Source: http://www.google.com/patents/US20050027182?dq=6,260,087
Timestamp: 2016-07-02 00:49:14
Document Index: 314212380

Matched Legal Cases: ['art 220', 'art 250', 'art 420', 'art 440', 'art 460', 'art 460', 'art 470']

Patent US20050027182 - System for monitoring physiological characteristics - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign inPatentsApparatuses and methods for medical monitoring physiological characteristic values such as blood glucose levels for the treatment of diabetes, are presented. The apparatuses and methods provide advanced alarm and reminder functions, as well as advanced data presentation tools to further facilitate convenient...http://www.google.com/patents/US20050027182?utm_source=gb-gplus-sharePatent US20050027182 - System for monitoring physiological characteristicsAdvanced Patent SearchPublication numberUS20050027182 A1Publication typeApplicationApplication numberUS 10/750,080Publication dateFeb 3, 2005Filing dateDec 31, 2003Priority dateDec 27, 2001Also published asCA2550855A1, CA2550855C, EP1703839A2, EP1703839B1, US8961416, US20070232880, WO2005065538A2, WO2005065538A3Publication number10750080, 750080, US 2005/0027182 A1, US 2005/027182 A1, US 20050027182 A1, US 20050027182A1, US 2005027182 A1, US 2005027182A1, US-A1-20050027182, US-A1-2005027182, US2005/0027182A1, US2005/027182A1, US20050027182 A1, US20050027182A1, US2005027182 A1, US2005027182A1InventorsUzair Siddiqui, Himanshu Patel, John Mastrototaro, Linda Fredrickson, Kris Holtzclaw, Bruce Wenholz, Mark Estes, Frank SaidaraOriginal AssigneeUzair Siddiqui, Patel Himanshu P., Mastrototaro John J., Fredrickson Linda P., Holtzclaw Kris R., Wenholz Bruce R., Estes Mark C., Frank SaidaraExport CitationBiBTeX, EndNote, RefManPatent Citations (46), Referenced by (467), Classifications (24), Legal Events (1) External Links: USPTO, USPTO Assignment, EspacenetSystem for monitoring physiological characteristics
CROSS-REFERENCE TO RELATED APPLICATIONS [0001] This continuation-in-part application claims priority under 35 U.S.C. �120 from U.S. patent application Ser. No. 10/034,139, filed Dec. 27, 2001, and entitled “SYSTEM FOR MONITORING PHYSIOLOGICAL CHARACTERISTICS,” which is incorporated herein by reference.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT [0047] 1. Overview [0048] Embodiments of the present invention encompass methods and systems for the convenient operation of monitoring physiological characteristics (“characteristic monitoring systems”). The description provided here encompasses the architecture of the apparatus as well as its control and convenience features. The control and convenience features of the present invention can be implemented in a wide range of detailed characteristic monitoring system designs. Although embodiments of the present invention are primarily described in the context of glucose monitors used in the treatment of diabetes, the embodiments of the invention are applicable to a wide variety of patient treatment programs where a physiological characteristic is periodically monitored to use in estimating the responsive treatment. For example, embodiments of the invention can be used to determine the status and/or levels of a variety of characteristics including those associated with agents such as hormones, cholesterol, medication concentrations, pH, oxygen saturation, viral loads (e.g., HIV), or the like. As is known in the art, a sensor for the characteristic monitor can be implanted in and/or through subcutaneous, dermal, sub-dermal, inter-peritoneal or peritoneal tissue. Such sensors typically communicate a signal from the sensor set to the characteristic monitor. [0049] General embodiments of the invention include a physiological characteristic monitor coupled to a sensor set. In preferred embodiments, the sensor set and monitor are for determining glucose levels in the blood and/or body fluids of the user without the use of, or necessity of, a wire or cable connection between the transmitter and the monitor. [0050] Embodiments of the characteristic monitor system of the invention are primarily adapted for use in subcutaneous human tissue. Alternatively, embodiments of the invention can be placed in a variety of other types of physiological milieus, such as muscle, lymph, organ tissue, veins, arteries or the like, as well as being used in related environments such as animal tissue. Embodiments of the invention can provide sensor readings on an intermittent, near-continuous or continuous basis. [0051] Embodiments of the invention include sensing and advanced predictive functions of the monitor which are designed to anticipate unsafe conditions for a user before they occur. In addition, predictive functions can be employed so that a user can obtain feedback to obtain a desired physical objective, such as maximizing athletic performance. Other functions of the monitor include multiple programmable alarms and reminders and diagnostic functions. Advanced alarm functions also include an alarm repeat delay function and a snooze function that can be set by a user. Embodiments of the invention can include advanced display tools to facilitate easy and quick interpretation of information related to the user's condition, including a display function for an alarm history as well as a history of measurements. [0052] 2. Glucose Monitor [0053] FIG. 1 A is a block diagram of a characteristic monitoring system 100 in accordance with an embodiment of the present invention. The characteristic monitoring system 100 generally includes a sensor set 102 that employs a sensor that produces a signal that corresponds to a measured characteristic of the user, such as a blood glucose level. The sensor set 102 communicates these signals to a characteristic monitor 104 that is designed to interpret these signals to produce a characteristic reading or value for the user, i.e. a measurement of the characteristic. The sensor signals enter the monitor 104 through a sensor input 106 and through the sensor input 106 the signals are conveyed to a processor 108. The processor 108 determines and manipulates the sensor readings within the monitor 104. In addition, but not limited to, the characteristic monitor 104 provides additional functions that will aid in the treatment regime to which the characteristic reading applies. For example, but not limited to, the monitor may track meals, exercise and other activities which affect the treatment of diabetes. These additional functions can be combined with or independent from the characteristic readings determined by the monitor 104. [0054] Other components of the monitor 104 support the processor 108 in performing functions. A memory 110 is used to store data and instructions used by the processor 108. A data entry device 112 such as a keypad is used to receive direct input from the user and a display 114 such as a liquid crystal display (LCD), or the like, is used to relate information to the user. In addition, the monitor 104 includes a data port 116, such as a digital input/output (I/O) port. [0055] The data port 116 can be used for the monitor 104 to communicate with a computer 118. To facilitate communication, the monitor 104 may interface with the computer 118 through a communication station 120 that can serve as a docking station for the monitor 104, for example. In some embodiments, the data port 116 within the monitor 104 can be directly connected to the computer 118. Through the communication link, data may be downloaded from the monitor 104, such as stored characteristic readings, settings, programs and other information related to the monitor's function. Thus, advanced analysis can be performed on the computer 118, freeing memory 110 within the monitor 104. Data such as characteristic readings, settings and programs can also be downloaded to the monitor 104. In this way, the monitor 104 can be conveniently reprogrammed without requiring tedious manual entry by the user. [0056] FIG. 1B is a block diagram of a telemetered characteristic monitoring system embodiment of the invention. In this system embodiment 200, the sensor input 106 of the monitor 104 is a wireless receiver, such as a radio frequency (RF) receiver. The sensor set 102 provides a signal via wired link to a telemetered monitor transmitter 202, where the signal is interpreted and converted to an RF signal. The wireless receiver sensor input 106 of the monitor 104 converts the signal to data understandable to the monitor processor. With some advantages, the telemetered characteristic monitoring system can perform any or all the functions of the characteristic monitoring system of FIG. 1A. [0057] A characteristic monitoring system 100, in accordance with a preferred embodiment of the present invention, includes a sensor set 102 and characteristic monitor device 104. The sensor set 102 generally utilizes an electrode-type sensor. However, in alternative embodiments, the system can use other types of sensors, such as electrically based sensors, chemically based sensors, optically based sensors, or the like. In further alternative embodiments, the sensors can be of a type that is used on the external surface of the skin or placed below the skin layer of the user. Preferred embodiments of a surface mounted sensor utilize interstitial fluid harvested from underneath the skin. The sensor set 102 is connected to the monitor device 104 and provides a signal based upon the monitored characteristic (e.g., blood glucose). The characteristic monitor device 104 utilizes the received signal to determine the characteristic reading or value (e.g., a blood glucose level). In still other embodiments, the sensor may be placed in other parts of the body, such as, but not limited to, subcutaneous, dermal, sub-dermal, inter-peritoneal or peritoneal tissue [0058] The telemetered characteristic monitor transmitter 202 generally includes the capability to transmit data. In alternative embodiments, the telemetered characteristic monitor transmitter 202 can include a receiver, or the like, to facilitate two-way communication between the sensor set 102 and the characteristic monitor 104. In alternative embodiments, the characteristic monitor 104 can be replaced with a data receiver, storage and/or transmitting device for later processing of the transmitted data or programming of the telemetered characteristic monitor transmitter 202. In addition, a relay or repeater (not shown) can be used with a telemetered characteristic monitor transmitter 202 and a characteristic monitor 104 to increase the distance that the telemetered characteristic monitor transmitter 202 can be used with the characteristic monitor 104. For example, the relay can be used to provide information to parents of children using the telemetered characteristic monitor transmitter 202 and the sensor set 102 from a distance. The information can be used when children are in another room during sleep or doing activities in a location remote from the parents. In further embodiments, the relay can include the capability to sound an alarm. In addition, the relay can be capable of providing telemetered characteristic monitor transmitter 202 data from the sensor set 102, as well as other data, to a remotely located individual via a modem connected to the relay for display on a monitor, pager or the like. The data can also be downloaded through the communication station 120 to a remotely located computer 118 such as a PC, laptop, or the like, over communication lines, by modem or wireless connection. As disclosed herein, some embodiments of the invention can omit the communication station 120 and use a direct modem or wireless