor electronics device  1225  or that the sensor is not operating properly. If the sensor has been disconnected from the sensor electronics device  1225 , the AC source may be coupled with little or low attenuation to the input of the detection circuit  1260 . As noted above, the detection circuit  1260  may generate an interrupt to the microcontroller. This interrupt may be received by the microcontroller and the microcontroller may reduce or eliminate power to one or a number of components or circuits in the sensor electronics device  1225 . This may be referred to as the second interrupt. Again, this helps reduce power consumption of the sensor electronics device  1225 , specifically when the sensor  1220  is not connected to the sensor electronics device  1225 .  
         [0100]     In an alternative embodiment of the election illustrated in  FIG. 12 , the AC signal may be applied to the reference electrode  1222 , as is illustrated by reference numeral  1291 , and an impedance measuring device  1277  may measure the impedance of an area in the sensor  1220 . Illustratively, the area may be an area between the reference electrode and the working electrode, as illustrated by dotted line  1292  in  FIG. 12 . Under certain operating conditions, the impedance measuring device  1277  may transmit a signal to the detection circuit  1260  if a measured impedance has decreased to below an impedance threshold or other set criteria. This represents that the sensor is sufficiently hydrated. Under other operating conditions, the impedance measuring device  1277  may transmit a signal to the detection circuit  1260  once the impedance is above an impedance threshold. The detection circuit  1260  then transmits the interrupt to the microcontroller  410 . In another embodiment of the invention, the detection circuit  1260  may transmit an interrupt or signal directly to the microcontroller.  
         [0101]     In an alternative embodiment of the invention, the AC source  1255  may be replaced by a DC source. If a DC source is utilized, then a resistance measuring element may be utilized in place of an impedance measuring element  1277 . In an embodiment of the invention utilizing the resistance measuring element, once the resistance drops below a resistance threshold or a set criteria, the resistance measuring element may transmit a signal to the detection circuit  1260  (represented by dotted line  1293 ) or directly to the microcontroller indicating that the sensor is sufficiently hydrated and that power may be applied to the sensor.  
         [0102]     In the embodiment of the invention illustrated in  FIG. 12 , if the detection circuit  1260  detects a low level or highly attenuated AC signal from the AC source, an interrupt is generated to the microcontroller  410 . This interrupt indicates that sensor is sufficiently hydrated. In this embodiment of the invention, in response to the interrupt, the microcontroller  410  generates a signal that is transferred to a digital-to-analog converter  420  to instruct or cause the digital-to-analog converter  420  to apply a voltage or current to the sensor  1220 . Any of the different sequence of pulses or short duration pulses described above in FIGS.  6 ( a ),  6 ( b ), or  6 ( c ) or the associated text describing the application of pulses, may be applied to the sensor  1220 . Illustratively, the voltage from the DAC  420  may be applied to an op-amp  1275 , the output of which is applied to the counter electrode  1221  of the sensor  1220 . This results in a sensor signal being generated by the sensor, e.g., the working electrode  1223  of the sensor. Because the sensor is sufficiently hydrated, as identified by the interrupt, the sensor signal created at the working electrode  1223  is accurately measuring glucose. The sensor signal is measured by a sensor signal measuring device  431  and the sensor signal measuring device  431  transmits the sensor signal to the microcontroller  410  where a parameter of a subject&#39;s physiological condition is measured. The generation of the interrupt represents that a sensor is sufficiently hydrated and that the sensor  1220  is now supplying accurate glucose measurements. In this embodiment of the invention, the hydration period may depend on the type and/or the manufacturer of the sensor and on the sensor&#39;s reaction to insertion or implantation in the subject. Illustratively, one sensor  1220  may have a hydration time of five minutes and one sensor  1220  may have a hydration time of one minute, two minutes, three minutes, six minutes, or 20 minutes. Again, any amount of time may be an acceptable amount of hydration time for the sensor, but smaller amounts of time are preferable.  
         [0103]     If the sensor  1220  has been connected, but is not sufficiently hydrated or wetted, the effective capacitances C r-c  and C w-r  may not attenuate the AC signal from the AC source  1255 . The electrodes in the sensor  1120  are dry before insertion and because the electrodes are dry, a good electrical path (or conductive path) does not exist between the two electrodes. Accordingly, a high level AC signal or lowly attenuated AC signal may still be detected by the detection circuit  1260  and no interrupt may be generated. Once the sensor has been inserted, the electrodes become immersed in the conductive body fluid. This results in a leakage path with lower DC resistance. Also, boundary layer capacitors form at the metal/fluid interface. In other words, a rather large capacitance forms between the metal/fluid interface and this large capacitance looks like two capacitors in series between the electrodes of the sensor. This may be referred to as an effective capacitance. In practice, a conductivity of an electrolyte above the electrode is being measured. In some embodiments of the invention, the glucose limiting membrane (GLM) also illustrates impedance blocking electrical efficiency. An unhydrated GLM results in high impedance, whereas a high moisture GLM results in low impedance. Low impedance is desired for accurate sensor measurements.  
         [0104]      FIG. 13 ( a ) illustrates a method of hydrating a sensor according to an embodiment of the present invention. In an embodiment of the invention, the sensor may be physically connected  1310  to the sensor electronics device. After the connection, in one embodiment of the invention, a timer or counter may be initiated to count  1320  a hydration time. After the hydration time has elapsed, a signal may be transmitted  1330  to a subsystem in the sensor electronics device to initiate the application of a voltage to the sensor. As discussed above, in an embodiment of the invention, a microcontroller may receive the signal and instruct the DAC to apply a voltage to the sensor or in another embodiment of the invention, a switch may receive a signal which allows a regulator to apply a voltage to the sensor. The hydration time may be five minutes, two minutes, ten minutes and may vary depending on the subject and also on the type of sensor.  
         [0105]     In an alternative embodiment of the invention, after the connection of the sensor to the sensor electronics device, an AC signal (e.g., a low voltage AC signal) may be applied  1340  to the sensor, e.g., the reference electrode of the sensor. The AC signal may be applied because the connection of the sensor to the sensor electronics device allows the AC signal to be applied to the sensor. After application of the AC signal, an effective capacitance forms  1350  between the electrode in the sensor that the voltage is applied to and the other two electrodes. A detection circuit determines  1360  what level of the AC signal is present at the input of the detection circuit. If a low level AC signal (or highly attenuated AC signal) is present at the input of the detection circuit, due to the effective capacitance forming a good electrical conduit between the electrodes and the resulting attenuation of the AC signal, an interrupt is generated  1370  by the detection circuit and sent to a microcontroller.  
         [0106]     The microcontroller receives the interrupt generated by the detection circuit and transmits  1380  a signal to a digital-to-analog converter instructing or causing the digital-to-analog converter to apply a voltage to an electrode of the sensor, e.g., the counter electrode. The application of the voltage to the electrode of the sensor results in the sensor creating or generating a sensor signal  1390 . A sensor signal measurement device  431  measures the generated sensor signal and transmits the sensor signal to the microcontroller. The microcontroller receives  1395  the sensor signal from the sensor signal measurement device, which is coupled to the working electrode, and processes the sensor signal to extract a measurement of a physiological characteristic of the subject or patient.  
         [0107]      FIG. 13 ( b ) illustrates an additional method for verifying hydration of a sensor according to an embodiment of the present invention. In the embodiment of the invention illustrated in  FIG. 13 ( b ), the sensor is physically connected  1310  to the sensor electronics device. In an embodiment of the invention, an AC signal is applied  1341  to an electrode, e.g., a reference electrode, in the sensor. Alternatively, in an embodiment of the invention, a DC signal is applied  1341  to an electrode in the sensor. If an AC signal is applied, an impedance measuring element measures  1351  an impedance at a point within the sensor. Alternatively, if a DC signal is applied a resistance measuring element measures  1351  a resistance at a point within the sensor. If the resistance or impedance is lower than an resistance threshold or impedance threshold, respectively, (or other set criteria), then the impedance (or resistance) measuring element transmits  1361  (or allows a signal to be transmitted) to the detection circuit, and the detection circuit transmits an interrupt identifying that the sensor is hydrated to the microcontroller. The reference numbers  1380 ,  1390 , and  1395  are the same in FIGS.  13 ( a ) and  13 ( b ) because they represent the same action.  