connection to the computer 118. In further embodiments, the telemetered characteristic monitor transmitter 202 transmits to an RF programmer, which acts as a relay, or shuttle, for data transmission between the sensor set 102 and a PC, laptop, communication station 118, a data processor, or the like. In further alternatives, the telemetered characteristic monitor transmitter 202 can transmit an alarm to a remotely located device, such as a communication station 118, modem or the like to summon help. [0059] In addition, further embodiments can include the capability for simultaneous monitoring of multiple sensors and/or include a sensor for multiple measurements. [0060] A purpose of the characteristic monitoring system 100 is to provide for better treatment and control in an outpatient or a home use environment. For example, the monitoring systems 100, 200 can provide indications of glucose levels, a hypoglycemia/hyperglycemia alarm and outpatient diagnostics. Embodiments of the invention are also useful as an evaluation tool under a physician's supervision. [0061] The characteristic monitor device 104 receives characteristic information, such as glucose data or the like, from the sensor set 102 and displays and/or logs the received glucose readings. Logged data can be downloaded from the characteristic monitor 104 to a PC, laptop, or the like, for detailed data analysis. In further embodiments, the characteristic monitoring system 100, 200 can be used in a hospital environment, or the like. Still further embodiments of the present invention can include one or more buttons to record data and events for later analysis, correlation, or the like. Further buttons can include a sensor on/off button to conserve power and to assist in initializing the sensor set 102. The characteristic monitoring system 200 can also be employed with other medical devices to combine other patient data through a common data network system. [0062] Further embodiments of the sensor set 102 can monitor the temperature of the sensor set 102, which can then be used to improve the calibration of the sensor. For example, for a glucose sensor, the enzyme reaction activity may have a known temperature coefficient. The relationship between temperature and enzyme activity can be used to adjust the sensor values to more accurately reflect the actual characteristic levels. In addition to temperature measurements, the oxygen saturation level can be determined by measuring signals from the various electrodes of the sensor set 102. Once obtained, the oxygen saturation level can be used in calibration of the sensor set 102 due to changes in the oxygen saturation levels and its effects on the chemical reactions in the sensor set 102. For example, as the oxygen level goes lower, the sensor sensitivity can be lowered. In alternative embodiments, temperature measurements can be used in conjunction with other readings to determine the required sensor calibration. [0063] In preferred embodiments, the sensor set 102 facilitates accurate placement of a flexible thin film electrochemical sensor of the type used for monitoring specific blood parameters representative of a user's condition. Preferably, the sensor monitors glucose levels in the body, and can be used in conjunction with automated or semi-automated medication infusion devices 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 (which are incorporated herein by reference), to control delivery of insulin to a diabetic patient. [0064] Embodiments of the flexible electrochemical sensor can be 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 at a tip end of the sensing portion are exposed through one of the insulative layers for direct contact with patient blood or other body fluids, when the sensing portion (or active portion) of the sensor is subcutaneously placed at an insertion site. The sensing portion is joined to a connection portion 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, can be used. 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 can be conveniently connected electrically to the monitor 104 or a telemetered characteristic monitor transmitter 202 by a connector block (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 102 are configured or formed to work with either a wired or a wireless characteristic monitoring system 100, 200. [0065] A. Glucose Monitor Status Checks [0066] The physiological characteristic monitoring system 100, 200 can perform a status check to confirm that the monitor 104 is operating properly and calibrated to take glucose measurements. The processor 108 determines the status of the monitor for receiving the signal from the sensor set 102. The monitor status is based upon at least one of a plurality of conditions including the sensor activity condition, the sensor calibration condition and the telemetry condition. The display 114 shows different observable indicators depending upon the status of the monitor 104. [0067] FIG. 2A is a flowchart 220 of an exemplary status check algorithm for a characteristic monitor embodiment of the present invention. Beginning at the default time screen 222 showing the current time, a user can press a key (e.g. the UP key) to initiate the status check. The processor 108 first performs a sensor activity condition check 224 to determine if there is an expired or dead sensor. If the sensor is determined to be dead, the display 114 shows a sensor “REPLACE” prompt 226 with the current time, which indicates that the sensor has expired and replacement of the sensor set 102 is required immediately. If the sensor is determined to be active by the sensor activity check 224, the processor 108 performs a telemetry condition check 228 to determine if the monitor 104 is synchronized with the telemetered monitor transmitter 202 coupled to the sensor set 102. If the monitor 104 and the transmitter 202 are not synchronized, a “NO SYNC” indicator 230 is shown on the display 114. If the devices are synchronized, a calibration condition check 232 is performed by the processor 108 to determine first whether a calibration of the sensor set 102 is pending (i.e., whether the monitor 104 is currently processing a previously entered blood glucose reference value, for example from a meter, to calibrate the sensor set 102). If a calibration is pending, the display 114 shows a “PENDING” indicator 234. If a calibration is not pending, the processor 108 checks whether the sensor calibration is currently valid 236. If the calibration is not valid, the display shows an “ENTER BG” indicator 242 with the current time, which indicates that a blood glucose reference value (e.g., from a blood glucose meter) is required by the monitor 104 to calibrate the sensor set 102. If the calibration is valid, the processor 108 then checks that the sensor expiration time is after the next calibration due time 238, and the display 114 shows a “BG DUE” indicator 240 with the time that the next calibration is due. If the sensor expiration time is before the next calibration due time, the display 114 shows the “REPLACE” prompt 226 with the time that the sensor will expire and replacement of the sensor set 102 will be required. [0068] B. Glucose Monitor Calibration Reference Value Entry [0069] FIG. 2B is an exemplary flowchart 250 of screens for entering a reference value to calibrate a characteristic monitoring system 100, 200 in accordance with an embodiment of the present invention. While a calibration is pending or valid as a result of entry of a calibration reference value (e.g., a blood glucose value measured by a blood glucose meter), the display 114 shows the calibration reference value and time of the most recent valid entry in the meter screen 252. In particular embodiments, the time of the most recent valid entry is unaffected by a change in a system time setting of the monitor 104. In other embodiments, the time of the most recent valid entry may be shifted in accordance with a change in a system time setting of the monitor 104. From the meter screen 252, pressing a button (e.g., the ACT/activate button) allows entry of a new calibration reference value in the entry screen 254. After entry of the new value (e.g., using the up and down arrow buttons and then pressing the ACT/activate button), the display 114 shows a confirmation screen 256, which requires confirmation of the value entered (e.g., by pressing the ACT/activate button) to release the display to the default time screen 258. [0070] 3. Dynamic Glucose Monitoring Functions [0071] Embodiments of the present invention include different types of continuous glucose monitors that identify trends in blood glucose dynamics to facilitate enhanced treatment of diabetes. In general, a first illustrative monitor can be used to anticipate a glucose “crash” (or other hypoglycemic incident) before the onset of debilitating symptoms. Another illustrative monitor can be used to detect an inadequate nocturnal basal rate and alert the patient in order to avoid an impaired fasting glucose incident. Another illustrative monitor can anticipate hyperglycemic (or hypoglycemic) incidents by detecting trends toward those levels and help the patient avoid such incidents. Another illustrative monitor can assist a patient in maximizing athletic performance in endurance type activities (e.g., a marathon race) by detecting trends toward hypoglycemic levels. [0072] The disclosed embodiments monitor the dynamics of a physiological characteristic such as blood glucose levels. These embodiments utilize this dynamic monitoring to provide functionality including the anticipation of glucose crash and alerting the patient, the detection of inadequate nocturnal basal rate, the anticipation of hyperglycemic (or hypoglycemic) incidents and maximizing athletic performance. All of these features can be implemented in software operating in the monitor's microprocessor and/or designed into an application specific integrated circuit (ASIC) or other specialized circuitry. Also, dynamic glucose monitoring functions use periodic measurements of a glucose level. [0073] A. Monitor for Anticipating a Glucose Crash [0074] In one embodiment of the invention, a monitor anticipates a glucose crash by monitoring trends in glucose levels. For example, the monitor can alert the patient when glucose levels are rapidly decreasing. By monitoring such trends or a rate information of measured glucose levels, the monitor can provide a much better warning system to alert the user with enough time to stabilize and reverse a dangerous physiological condition. [0075] In some embodiments of the invention, the monitor measures glucose more frequently than typical glucose monitoring devices. For example, one embodiment of the invention measures approximately every minute, whereas other monitors measure at a lower rate (e.g., but not limited to, once per 5 minutes). Frequent measurements are taken because of the short time intervals which are evaluated. Alternative embodiments may utilize more frequent measurements, such as, but not limited to, 10 seconds, 1 second, or the like. [0076] In an illustrative embodiment, the monitor periodically measures glucose, analyzes the present trend, determines whether a glucose crash incident is probable and appropriately alerts the patient. At some frequent interval (e.g., but not limited to, once per minute), the device measures the glucose level, applies a smoothing filter to the result, and records the filtered value. The smoothing filter may take a weighted sum of past sensor values (so called finite impulse response—FIR—filter), a weighted sum of past sensor values and past filtered values (so called infinite impulse response—IIR—filters), may use simple clipping algorithms (e.g. limit the percent change in filtered output), or employ models to predict the output (e.g. Weiner and Kalman filter designs). For example, if the most recent (filtered) value is in the “qualifying range”, the monitor can calculate the slope of a line fit to the most recent values (most likely, but not limited to, using a Saritzky gulag filter) and determine if the slope is steeper than a selected threshold rate (e.g., but not limited to, 3% or declining at more than 30 mg/dL in ten minutes). If the slope equals or exceeds the threshold rate, a glucose crash incident is likely and the monitor alerts the patient accordingly. [0077] Those skilled in the art will understand that in some embodiments the qualifying range can be a closed range (e.g., but not limited to, between 100 and 150 mg/dL) and in other embodiments the qualifying range can be an open range (e.g., but not limited to, greater than 100 mg/dL). By first identifying whether a most recent value is within the qualifying range, further calculation of the dynamic behavior of the physiologic characteristic can be avoided. Thus, the determination of a glucose crash can be unconcerned with rate magnitudes occurring when the current characteristic value is outside of the range (of course, other alarms, which merely monitor the current characteristic value, can be triggered when the reading is too high or too low). However, in alternate embodiments, the slope can be calculated and compared to the threshold rate with every new value. In further embodiments, multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a glucose crash warning. [0078] In one preferred embodiment, the monitor determines that a glucose crash is likely if three criteria are met. The criteria are as follows. The first, dG/dT (the rate of glucose level change) is negative, can be considered for example in situations where blood glucose levels are dropping (e.g., but not limited to, when a value pertaining to the rate of glucose change is negative). The second, |dG/dT| exceeds a threshold rate, can be considered in contexts, for example where a specified blood glucose change rate is exceeded for a specified sustained period (e.g., but not limited to, greater than 3% per minute for 10 minutes). The third, G, the glucose level, can be considered for example, when this value begins dropping starting within a specified range, (e.g., but not limited to, 100-150 mg/dL). [0079] In some embodiments, these criteria can be parameterized to allow the user to customize the values. The qualifying range, threshold rate and period can be general values, applied to all users, or determined from factors specific to the individual user. For example, the monitor can include a feature to adjust the qualifying glucose level range, the maximum rate of glucose change, or in some embodiments, the sustained time period length. In addition, in some embodiments, any or all of the dynamic glucose monitoring functions can enabled or disabled, selectively or together. [0080] The following control program pseudo code provides an example of a programming routine performed by the processor of the monitor to implement an embodiment of the invention. REPEAT every minute) { Measure glucose level gi Filter gi and store the filtered value g′i IF(g′i is in range 100 - 150 mg/dL) THEN Fit a line to the most recent 10 filtered (or, alternatively, unfiltered) values IF (dG/dT for that line < ( − 3% per minute ) THEN Alert the patient and record in history ENDIF ENDIF } END REPEAT [0081] FIG. 3A is a flowchart of a method for anticipating a glucose crash 300. At block 302, a characteristic level is repeatedly measured to obtain a group of characteristic level values. Following this at block 304, a smoothing filter can be applied to the group of characteristic level values to produce a filtered measurement value. The filtered measurement value is recorded at block 306. At block 308 it is determined if the recorded value falls within a qualifying range (e.g., but not limited to, between 100 to 150 mg/dL). If not, the process returns to block 302. If the recorded measurement is within the range, a slope of a line fit to a recent series of recorded filtered values is calculated at block 310. The calculated slope is compared to a threshold rate (e.g., but not limited to, −3% per minute) at block 312. If the calculated slope is not steeper than the threshold rate the process returns to block 302. If the slope exceeds the threshold rate, an anticipated glucose crash is indicated at block 314. Alternative embodiments may utilize similar logic for when the glucose level is already outside of the range and continues to drop. In addition in an alternative preferred embodiment of the invention, one can utilize a raw data measurement (e.g. a group of characteristic level values) to determine a derivative as an alternative to using a filtered measurement value to determine a derivative. [0082] B. Monitor for Detecting an Inadequate Nocturnal Basal Rate [0083] In another embodiment of the invention, the characteristic monitor can be used to detect an inadequate nocturnal basal rate. This embodiment generally applies to diabetic patients using an insulin infusion device that continually administers insulin at a patient controlled basal rate. The monitor detects an inadequate basal rate (i.e., but not limited to, “low basal rate” or a “high basal rate”), by monitoring trends in glucose levels. The monitor then alerts a patient in the early morning, when glucose levels are high and relatively steady, low and relatively stable or changing rapidly. This gives the patient time to adjust the basal rate of the infusion device upward or downward to and avoid an impaired fasting glucose incident. [0084] The monitor operates to track the characteristic level rate. For example, every 5 minutes the monitor measures and records the glucose level. Once a day (e.g., but not limited to, 3 hours before to the anticipated wakeup time), the monitor calculates the average blood glucose and the rate of blood glucose change for the previous hour. The monitor can then determine a prediction of the “morning glucose” level at wake up based upon the calculated average blood glucose and the rate of blood glucose change. In one embodiment the “morning glucose” is predicted assuming that the rate of change remains constant, however in other embodiments nonlinear characteristic curves and functions can be applied in making the prediction. If the anticipated “morning glucose” level is greater than a high threshold value (e.g., but not limited to, 126 mg/dL), or less than a low threshold value (e.g., but not limited to, 60 mg/dL), an alarm is sounded. This will allow time for the infusion device basal rate to be adjusted appropriately. In alternative embodiments, different times before anticipated wakeup, different high threshold values, or different low threshold values, may be used. [0085] In some embodiments, the triggering criteria can also be parameterized to allow the user to customize the values. In some embodiments, the user is allowed to set the values for the controlling parameters. For example, the user can set the qualifying low and high glucose levels as well as the anticipated waking time. For each of the settings a default value can be used in the absence of a user setting. For example, a default low glucose level of 60 mg/dL, a default high glucose level of 126 mg/dL and an anticipated waking time of 7:00 AM can be used. In addition, the entire function can be enabled and disabled. [0086] FIG. 3B is a flowchart of a method for detecting an inadequate nocturnal basal rate 320. At block 322, the method begins by measuring a characteristic level to obtain a measurement value. The value is recorded at block 324. Measuring and recording is repeated periodically to obtain a series of values at block 326. At block 328, the average of the series of values is calculated. At block 330, a slope of a line fit to the series of values is calculated. The calculated slope and average of the series of values are then used to determine a predictive curve at block 332. At block 334, the curve is extrapolated to predict a glucose level at wakeup. Those skilled in the art understand that such calculations are not limited to slope y=mx+b, and that, in this context, one can use alternative filtered arrangements as are known in the art. The extrapolation is performed some time before wakeup (e.g., but not limited to, 3 hours prior) to provide enough time to correct any impending negative condition. The predicted glucose level is compared to an acceptable range at block 336. If the predicted glucose value falls within the range, the process ends. If the predicted glucose value falls outside the range, a morning glucose incident is reported at block 338. [0087] C. Monitor for Anticipating Hyperglycemic Incidents [0088] In another embodiment of the invention, a glucose monitor anticipates a hyperglycemic (or hypoglycemic) incident by monitoring trends in glucose levels. The monitor alerts the patient when a “relatively steady increase” (or decrease) in glucose levels occurs. The monitor periodically measures glucose, analyzes the present trend, determines whether a hyperglycemic (or hypoglycemic) incident is probable and appropriately alerts the patient. [0089] In one embodiment, the device measures glucose values at a specific time interval (e.g. once every minute), and then, e.g. at 5 minute intervals, applies a smoothing filter to this group of values and records the filtered value. If the most recent (filtered) value exceeds a threshold value (e.g., but not limited to, 180 mg/dL), the monitor calculates the slope of a line fit to a recent series of recorded values (for example, but not limited to, six values). If the slope is greater than a threshold rate (e.g., but not limited to, 3% per minute), a hyperglycemic incident is likely and the monitor alerts the patient. For hypoglycemic incidents, values and thresholds corresponding to low glucose levels would be used. [0090] The threshold value is applied in a similar manner to the “qualifying range” applied in determining a glucose crash previously discussed. The threshold value effectively operates as an open range (e.g., but not limited to, greater than 180 mg/dL). In other embodiments, the threshold value can be a closed range. Therefore, determining a hyperglycemic incident can be unconcerned with values below the threshold value (as determining a hypoglycemic incident can be unconcerned with values above a threshold value). In one embodiment, a slope calculation can be avoided if the current reading is outside the range. However, in alternate embodiments, the slope can be calculated and compared to the threshold rate with every new reading. In further embodiments, multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a hyperglycemic (or hypoglycemic) incident warning. [0091] Here again, in some embodiments the criteria can be parameterized to allow the user to customize the controlling values for anticipating hyperglycemic (or hypoglycemic) incidents. For example, some embodiments can allow the user to set the glucose threshold level and/or the threshold rate. Embodiments of the invention can also use default parameters if no user settings are provided (e.g., but not limited to, a threshold level of 180 mg/dL and a maximal rate of 3% per minute). Embodiments of the invention can also enable and disable this function. [0092] FIG. 3C is a flowchart of a method for anticipating a hyperglycemic incident 