         [0108]     The microcontroller receives the interrupt and transmits  1380  a signal to a digital-to-analog converter to apply a voltage to the sensor. In an alternative embodiment of the invention, the digital-to-analog converter can apply a current to the sensor, as discussed above. The sensor, e.g., the working electrode, creates  1390  a sensor signal, which represents a physiological parameter of a patient. The microcontroller receives  1395  the sensor signal from a sensor signal measuring device, which measures the sensor signal at an electrode in the sensor, e.g., the working electrode. The microcontroller processes the sensor signal to extract a measurement of the physiological characteristic of the subject or patient, e.g., the blood glucose level of the patient.  
         [0109]     FIGS.  14 ( a ) and ( b ) illustrate methods of combining hydrating of a sensor with stabilizing of a sensor according to an embodiment of the present invention. In an embodiment of the invention illustrated in  FIG. 14 ( a ), the sensor is connected  1405  to the sensor electronics device. The AC signal is applied  1410  to an electrode of the sensor. The detection circuit determines  1420  what level of the AC signal is present at an input of the detection circuit. If the detection circuit determines that a low level of the AC signal is present at the input, (representing a high level of attenuation to the AC signal), an interrupt is sent  1430  to microcontroller. Once the interrupt is sent to the microcontroller, the microcontroller knows to begin or initiate  1440  a stabilization sequence, i.e., the application of a number of voltage pulses to an electrode of the sensors, as described above. For example, the microcontroller may cause a digital-to-analog converter to apply three voltage pulses (having a magnitude of +0.535 volts) to the sensor with each of the three voltage pulses followed by a period of three voltage pulses (having a magnitude of 1.07 volts to be applied). This may be referred to transmitting a stabilization sequence of voltages. The microcontroller may cause this by the execution of a software program in a read-only memory (ROM) or a random access memory. After the stabilization sequence has finished executing, the sensor may generate  1450  a sensor signal, which is measured and transmitted to a microcontroller.  
         [0110]     In an embodiment of the invention, the detection circuit may determine  1432  that a high level AC signal has continued to be present at the input of the detection circuit (e.g., an input of a comparator), even after a hydration time threshold has elapsed. For example, the hydration time threshold may be 10 minutes. After 10 minutes has elapsed, the detection circuit may still be detecting that a high level AC signal is present. At this point in time, the detection circuit may transmit  1434  a hydration assist signal to the microcontroller. If the microcontroller receives the hydration assist signal, the microcontroller may transmit  1436  a signal to cause a DAC to apply a voltage pulse or a series of voltage pulses to assist the sensor in hydration. In an embodiment of the invention, the microcontroller may transmit a signal to cause the DAC to apply a portion of the stabilization sequence or other voltage pulses to assist in hydrating the sensor. In this embodiment of the invention, the application of voltage pulses may result in the low level AC signal (or highly attenuated signal) being detected  1438  at the detection circuit. At this point, the detection circuit may transmit an interrupt, as is disclosed in step  1430 , and the microcontroller may initiate a stabilization sequence.  
         [0111]      FIG. 14 ( b ) illustrates a second embodiment of a combination of a hydration method and a stabilization method where feedback is utilized in the stabilization process. A sensor is connected  1405  to a sensor electronics device. An AC signal (or a DC signal) is applied  1411  to the sensor. In an embodiment of the invention, the AC signal (or the DC signal) is applied to an electrode of the sensor, e.g. the reference electrode. A impedance measuring device (or resistance measuring device) measures  1416  the impedance (or resistance) within a specified area of the sensor. In an embodiment of the invention, the impedance (or resistance) may be measured between the reference electrode and the working electrode. The measured impedance (or resistance) may be compared  1421  to an impedance or resistance value to see if the impedance (or resistance) is low enough in the sensor, which indicates the sensor is hydrated. If the impedance (or resistance) is below the impedance (or resistance) value or other set criteria, (which may be a threshold value), an interrupt is transmitted  1431  to the microcontroller. After receiving the interrupt, the microcontroller transmits  1440  a signal to the DAC instructing the DAC to apply a stabilization sequence of voltages (or currents) to the sensor. After the stabilization sequence has been applied to the sensor, a sensor signal is created in the sensor (e.g., at the working electrode), is measured by a sensor signal measuring device, is transmitted by the sensor signal measuring device, and is received  1450  by the microcontroller. Because the sensor is hydrated and the stabilization sequence of voltages has been applied to the sensor, the sensor signal is accurately measuring a physiological parameter (i.e., blood glucose).  