350. The method begins at block 352 by repeatedly measuring a characteristic level to obtain a group of values. At block 354, a smoothing filter is applied to the group of values to obtain a filtered measurement value. The filtered value is recorded at block 356. The recorded value is compared to a threshold value at block 358. If the recorded value does not exceed the threshold value (e.g., but not limited to, 180 mg/dL), the process returns to block 352. If the recorded value does exceed the threshold value, a slope of a line fit to a recent series of values is calculated at block 354. The calculated slope is compared to a threshold rate (e.g., but not limited to, +3% per minute) at block 362. If the slope is not steeper than the threshold rate, the process returns to block 352. If the slope is steeper than the threshold rate, an anticipated hyperglycemic incident is reported at block 364. For hypoglycemic incidents, corresponding steps for low glucose levels would be used. As noted previously, estimates of dG/dt may be calculated by a variety of methods known in the art including the slope (and that such calculations are not limited to, for example, determinations based on y=mx+b). [0093] D. Monitor for Maximizing Athletic Performance [0094] Dynamic monitoring can also be used to provide feedback based upon the engaged activity of the user. For example, the monitor can be used to maximize performance during an endurance type activity (e.g., but not limited to, a marathon race). The endurance athlete strives to burn glucose rather than fat and accordingly needs to anticipate low glucose levels and ingest carbohydrates early enough to avoid low glucose levels. [0095] In such embodiments, the monitor anticipates low glucose levels and alerts the athlete to ingest carbohydrates. It is important to note that this embodiment is not strictly anticipating hypoglycemic incidents. Instead it is anticipating low glucose levels where it would otherwise be too late for the athlete to compensate by ingesting carbohydrates and still perform effectively and/or at full capacity. [0096] In one embodiment, once a minute, the device measures a glucose level, applies a smoothing filter and records the filtered value at 5-minute intervals. If the most recent recorded (i.e., filtered) value is in a qualifying range (e.g., but not limited to, 60-140 mg/dL), the processor calculates the slope of a line fit to the most recent six filtered values and determines if the slope is steeper than −1% (i.e., but not limited to, 30 mg/dL in 30 minutes). If the rate of decline exceeds this threshold, a low glucose level is likely and the monitor alerts the athlete accordingly. Thus, for example, but not limited to, to trigger an alarm, the glucose level rate, dG/dT, is negative with a magnitude greater than 1% per minute for 30 minutes beginning in range 60-140 mg/dL. [0097] Similar to the glucose crash monitor, in embodiments for maximizing athletic performance, the qualifying range can be a closed range (e.g., but not limited to, between 60 and 140 mg/dL) or an open range (e.g., but not limited to, less than 140 mg/dL). By first identifying whether a most recent value is within the qualifying range, further calculation of the dynamic behavior of the physiologic characteristic is avoided. However, other alarms which merely monitor the current characteristic value can be triggered when the reading is too high or too low. In alternate embodiments, the slope can be calculated and compared to the threshold rate with every new value. In further embodiments, multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a low glucose warning. [0098] Here too, these criteria can be parameterized to allow the user to customize the values. Typically, the monitor will allow a user to set the qualifying glucose range and/or enable and disable the function. A default qualifying range (e.g., but not limited to, 60-140 mg/dL) can be used. [0099] FIG. 3D is a flowchart of a method for maximizing athletic performance 370. The process begins at block 372, where a characteristic level is repeatedly measured to obtain a group of characteristic level values. Following this at block 374, a smoothing filter can be applied to the group of characteristic level values to produce a filtered measurement value. The filtered measurement value is recorded at block 376. At block 378 it is determined if the recorded value falls within a qualifying range (e.g., but not limited to, between 60 to 140 mg/dL). If not, the process returns to block 372. If the recorded measurement is within the range, a slope of a line fitted to a recent series of recorded filtered values is calculated at block 380. The calculated slope is compared to a threshold rate (e.g., but not limited to, −1% per minute) at block 382. If the calculated slope is not steeper than the threshold rate the process returns to block 372. If the slope exceeds the threshold rate, an anticipated low glucose level is indicated at block 384. As noted previously, estimates of dG/dt may be calculated by slope as well as other methods known in the art. [0100] 4. Glucose Alarm Functions [0101] Embodiments of the invention can utilize various advanced alarm functions. For example, in some embodiments multiple alarms can be independently set by the user. In further embodiments, user input can direct review of the alarm history and also alter the alarm display to suit the user's preference. Alarm settings for embodiments of the invention can also include an alarm snooze or “blackout” period as well as an alarm repeat delay. [0102] A. Multiple Glucose Alarm Functions [0103] Embodiments of the invention can employ multiple alarms that can be independently set by the user. For example, a continuous glucose monitoring system can have multiple alarms for different glucose values. The system can allow a user to set threshold glucose values that define a “narrow” glucose range (as compared to the ordinary alarm limits). If the user's glucose level passes outside the “narrow” range, an alarm can sound. This alarm alerts the user to monitor his glucose levels more closely. The system can sound a second alarm (preferably having a sound distinguishable from the first “narrow” range alarm) in the event the user's glucose level reaches a more dangerous condition requiring immediate action. Alarm indications may be audible, tactile, vibratory, visual, combinations of alarm indications, or the like. In the case of visual alarm indications, but not limited to, green lights can be displayed while the user's glucose level remains within the defined “narrow” range; yellow for the first alarm level; and red for the second alarm level. The visual alarm indications may flash and/or also be combined with other alarm indications. [0104] Although the above example describes a two-layer alarm system, further embodiments of the invention can incorporate multiple alarm layers. In addition, the alarms can be set in ranges, or separate high and low glucose level alarms can be set. Distinctive sounds can be used for each alarm. For example, each successive high glucose level alarm can have, but is not limited to having, a higher pitch. Successive low glucose level alarms can each have, but are not limited to having, lowering pitches. Alternately, intermittent or wavering volumes that also increase in pitch according to the severity of the condition can be used. In still other embodiments, the user can select or program alarm tones and other sounds and assign them to the various alarms. Also, in some embodiments, these distinguishable alarms can also be set at different volume levels. In addition, as discussed above, the alarms are not limited to audible signals; some embodiments of the invention can also utilize visual alarms, such as flashing lights or displays, or tactile alarms, such as vibrating indicators. [0105] In still further embodiments, threshold values and associated alarms can be set according to a schedule. For example, but not limited to, particular alarms can be set to be active only during selected portions of the day. [0106] FIG. 4A illustrates a multiple alarm function of the invention. A plot of the monitored characteristic value 400 (e.g., blood glucose) changing over time is shown. A typical wide alarm range 402 is defined by an upper threshold value 404 and a lower threshold value 406. If the monitored characteristic value 400 should exceed the defined range and cross either threshold, an alarm is initiated to indicate to the user to check his blood glucose. In one embodiment, a distinctive alarm can be associated with the alarm range 402. Thus, the same alarm is produced whether the range 402 is exceeded by passing the upper threshold value 404 or the lower threshold value 406. In other embodiments, distinctive alarms can be assigned to each threshold value 404, 406. In further embodiments of the invention, other alarm ranges can also be set. For example, a second narrower range 408 can be set with a lower upper threshold value 410 than that of the wider range 402; and a higher lower threshold value 412 than that of the wider range 402. As with the wider range 402, an alarm is initiated if the narrower range is exceeded by the monitored characteristic value 400. Here also, alarms can be the same or different for each threshold value 410, 412. [0107] The ability to set different ranges and associated alarms allows the monitor to immediately convey some information about the condition of the user even before checking the actual readings. Particularly, using the narrower range 408 and associated alarms allows the user to know of a negative trend that does not require the same urgency as an alarm triggered by the wider range 402. In effect, the user is able to set multiple alarms, each indicating a different level of urgency and/or different conditions. In some embodiments, threshold values for alarms can also be set independent from ranges. [0108] Instill further embodiments, alarms or indicators can be set according to the direction in which a threshold value is crossed by the monitored characteristic value 400. For example, as the monitored characteristic value 400 crosses a lower threshold value 412 from the narrow range (e.g., but not limited to, at point 414), one type of alarm can be provided. However, when the monitored characteristic value 400 crosses a lower threshold value 412 from the wider range 402 (e.g., but not limited to, at point 416), another type of alarm can be provided. The difference in the alarms is appropriate because only the former case indicates a worsening of the user's condition. In the latter case, the transition actually indicates an improvement in the user's condition. Thus, in some embodiments of the invention, alarms will only be given when crossing a threshold indicates a worsening of the user's condition. In other embodiments, an indicator will also be given when a threshold has been crossed in an improving direction. In these cases, either the same indicator (sound, light, display or other) or different indicators can be used. In a similar manner, reminders can be set to indicate to a user various conditions (not necessarily negative) that will aid in convenient therapy management. [0109] The multiple alarm function of the invention can be readily incorporated with any of the individual alarm functions and settings such as discussed hereafter. [0110] B. Individual Alarm Functions and Settings [0111] In further embodiments of the invention, a physiological characteristic monitor can incorporate various individual alarm functions and settings to enhance convenient