         [0112]      FIG. 14 ( c ) illustrates a third embodiment of the invention where a stabilization method and hydration method are combined. In this embodiment of the invention, the sensor is connected  1500  to the sensor electronics device. After the sensor is physically connected to the sensor electronics device, an AC signal (or DC signal) is applied  1510  to an electrode (e.g., reference electrode) of the sensor. At the same time, or around the same time, the microcontroller transmits a signal to cause the DAC to apply  1520  a stabilization voltage sequence to the sensor. In an alternative embodiment of the invention, a stabilization current sequence may be applied to the sensor instead of a stabilization voltage sequence. The detection circuit determines  1530  what level of an AC signal (or DC signal) is present at an input terminal of the detection circuit. If there is a low level AC signal (or DC signal), representing a highly attenuated AC signal (or DC signal), present at the input terminal of the detection circuit, an interrupt is transmitted  1540  to the microcontroller. Because the microcontroller has already initiated the stabilization sequence, the microcontroller receives the interrupt and sets  1550  a first indicator that the sensor is sufficiently hydrated. After the stabilization sequence is complete, the microcontroller sets  1555  a second indicator indicating the completion of the stabilization sequence. The application of the stabilization sequence voltages results in the sensor, e.g., the working electrode, creating  1560  a sensor signal, which is measured by a sensor signal measuring circuit, and sent to the microcontroller. If the second indicator that the stabilization sequence is complete is set and the first indicator that the hydration is complete is set, the microcontroller is able to utilize  1570  the sensor signal. If one or both of the indicators are not set, the microcontroller may not utilize the sensor signal because the sensor signal may not represent accurate measurements of the physiological measurements of the subject.  
         [0113]     In further embodiments of the present invention, an Electrochemical Impedance Spectroscopy (EIS) technique can be incorporated into the both the hydration and stabilization routines as another way to determine when additional initializations should be applied to help in the hydration and stabilization processes of the sensor. Typically, the microcontroller will transmit an EIS signal to a digital-to-analog converter instructing or causing the digital-to-analog converter to apply an AC voltage of various frequencies and a DC bias between the working and reference electrodes. In preferred embodiments, the electrochemical impedance spectroscopy (EIS) circuit using the existing hardware is capable of generating an AC voltage between 0.1 Hz to 100 KHz, with a programmable amplitude of up to 100 mV, between the working and reference electrodes. In addition, the EIS circuit is also capable of sampling the current through the working electrode at up to 1 MHz sampling rate. Electrochemical Impedance Spectroscopy is a technique used to better characterize the behavior of an electrochemical system, and in particular, an electrode, and thus an improvement of previous methodology that limited the application to a simple DC current or an AC voltage of single frequency.  FIG. 15  illustrates some examples of applied voltage between working and reference electrodes using the EIS technique. In the examples of  FIG. 15 , the DC bias is set at 0.535 V, and an AC voltage of varying frequencies are added to the DC bias to create a perturbation signal. The amplitude of the AC voltage is fixed at 0.01V. The EIS may be performed at frequencies from μHz to MHz range, but in this invention, only a narrow range of frequencies is needed. Using a current-measuring device, the current passing through the working electrode can be measured. By dividing the applied voltage by the current, the impedance of the working electrode can be calculated.  