operation by a user. As typical of the monitoring system 100, 200 shown in FIGS. 1A and 1B, the monitor includes a sensor input capable of receiving a signal from a sensor, the signal being based on a sensed physiological characteristic value of a user, and a processor for operating an alarm based on user input from an input device. The alarm indicates an alarm condition where the sensed physiological characteristic value exceeds a set range. In preferred embodiments of the invention, the physiological characteristic value is a measurement related to a blood glucose level in the user and the alarm indicates a glycemic condition. Operating the alarm comprises setting parameters of the alarm based on the user input from the input device. For example, the blood glucose level or value that will activate a hypoglycemia or hyperglycemia alarm may be set by the user utilizing the input device. The hypoglycemia alarm may be set to trigger if the user's blood glucose level is less than or equal to 60, 65, or 70 mg/dl (or any other desired level), and the hyperglycemia alarm may be set to trigger if the user's blood glucose level is greater than or equal to 150, 160, or 175 mg/dl (or any other desired level). [0112] FIGS. 4B and 4C illustrate the hypoglycemia and hyperglycemia alarm screens, respectively. In each case, the display shows the measurement of the concentration of blood glucose indicating the glycemic condition, preferably until the alarm is acknowledged by the user. Furthermore, the display shows a time of the alarm. In particular embodiments, the alarm indicates the glycemic condition only if the monitor is calibrated, although in alternative embodiments, the alarm may indicate the glycemic condition regardless if the monitor is calibrated. [0113] In the illustrated embodiment, the display shows a LOW indicator when the measurement of the concentration of blood glucose is below a specified level for a hypoglycemia alarm, such as 60 mg/dl. Similarly, the display shows a HIGH indicator when the measurement of the concentration of blood glucose is above a specified level for a hyperglycemia alarm, such as 150 mg/dl. In some embodiments, alarm indications may be other visual indicators (e.g., lights, flashing displays, or the like), audible, tactile, and/or vibratory. For example, a hypoglycemia alarm can be indicated by at least two audible descending tones, and a hyperglycemia alarm can be indicated by at least two audible ascending tones. [0114] In further embodiments of the invention, an alarm repeat delay period is employed. Subsequent alarms are prevented for the alarm repeat delay period after the measurement of the concentration of blood glucose first indicates a glycemic condition. For example, the alarm repeat delay period can be less than 20 minutes (e.g. approximately 17.5 minutes) for the glycemic condition comprising a hypoglycemic condition. In another example, the alarm repeat delay period is less than 1 hour (e.g. approximately 52.5 minutes) for the glycemic condition comprising a hyperglycemic condition. In alternative embodiments, the alarm repeat delay period may be other time periods, such as 10 minutes, 15 minutes, 30 minutes, 1� hours, 2 hours, or the like. [0115] In particular embodiments, the level of the measurement of the concentration of blood glucose from the sensor that will trigger a low limit (or hypoglycemia) alarm or a high limit (or hyperglycemia) alarm can be set based upon input from the user. Particularly, these two alarm levels can be separately set. FIGS. 4D and 4E show exemplary hypoglycemia and hyperglycemia alarm setting algorithms, respectively. FIG. 4D shows an exemplary hypoglycemia alarm setting flowchart 420. To begin setting the hypoglycemia alarm, from the hypoglycemia alarm setting screen 422, the ACT/activate button is pressed, and the hypoglycemia alarm activation screen 424 is entered. From this screen 424, the user can select setting the hypoglycemia alarm on, off or entering the alarm repeat setting function menu. If the user sets the hypoglycemia alarm off and presses the ACT/activate button, an alarm off confirmation screen 426 is presented. If the hypoglycemia alarm is set on and the ACT/activate button is pressed, the low limit entry screen 428 is presented. The low limit entry screen 428 allows the user to scroll through low limit alarm level settings using up and down arrow buttons to specify that the hypoglycemia alarm will trigger if the user's blood glucose level is less than or equal to 60, 65, or 70 mg/dl, or any other desired level. After setting the low limit alarm level, pressing the ACT/activate button again presents a hypoglycemia low limit alarm level confirmation screen 430 for confirming the specified hypoglycemic blood glucose level. [0116] From the hypoglycemia alarm activation screen 424, if the alarm repeat setting function is selected, the alarm repeat display screen 432 is entered, which allows the user to set a period for delaying a repeated check of the hypoglycemia alarm condition. The current alarm repeat delay period is shown in the alarm repeat display screen 432. Pressing the ACT/activate button allows the user to enter the repeat time select screen 434. Alternatively, the alarm repeat display screen 432 may be omitted, and the repeat time select screen 434 is entered once the alarm repeat setting function is selected. In the repeat time select screen 434, the alarm repeat delay period blinks while being set by the user utilizing the input device. The user can scroll through a list of delay increments and select the desired alarm repeat delay period from the list of delay increments. The alarm repeat delay period has a default value of 20 minutes for the hypoglycemia (low limit) alarm level. For convenience, the scrolled list of delay increments can wrap around, beginning again when one end of the list is reached. For the low limit alarm level, the alarm repeat delay period can be selected from a group of values differing in 10 minute increments. For example, the alarm repeat delay period can be selected from 20, 30, 40, 50 and 60 minutes for the low limit alarm level. In alternative embodiments, the alarm repeat delay period may be selected from a group of values differing in other time increments, such as 5, 15, or 20 minutes, or further, may be specified using up and down arrow buttons and then pressing the ACT/activate button. After selecting the alarm repeat delay period, pressing the ACT/activate button displays the alarm repeat delay confirmation screen 436 for confirming the period selection. [0117] FIG. 4E shows an exemplary hyperglycemia alarm setting flowchart 440. From the hyperglycemia alarm setting screen 442, if the ACT/activate button is pressed, the hyperglycemia alarm activation screen 444 is entered. From this screen 444, the user can select setting the hyperglycemia alarm on, off or entering the alarm repeat setting function menu. If the user sets the hyperglycemia alarm off and presses the ACT/activate button, an alarm off confirmation screen 446 is presented. If the hyperglycemia alarm is set on and the ACT/activate button is pressed, the high limit entry screen 448 is presented. The high limit entry screen 448 allows the user to scroll through high limit alarm level settings using up and down arrow buttons to specify that the hyperglycemia alarm will trigger if the user's blood glucose level is greater than or equal to 150, 160, 170, 175, or 180 mg/dl, or any other desired level. After setting the high limit alarm level, pressing the ACT/activate button again presents a hyperglycemia high limit alarm level confirmation screen 450 for confirming the specified hyperglycemic blood glucose level. [0118] The alarm repeat delay period for the hyperglycemia alarm is set in the same manner as that for the hypoglycemia alarm described above with respect to FIG. 4D; however, the alarm repeat delay period is typically set separately for a low limit alarm level and a high limit alarm level because the desired delays are different in each case. In general, the hyperglycemia alarm repeat delay period may be longer than that of the hypoglycemia alarm. From the hyperglycemia alarm activation screen 444, if the alarm repeat setting function is selected, the alarm repeat display screen 452 is entered, which allows the user to set a period for delaying a repeated check of the hyperglycemia alarm condition. The current alarm repeat delay period is shown in the alarm repeat display screen 452. Pressing the ACT/activate button allows the user to enter the repeat time select screen 454. Alternatively, the alarm repeat display screen 452 may be omitted, and the repeat time select screen 454 is entered once the alarm repeat setting function is selected. In the repeat time select screen 454, the hyperglycemia alarm repeat delay period is selected in a manner similar to the hypoglycemia alarm repeat delay period described above with respect to FIG. 4D, and then pressing the ACT/activate button displays the alarm repeat delay confirmation screen 456 for confirming the period selection. The alarm repeat delay period can have a default value of 1 hour for the hyperglycemia (high limit) alarm level. For the high limit alarm level, the alarm repeat delay period can be selected from a group of values differing in 30 minute increments. For example, the alarm repeat delay period can be selected from 1, 1�, 2, 2� and 3 hours for the hyperglycemia alarm level. In alternative embodiments, the alarm repeat delay period may be selected from a group of values differing in other time increments, such as 15 or 20 minutes or 1 hour, or further, may be specified using up and down arrow buttons and then pressing the ACT/activate button. [0119] As noted above, the multiple alarm function of the invention can be incorporated with various specific alarm features. For example, the alarm repeat delay function can be set differently for hypoglycemic alarms and hyperglycemic alarms of different severities. If a lower threshold hyperglycemic alarm is triggered, a relatively long repeat delay may be invoked. However, if a higher threshold hyperglycemic alarm is triggered, a shorter repeat delay may be used so that the user is warned more frequently because of the severity of his condition. [0120] FIG. 4F illustrates a hyperglycemia alarm snooze setting flowchart 460. The hyperglycemia alarm snooze function sets an alarm snooze period for temporarily disabling the alarm. The snooze function is set by the user utilizing the input device. In some embodiments, the alarm snooze period is only available for a hyperglycemia alarm, although in other embodiments, the alarm snooze period may also be available for a hypoglycemia alarm. Generally, the snooze function is available only when the snooze period is running and the monitor is calibrated, although in alternative embodiments, the snooze function may be available regardless if the monitor is calibrated. Further, the alarm snooze period is preferably deactivated upon any adjustment of the hyperglycemia alarm setting described above with respect to FIG. 4E. The snooze setting flowchart 460 begins at the snooze display screen 462, which can be entered by scrolling past the default time screen 464 and the BG due screen 466. From the snooze display screen 462, pressing the ACT/activate button will produce the snooze time select screen 468. In this screen 468, a user can select the desired period for the snooze function to operate, and the alarm snooze period blinks while being set by the user utilizing the input device. The alarm snooze period can be set by the user scrolling through