         [0114]     In further preferred embodiment, the use of EIS technique can give valuable information on the aging of the sensor. Specifically, under different frequencies, the amplitude and the phase angle of the impedance vary. By plotting the real (X-Axis) and imaginary part (Y-Axis) of the impedance under different frequencies, a Nyquist plot may be obtained as seen in  FIG. 16 . Impedance is a measure of opposition to an alternating or direct current. It is a complex value, i.e., it has an amplitude and a phase angle, and it has a real and an imaginary part. On a Nyquist Plot, the X value of an impedance is the real impedance, and the Y value of an impedance is the imaginary impedance. The phase angle is the angle between the impedance point, (X,Y), and the X axis.  FIG. 16  illustrates an example of a Nyquist plot where the selected frequencies, from 0.1 Hz to 1000 Mhz AC voltages plus a DC voltage (DC bias) are applied between the working electrode and the counter electrode. Starting from the right, the frequency increases from 0.1 Hz. With each frequency, the real and imaginary impedance can be calculated and plotted. A typical Nyquist plot of an electrochemical system looks like a semicircle joined with a straight line, where the semicircle and the line indicates the plotted impedance. In preferred embodiments, the impedance at the inflection point is a particular interest since it is easiest to identify in the Nyquist plot (i.e. where the semicircle meets the straight line). Typically the inflection point is close to the X axis, and the X value of the inflection point approximates the sum of polarization resistance and solution resistance (Rp+Rs). Solution Resistance (Rs) is defined as the resistance of the solution in which the electrodes are immersed in, and Polarization Resistance (Rp) is defined as the voltage between the working electrode and the bulk of the solution divided by the current flowing through the working electrode. Current flowing through the working electrode is produced as a result of electrical voltage being applied to the working electrode such that electrochemical reactions occur (i.e., gaining from, or losing to, electrons to the electrode) thus generating the current that flows through the working electrode. Although the preferred embodiment uses the impedance at the inflection point (i.e. Rp+Rs) to determine the aging, status, stabilization and hydration of the sensor, alternative embodiments can use any impedance value using either the X value or phase angle as a reference for the particular impedance being used.  
         [0115]     In alternative embodiments, a variety of alternative EIS techniques can be used to measure the impedance of the sensor. For example, a potential step, from the normal operating voltage of 0.535 volt to 0.545 volt, can be applied between the working and reference electrodes. The current through the working electrode can then be measured. In response to the potential step, the current would spike and then decline. The speed of current decline provides an alternative way to estimate the impedance, in particular, Rp+Rs.  
         [0116]     As seen in  FIG. 17 , the sensor impedance, in particular, the sum of Rp and Rs, reflects the sensor age as well as the sensor&#39;s operating conditions. Thus, a new sensor normally has higher impedance than a used sensor as seen from the different plots in  FIG. 17 . Thus, by looking at the X-value of the sum of Rp and Rs, a threshold can be used to determine when the sensor&#39;s age has exceeded the specified operating life of the sensor.  FIG. 17  illustrates an example of Nyquist plot over the life time of a sensor. The points indicated by arrows are the inflection point. Before initialization, Rs+Rp is higher than 8.5 kiloohms, after initialization, the Rs+Rp dropped to below 8 kiloohms. Over the next six days, Rs+Rp continues to decrease, at the end of the specified sensor life, Rs+Rp dropped below 6.5 kiloohms. Based on such examples, a threshold value can be set to specify when Rs+Rp value would indicate the end of the specified operating life of the sensor. Therefore, the EIS technique allows the sensor to close the loophole of allowing the reusing a sensor beyond the specified operating time. In other words, if the patient attempts to re-use a sensor after the sensor has reached its specified operating time by disconnecting and then re-connecting the sensor again, the EIS will measure abnormal low impedance. Thereby, the system may then be able to reject the sensor and prompt the patient for a new sensor. Additionally, the use of the EIS may also detect sensor failure by detecting when the sensor&#39;s impedance drops below a low impedance threshold level indicating that the sensor may be too worn to operate normally. The system may then terminate the sensor before the specified operating life. In addition, sensor impedance can also be used to detect additional sensor failure. For example, when a sensor is going into a low-current state (i.e. sensor failure) due to any variety of reasons, the sensor impedance may also increase beyond a certain high impedance threshold. If the impedance becomes abnormally high during sensor operation, due to protein or polypeptide fouling, macrophage attachment or any other factor, the system may also terminate the sensor before the specified sensor operating life.  