a list of snooze period increments and selecting the desired alarm snooze period from the list of snooze period increments. For example, the list of snooze period increments can include 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11 and 12 hours, and for convenience, the list of snooze period increments wraps around as it is scrolled by the user. In alternative embodiments, the snooze period may be selected from a list of other time increments, such as 15 or 30 minutes, or further, may be specified using up and down arrow buttons and then pressing the ACT/activate button. When the snooze function is activated, the display shows time remaining of the alarm snooze period and an indicator (e.g. an “S”) showing that the snooze function is active. [0121] It may be instructive to note that, although both the alarm repeat delay function and the alarm snooze function prevent alarms for specified periods, they are not the same. One difference between the two functions can generally be identified by how each function is initiated. The alarm repeat delay is initiated (assuming the function is activated and set by the user) in response to a first alarm. In contrast, the alarm snooze function is activated by the user directly, either by directing the monitor to snooze immediately or scheduling a snooze at a specified time. For example, a user may schedule a snooze during sleeping hours that occur at some known time. [0122] Just as with the alarm repeat delay, the multiple alarm function of the invention can also be incorporated with the alarm snooze function. For example, the snooze function can be set differently for hypoglycemic alarms and hyperglycemic alarms of different severities. The snooze function can function normally when a lower threshold hyperglycemic alarm is set (i.e. ignore the alarm). However, when a higher threshold hyperglycemic alarm is set, the snooze function may be overridden due to the severity of the user's condition. [0123] FIG. 4G illustrates glycemia alarm history review in accordance with an embodiment of the invention. Operating the alarm history review can allow a user to review a historical list of the alarms indicating a glycemic condition occurrence. The alarm history review flowchart 470 shows the alarm history is entered by pressing the ACT/activate button from the alarms menu screen 472. If no alarm history exists, a screen 474 indicating “NONE” will be displayed. However, if at least one alarm event has occurred, the entries will be displayed in a historical list 476. In one embodiment, the display shows a single glycemic alarm in the historical list at a time. The display shows a physiological characteristic value (e.g. blood glucose value) and time of the glycemic condition occurrence indicated for each alarm in the historical list. The time of the glycemic condition occurrence can also include a date of the alarm. Further, the display can show at least a portion of the time of the glycemic condition occurrence in blinking text. The historical list typically includes a limited number of stored entries. For example, the historical list can comprise the 20 most recent alarms indicating a glycemic condition occurrence. In alternative embodiments, the historical list may include more or less alarms, such as the 10, 15, 30, or 50 most recent alarms. [0124] As part of the display of the historical list, the display can show the blood glucose measurements only within a specified range. For example, the specified range can be the operational range of the sensor, such as from 40 to 400 mg/dl, although the range may span other values, such as from 20 to 600 mg/dl. When a measurement in the historical list is above the specified range, the display shows a HI indicator. Similarly, the display shows a LO indicator for the measurements below the specified range. [0125] 5. Advanced Blood Glucose Reminder Functions [0126] Another aspect of the invention allows the user to set reminders that will be provided by the monitor. The reminders can be alarm signals (including, but not limited to, auditory, visual, tactile, etc.) that are initiated after a timer has run to prompt the user to take action or merely inform the user of a particular status. The reminder is started (i.e. the timer is initiated), when an event occurs and/or certain conditions are met. The alarm signals can be the same or different based upon the triggering events or conditions. These reminders can be used to further assist the user in managing insulin delivery for optimum results. For example, but not limited to, reminders can be set for event markers, blood glucose values, reference values, high or low sensor measurements. [0127] Characteristic monitors and infusion devices can use event markers that place tags in the data for events the user experiences (e.g., but not limited to, meals, exercise, and high or low blood glucose). For example, but not limited to, when an infusion device identifies a high or low blood glucose event marker, it can start a timer that reminds the user to check blood glucose levels. This is intended to make therapy safer by encouraging more frequent checks during times that the patient may be at risk from hypoglycemia or hyperglycemia. In addition, this feature can also be applied to characteristic monitors. For example, but not limited to, a characteristic monitor that is used to show low or high blood glucose tags can have a timer set to remind a user to check their blood glucose levels at a later time. [0128] In addition, a reminder timer can be set that is triggered if a blood glucose value is entered. For example, but not limited to, the reminder can be if the user enters a low or high blood glucose value into the monitor as a reference or calibration value. [0129] A reminder timer can also be triggered by a user providing a reference value to the monitor. Thus, the user can be reminded to supply a new reference value after a minimum time period has elapsed. In this way calibration of the monitor is assured. [0130] A blood glucose reminder can also be triggered by high or low measurement from the sensor. Thus, the monitor will request a blood glucose reference value during an excursion away from the normal range of values. The trigger for this reminder can be tempered by setting a minimum time between reminders to avoid pestering the user. This reminder can be used to provide more robust data for curve fitting as correlation improves with variability in the data pairs. The reminder promotes more frequent data collection during more critical periods (e.g., but not limited to, when blood glucose is too high or too low) and therefore the interpolated curve for this period is more reliably representative of the true curve. [0131] One aspect behind the use of these reminders is that they also serve to prevent redundant and excessive alarms for the user. For example, if the timer is removed from the previously described high or low measurement reminder, the result would be a simple hypoglycemia or hyperglycemia alarm. Using a reminder, however, the message is not that the user's blood glucose is out of range. Rather, the reminder's message is to check the user's blood glucose with a meter, or the like. If a user's blood glucose is very near an alarm triggering threshold, an alarm might be triggered repeatedly as the value passes back and forth across the threshold. A reminder will set a timer, preventing duplicative warnings for a short period of time, but reminding the user to check blood glucose again when that period has expired. This can provide a better or easier path through the regulatory process. Thus, reminders are less likely to become a nuisance to the user and also prompt more useful data collection. In alternative embodiments, the alarm is triggered again, regardless of the presence of a time, if the glucose level continues to change in the direction of the trend. [0132] FIG. 5 illustrates a reminder function of the invention triggered by high or low characteristic values. A plot of a monitored characteristic value 500 (such as, but not limited to, blood glucose) is shown. One or more ranges 502, 504 define safe characteristic values (e.g., but not limited to, a first range 502 being a warning range and a second range 504 being a critical range), such as can be employed using multiple alarms as previously described. When a range is exceeded (e.g., but not limited to, at time 506), an alarm can be triggered but also a timer is started such that a reminder is also initiated after its expiration (e.g., but not limited to, at time 508). Over the timer period further occurrences of exceeding the threshold (e.g., but not limited to, at point 510) will not result in a duplicative alarm. [0133] However, the situation can be somewhat different when the intervening triggering event is not identical to the first triggering event. For example, if a first range 502 is exceeded (e.g., but not limited to, at time 512) and a timer is started, but before a reminder can be issued (e.g., but not limited to, at time 514) a second range 504 is exceeded (e.g., but not limited to, at time 516), then the second alarm will be issued and the timer will be restarted. No reminder will be indicated at the theoretical expiration of the first timer (e.g., but not limited to, at time 514), but a reminder will be issued at the expiration of the second timer (e.g., but not limited to, at time 518). In this case, exceeding the second range overrides the first reminder because the second alarm is a different, albeit related, condition. As previously described, however, the use of reminders is not limited to monitoring high and low characteristic values. In a similar manner, reminders can be triggered by user's supplied reference values for calibration as well as event markers entered into the monitor. [0134] 6. Glucose Monitoring Information Management [0135] Another aspect of the invention is to provide meaningful retrospective information to the patient using the sensor. In particular, a retrospective display of one or more physiological values can provide significantly useful data. As disclosed, the retrospective displays can be designed in a variety of ways to provide various useful information. For example, but not limited to, as the sleeping user receives no benefit from a real-time display, a retrospective view of data is important. While a simple listing of previous values has value, it can be time consuming to review, provides information that is difficult to visualize and comprehend and requires significant memory space within the device. Providing useful information that is easy to understand and that can be stored within a small memory space is very important. The ability to review data from the previous sleep period is particularly helpful to a user with nocturnal hypoglycemia or “dawn effect”, as there is typically no witness to the real-time display. These measures can be even more important in cases where the alarm system can exhibit many false positives and/or false negatives, which might otherwise frustrate the user and lead to non-use of the monitor. [0136] The following advanced data presentation tools can be used to conveniently and efficiently store and display useful information on a screen for a user to review while the monitor is in use. The tools provide useful information while requiring only a minimal amount memory space. These data presentation tools can also be used in any retrospective analysis package, such as software running on a computer or network designed to analyze trends and provide advise regarding a treatment regime. [0137] The tools