         [0117]      FIG. 18  illustrates how the EIS technique can be applied during sensor stabilization and detecting the age of the sensor in accordance with embodiments of the present invention. The logic of  FIG. 18  begins at  1800  after the hydration procedure and sensor initialization procedure described above has been completed. In other words, the sensor has been deemed to be sufficiently hydrated, and the first initialization procedure has been applied to initialize the sensor. In preferred embodiments, the initialization procedure is in the form of voltage pulses as described previous in the detailed description. However, in alternative embodiments, different waveforms can be used for the initialization procedure. For example, a sine wave can be used, instead of the pulses, to accelerate the wetting or conditioning of the sensor. In addition, it may be necessary for some portion of the waveform to be greater than the normal operating voltage of the sensor, i.e., 0.535 volt.  
         [0118]     At block  1810 , an EIS procedure is applied and the impedance is compared to both a first high and low threshold. An example of a first high and first low threshold value would be 7 kiloohm and 8.5 kiloohm, respectively, although the values can be set higher or lower as needed. If the impedance, for example, Rp+Rs, is higher than the first high threshold, the sensor undergoes an additional initialization procedure (e.g., the application of one or more additional pulses) at block  1820 . Ideally, the number of total initialization procedures given to the initialize the sensor would be optimized to limit the impact on both the, battery life of the sensor, and the overall amount of time needed to stabilize a sensor. Thus, by applying the EIS procedure, fewer initializations can be initially sent, and the number of initializations can incrementally added to give just the right amount of initializations to ready the sensor for use. Similarly, in an alternative embodiment, the EIS procedure can be applied to the hydration procedure to minimize the number of initializations needed to aid the hydration process as described in  FIGS. 13-14 .  
         [0119]     On the other hand, if the impedance, for example Rp+Rs, is below the first low threshold, the sensor will be determined to be faulty and would be terminated immediately at block  1860 . A message to the user will be given to replace the sensor and to begin the hydration process again. If the impedance is within the high and low threshold, the sensor will begin to operate normally at block  1830 . The logic than proceeds to block  1840  where an additional EIS is performed to check the age of the sensor. The first time the logic reaches block  1840 , the microcontroller will perform an EIS to gauge the age of the sensor to close the loophole of the user being able to plug in and plug out the same sensor. In future iterations of the EIS procedure as the logic returns to block  1840 , the microprocessor will perform an EIS at fixed intervals during the specified life of the sensor. In preferred embodiments, the fixed interval is set for every 2 hours, however, longer or shorter periods of time can easily be used. At block  1850 , the impedance is compared to a second high and low threshold. An example of a second high and second low threshold value would be 5.5 kiloohm and 8.5 kiloohm, respectively, although the values can be set higher or lower as needed. As long as the impedance values stay within a second high and low threshold, the logic proceeds to block  1830  where the sensor operates normally until the specified sensor life, for example, 5 days, is reached. Of course, as described with respect to block  1840 , EIS will be performed at the regularly scheduled intervals throughout the specified sensor life. However, if after the EIS is performed, the impedance is determined to have dropped below a second lower threshold or risen above a second higher threshold at block  1850 , the sensor is terminated at block  1860 . In further alternative embodiments, a secondary check can be implemented of a faulty sensor reading. For example, if the EIS indicates that the impedance is out of the range of the second high and low threshold, the logic can perform a second EIS to confirm that the second thresholds are indeed not met (and confirm that the first EIS was correctly performed) before determining the end of sensor at block  1860 .  
         [0120]     While the description above refers to particular embodiments of the present invention, it will be understood that many modifications may be made without departing from the spirit thereof. For example, additional steps and changes to the order of the algorithms can be made while still performing the key teachings of the present invention. Thus, the accompanying claims are intended to cover such modifications as would fall within the true scope and spirit of the present invention. The presently disclosed embodiments are, therefore, to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than the foregoing description. All changes that come within the meaning of and range of equivalency of the claims are intended to be embraced therein.