operate by processing that compares actual reading to high and low value limits (e.g., but not limited to, acceptable blood glucose ranges). For example, but not limited to, the limits can be the adjustable hypoglycemic and hyperglycemic alarm thresholds of a monitor. Alternately, for standardization, the tools can be applied to a fixed definition of a target blood glucose range that is independent of the hyperglycemic and hypoglycemic alarm thresholds for the particular user/monitor. [0138] FIG. 6A illustrates one minimum and maximum data presentation. A display of the minimum and maximum values 600 of the characteristic monitor that have been measured for the user can be displayed on the monitor. The minimum value and maximum values can be conveniently displayed along with the date and time of their occurrence. Such a display 600 is useful, but becomes more useful when combined with an excursion count, a distribution of values, and/or integrated values as discussed below [0139] FIG. 6B illustrates an excursion data presentation. The number of excursions above or below the respective blood glucose limits is also very useful to have summarized for the user. An excursion display 602 provides good information, particularly when there are no alarms active on the monitor (either because the monitor is not turned on or alarms are not being employed by the user). A display 602 of the number of excursions above the hyperglycemic limit and the number of excursions below hypoglycemic limit give the user an idea of performance of a treatment program at a glance. A high number of incidents exceeding either limit indicate a need for improvements. [0140] FIG. 6C illustrates a characteristic value distribution data presentation. A simple distribution of sensor values offers a very powerful tool. In a preferred embodiment, the distribution is described in percentages that are automatically scaled with the duration of monitor use. Optionally, a monitor can include the total time of use with a percentage distribution. Awareness of a total time provides perspective for reviewing the percentage distribution. A time based distribution can also be used, but requires the total time to be included in the analysis as a reference. A distribution can also be presented based upon the total number of readings, but requires the total time is required in the analysis. [0141] For example, but not limited to, the display can show a percentage of readings above a hyperglycemic alarm level, a percentage of readings below a hypoglycemic alarm level and a percentage of readings of readings within alarm range as shown in FIG. 6C. Optionally, the total time covered in the analysis can also be displayed. Similarly, an alternate display can show the time spent above a hyperglycemic alarm level, the time spent below a hypoglycemic alarm level and the time spent within alarm range (not shown). As mentioned, the time base display requires a known total time as part of the analysis. Finally, a display can also include the number of readings above hyperglycemic alarm level, the number of readings below a hypoglycemic alarm level and the number of readings within alarm range (not shown). [0142] FIG. 6D illustrates an integrated characteristic value data presentation. Performing an integration of the readings outside the alarm levels with respect to time can provide a measure of the hypoglycemic and hyperglycemic events' severity. In addition, these results can also be scaled these by a total sensor time to provide a measure that is duration independent. [0143] For example, a “hyperglycemic area” can be calculated as the sum of the differences between the readings and the hyperglycemic alarm limit. A “hypoglycemic area” can be calculated from the sum of all the differences between the hypoglycemic alarm limit and the readings. A “hyperglycemic index” is calculated by taking the “hyperglycemic area” and dividing it by the duration of sensor use. Similarly, the “hypoglycemic index” can be calculated by taking the “hypoglycemic area” divided by the duration of sensor use. [0144] Various alarms and/or monitoring aspects discussed above may be combined or utilized with other alarms and/or monitoring aspects. The possible embodiments and/or combinations should not be limited to the specific embodiments described above. [0145] 7. Real-Time Glucose Display and History [0146] In other embodiments of the invention, a physiological characteristic monitor 104 is used for reviewing a history of measurements of the sensed characteristic value based on user input from an input device with a display for showing the history of the measurements of the sensed characteristic value. As discussed above with respect to the alarm history, the display may show the measurements only within a specified range, such as the operational range of the sensor (e.g. 40 to 400 or 20 to 600 mg/dl). Outside the specified range, a HI or LO indicator is shown. [0147] FIG. 7 illustrates the real-time and history display 700 of an embodiment of the invention. Three exemplary screens 702, 704, 706 are shown for the display of real-time or historical measurement data. The in-range screen 702 is used when the measurement is within the specified range; the actual measurement is shown. The high screen 704 (showing a HI indicator) is used when the measurement is above the specified range, and the low screen 706 (showing a LO indicator) is used when the measurement is below the specified range. The display shows a no measurement indicator where no value was recorded in the history. [0148] The user input also directs scrolling through a history of the measurements of the sensed characteristic value. In a typical embodiment, the display shows a single measurement at a time. The display shows a time of acquisition by the sensor for each measurement in the history. In the example in-range screen 702, the current measurement is being shown, indicated by the “NOW” indicator. The time of acquisition can be shown as a value relative to a most recent measurement of the history. For example, the high and low screens 704, 706 each show values measured 5 hours and 25 minutes before the current time interval. Alternatively, the actual date and time of the measurement may be shown. [0149] The history of the measurements of the sensed characteristic value can be scrolled through in even time increments. In further embodiments, the even time increment can have a selectable size (e.g. selectable between 5 minute or 30 minute increments), and the selected time increment can be indicated on the display as the history is reviewed. The history itself can comprise a fixed total period from the present backward. For convenience, scrolling through the history wraps around after an end of the history is reached. [0150] In further embodiments of the invention, when no measurement is currently available, the NOW indicator can be replaced by a status message indicating no calibration, noise or a missed measurement. [0151] This concludes the description including the preferred embodiments of the present invention. The foregoing description including the preferred embodiment of the invention has been presented for the purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise form disclosed. Many equivalent modifications and variations are possible in light of the above teaching. [0152] It is intended that the scope of the invention be limited not by this detailed description, but rather by the claims appended hereto. The above specification, examples and information provide a description of the manufacture and use of the apparatus and method of the invention. Since many embodiments of the invention can be made without departing from the scope of the invention, the invention resides in the claims hereinafter appended. Throughout this application, various publications are referenced. The disclosures of these publications are hereby incorporated by reference herein in their entireties. Patent CitationsCited PatentFiling datePublication dateApplicantTitleUS566063 *Feb 8, 1893Aug 18, 1896 Thomas curleyUS3701345 *Sep 29, 1970Oct 31, 1972Medrad IncAngiographic injector equipmentUS4385272 *Dec 24, 1980May 24, 1983Whitehead Gary JCable checker utilizing logic circuitryUS4498479 *Jun 24, 1982Feb 12, 1985Kone OyElectrocardiograph (ECG) electrode testing systemUS4510346 *Sep 30, 1983Apr 9, 1985At&T Bell LaboratoriesShielded cableUS4562751 *Jan 6, 1984Jan 7, 1986Nason Clyde KSolenoid drive apparatus for an external infusion pumpUS4573994 *Dec 7, 1981Mar 4, 1986The Johns Hopkins UniversityRefillable medication infusion apparatusUS4619646 *Jan 22, 1985Oct 28, 1986Fernandez Tresguerres HernandeDevice for the delivery-dosing of injectable productsUS4676568 *Feb 21, 1986Jun 30, 1987Adc Telecommunications, Inc.Terminal test plugUS4678406 *Apr 25, 1986Jul 7, 1987Frick CompanyVariable volume ratio screw compressor with step controlUS4685903 *Jan 6, 1984Aug 11, 1987Pacesetter Infusion, Ltd.External infusion pump apparatusUS4731726 *May 19, 1986Mar 15, 1988Healthware CorporationPatient-operated glucose monitor and diabetes management systemUS4747824 *May 30, 1986May 31, 1988Spinello Ronald PHypodermic anesthetic injection methodUS4760730 *Jul 14, 1987Aug 2, 1988Medex, Inc.Calibration system for blood pressure transducerUS4857857 *Nov 23, 1988Aug 15, 1989The Research Foundation Of State University Of New YorkElectrode catheter testing deviceUS5080653 *Apr 16, 1990Jan 14, 1992Pacesetter Infusion, Ltd.Infusion pump with dual position syringe locatorUS5097122 *Apr 16, 1990Mar 17, 1992Pacesetter Infusion, Ltd.Medication infusion system having optical motion sensor to detect drive mechanism malfunctionUS5124661 *Jul 23, 1990Jun 23, 1992I-Stat CorporationReusable test unit for simulating electrochemical sensor signals for quality assurance of portable blood analyzer instrumentsUS5219099 *Sep 6, 1991Jun 15, 1993California Institute Of TechnologyCoaxial lead screw drive syringe pumpUS5233986 *Nov 4, 1992Aug 10, 1993Random Technologies, Inc.Time domain reflectometer-integrity testing system and method for medical device electrodeUS5376070 *Sep 29, 1992Dec 27, 1994Minimed Inc.Data transfer system for an infusion pumpUS5390671 *Mar 15, 1994Feb 21, 1995Minimed Inc.Transcutaneous sensor insertion setUS5391250 *Mar 15, 1994Feb 21, 1995Minimed Inc.Method of fabricating thin film sensorsUS5414213 *Oct 5, 1993May 9, 1995Hillburn; Ralph D.Shielded electric cableUS5482473 *May 9, 1994Jan 9, 1996Minimed Inc.Flex circuit connectorUS5523534 *Jun 28, 1993Jun 4, 1996Vital Connections, Inc.Shielded carbon lead for medical electrodesUS5557210 *Apr 6, 1994Sep 17, 1996Pacesetter, Inc.Universal cable connector for temporarily connecting implantable stimulation leads and implantable stimulation devices with a non-implantable system analyzerUS5569186 *Apr 25, 1994Oct 29, 1996Minimed Inc.Closed loop infusion pump system with removable glucose sensorUS5586553 *Feb 16, 1995Dec 24, 1996Minimed Inc.Transcutaneous sensor insertion setUS5683270 *Feb 9, 1995Nov 4, 1997W.W. Fischer SaElectrical plug-type connector, particularly for medical technologyUS5781024 *Jul 26, 1996Jul 14, 1998Diametrics Medical, Inc.Instrument performance verification systemUS5792068 *Nov 24, 1993Aug 11, 1998Edentec, Inc.Medical monitor with failure protectionUS5822715 *Apr 18, 1997Oct 13, 1998Health Hero NetworkDiabetes management system and method for controlling blood glucoseUS5824959 *Oct 25, 1996Oct 20, 1998Karl Mayer Textilmachinenfabrik GmbhFlexible electrical cable and associated apparatusUS5834699 *Sep 10, 1997Nov 10, 1998The Whitaker CorporationCable with spaced helicesUS5954643 *Jun 9, 1997Sep 21, 1999Minimid Inc.Insertion set for a transcutaneous sensorUS6030346 *Apr 29, 1998Feb 29, 2000The Whitaker CorporationUltrasound imaging probe assemblyUS6113537 *Oct 15, 1997Sep 5, 2000Castano; Jaime A.Optical method and device for determining blood glucose levelsUS6117083 *Apr 30, 1998Sep 12, 2000The Whitaker CorporationUltrasound imaging probe assemblyUS6175752 *Apr 30, 1998Jan 16, 2001Therasense, Inc.Analyte monitoring device and methods of useUS6551276 *Dec 17, 1999Apr 22, 2003Medtronic Minimed, Inc.External infusion device with remote programming bolus estimator and/or vibration alarm capabilitiesUS6558351 *Jun 1, 2000May 6, 2003Medtronic Minimed, Inc.Closed loop system for controlling insulin infusionUS6893396 *May 18, 2001May 17, 2005I-Medik, Inc.Wireless internet bio-telemetry monitoring system and interfaceUS7048687 *Feb 6, 2003May 23, 2006Ob Scientific, Inc.Limited use medical probeUS20010011224 *Jan 26, 1999Aug 2, 2001Stephen James BrownModular microprocessor-based health monitoring systemUS20030211617 *May 7, 2002Nov 13, 2003International Business Machines CorporationBlood glucose meter that reminds the user to test after a hypoglycemic event* Cited by examinerReferenced byCiting PatentFiling datePublication dateApplicantTitleUS7640048 *Dec 29, 2009Dexcom, Inc.Analyte sensorUS7654956Feb 2, 2010Dexcom, Inc.Transcutaneous analyte sensorUS7715893Dec 3, 2004May 11, 2010Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS7742807 *Nov 7, 2006Jun 22, 2010Pacesetter, Inc.Musical representation of cardiac markersUS7761130Jul 20, 2010Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS7771352May 1, 2008Aug 10, 2010Dexcom, Inc.Low oxygen in vivo analyte sensorUS7775975Aug 17, 2010Dexcom, Inc.Analyte sensorUS7778680Aug 17, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS7797028Sep 14, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS7826981Nov 2, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS7831287Nov 9, 2010Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS7857760Feb 22, 2006Dec 28, 2010Dexcom, Inc.Analyte sensorUS7860544Mar 7, 2007Dec 28, 2010Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS7869853Jan 11, 2011Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS7885697Feb 8, 2011Dexcom, Inc.Transcutaneous analyte sensorUS7885699Feb 8, 2011Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS7896809Nov 3, 2008Mar 1, 2011Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS7899511Jan 17, 2006Mar 1, 2011Dexcom, Inc.Low oxygen in vivo analyte sensorUS7901354May 1, 2008Mar 8, 2011Dexcom, Inc.Low oxygen in vivo analyte sensorUS7905833Jun 21, 2005Mar 15, 2011Dexcom, Inc.Transcutaneous analyte sensorUS7914450Mar 29, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS7917186Mar 29, 2011Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS7920906Mar 9, 2006Apr 5, 2011Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS7920907Jun 7, 2007Apr 5, 2011Abbott Diabetes Care Inc.Analyte monitoring system and methodUS7925321Mar 23, 2010Apr 12, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS7927274Apr 19, 2011Dexcom, Inc.Integrated receiver for continuous analyte sensorUS7933639Apr 26, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS7935057May 3, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS7946984May 24, 2011Dexcom, Inc.Transcutaneous analyte sensorUS7949381Apr 11, 2008May 24, 2011Dexcom, Inc.Transcutaneous analyte sensorUS7955261Mar 23, 2010Jun 7, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS7959569Mar 23, 2010Jun 14, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS7976492Jul 12, 2011Dexcom, Inc.Integrated delivery device for continuous glucose sensorUS7979104Jul 12, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS7986986Mar 23, 2010Jul 26, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS7998071Oct 14, 2009Aug 16, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8000901Aug 16, 2011Dexcom, Inc.Transcutaneous analyte sensorUS8005524Aug 23, 2011Dexcom, Inc.Signal processing for continuous analyte sensorUS8005525Aug 23, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8010174Aug 22, 2003Aug 30, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8052601Nov 8, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS8060173Nov 15, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS8073519Oct 14, 2009Dec 6, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8073520Dec 6, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8092386 *Jan 10, 2012Pacesetter, Inc.Method and implantable system for blood-glucose concentration monitoringUS8115635Nov 24, 2009Feb 14, 2012Abbott Diabetes Care Inc.RF tag on test strips, test strip vials and boxesUS8128562Oct 14, 2009Mar 6, 2012Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8133178Feb 22, 2006Mar 13, 2012Dexcom, Inc.Analyte sensorUS8150488Oct 14, 2009Apr 3, 2012Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8160669Apr 17, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8160671Apr 17, 2012Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS8162829Mar 30, 2009Apr 24, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8167801May 1, 2012Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8170803May 1, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8175673Nov 9, 2009May 8, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8177716Dec 21, 2009May 15, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8195265Feb 9, 2011Jun 5, 2012Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8206297Jun 26, 2012Dexcom, Inc.System and methods for processing analyte sensor dataUS8216139Sep 23, 2009Jul 10, 2012Dexcom, Inc.Signal processing for continuous analyte sensorUS8223021Jul 17, 2012Abbott Diabetes Care Inc.RF tag on test strips, test strip vials and boxesUS8224413Oct 10, 2008Jul 17, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8226555Mar 18, 2009Jul 24, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8226557Jul 24, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8226558Sep 27, 2010Jul 24, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8229534Jul 24, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8229535Jul 24, 2012Dexcom, Inc.Systems and methods for blood glucose monitoring and alert deliveryUS8229536Jul 24, 2012Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8231531 *Jul 31, 2012Dexcom, Inc.Analyte sensorUS8231532Apr 30, 2007Jul 31, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8233958Oct 12, 2009Jul 31, 2012Dexcom, Inc.Signal processing for continuous analyte sensorUS8233959Jul 31, 2012Dexcom, Inc.Systems and methods for processing analyte sensor dataUS8235896Dec 21, 2009Aug 7, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8249684Aug 21, 2012Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS8251906Apr 15, 2009Aug 28, 2012Dexcom, Inc.Signal processing for continuous analyte sensorUS8255031Mar 17, 2009Aug 28, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8257259Sep 4, 2012Dexcom, Inc.Signal processing for continuous analyte sensorUS8260392Sep 4, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8260393Sep 4, 2012Dexcom, Inc.Systems and methods for replacing signal data artifacts in a glucose sensor data streamUS8265725Sep 11, 2012Dexcom, Inc.Signal processing for continuous analyte sensorUS8265726Sep 11, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8273022Sep 25, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8275437Mar 23, 2007Sep 25, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8275438Sep 25, 2012Dexcom, Inc.Analyte sensorUS8275439Nov 9, 2009Sep 25, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8280475Feb 23, 2009Oct 2, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8282549Oct 9, 2012Dexcom, Inc.Signal processing for continuous analyte sensorUS8282550Jul 29, 2008Oct 9, 2012Dexcom, Inc.Integrated receiver for continuous analyte sensorUS8285354Mar 23, 2010Oct 9, 2012Dexcom, Inc.System and methods for processing analyte sensor dataUS8287453Nov 7, 2008Oct 16, 2012Dexcom, Inc.Analyte sensorUS8287454Oct 16, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8287495Oct 10, 2011Oct 16, 2012Tandem Diabetes Care, Inc.Infusion pump system with disposable cartridge having pressure venting and pressure feedbackUS8290559Oct 24, 2008Oct 16, 2012Dexcom, Inc.Systems and methods for processing sensor dataUS8290560Oct 16, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8290561Oct 16, 2012Dexcom, Inc.Signal processing for continuous analyte sensorUS8290562Oct 16, 2012Dexcom, Inc.System and methods for processing analyte sensor dataUS8292810Jan 27, 2011Oct 23, 2012Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8298142Oct 30, 2012Dexcom, Inc.Analyte sensorUS8298184Oct 30, 2012Tandem Diabetes Care, Inc.Infusion pump system with disposable cartridge having pressure venting and pressure feedbackUS8306598Nov 9, 2009Nov 6, 2012Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8311749Nov 13, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8313434Nov 20, 2012Dexcom, Inc.Analyte sensor inserter systemUS8318096Dec 8, 2008Nov 27, 2012Panasonic CorporationBiological sample measurement apparatusUS8321149Nov 27, 2012Dexcom, Inc.Transcutaneous analyte sensorUS8323194Dec 4, 2012Inlight Solutions, Inc.Detection of bubbles during hemodynamic monitoring when performing automated measurement of blood constituentsUS8332008Mar 23, 2010Dec 11, 2012Dexcom, Inc.System and methods for processing analyte sensor dataUS8346336Mar 18, 2009Jan 1, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8346337Jun 30, 2009Jan 1, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8346338Jan 1, 2013Dexcom, Inc.System and methods for replacing signal artifacts in a glucose sensor data streamUS8353829Dec 21, 2009Jan 15, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8357091Jan 22, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8358210Jan 22, 2013Abbott Diabetes Care Inc.RF tag on test strips, test strip vials and boxesUS8364230Jan 29, 2013Dexcom, Inc.Analyte sensorUS8364231Jan 29, 2013Dexcom, Inc.Analyte sensorUS8366614Mar 30, 2009Feb 5, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8369919Oct 24, 2008Feb 5, 2013Dexcom, Inc.Systems and methods for processing sensor dataUS8372005Dec 21, 2009Feb 12, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8374667Oct 16, 2008Feb 12, 2013Dexcom, Inc.Signal processing for continuous analyte sensorUS8380273Feb 19, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8386004Feb 26, 2013Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS8390455Mar 5, 2013Abbott Diabetes Care Inc.RF tag on test strips, test strip vials and boxesUS8391945Mar 17, 2009Mar 5, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8394021Mar 12, 2013Dexcom, Inc.System and methods for processing analyte sensor dataUS8396528Mar 12, 2013Dexcom, Inc.Analyte sensorUS8409131Mar 7, 2007Apr 2, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8412301Apr 2, 2013Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8417312Oct 24, 2008Apr 9, 2013Dexcom, Inc.Systems and methods for processing sensor dataUS8423113Apr 16, 2013Dexcom, Inc.Systems and methods for processing sensor dataUS8423114Oct 1, 2007Apr 16, 2013Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS8425416Apr 23, 2013Dexcom, Inc.Analyte sensorUS8425417Apr 23, 2013Dexcom, Inc.Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion deviceUS8428678Apr 23, 2013Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS8428679Mar 26, 2010Apr 23, 2013Dexcom, Inc.System and methods for processing analyte sensor dataUS8435179Jan 27, 2011May 7, 2013Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8442610Aug 21, 2008May 14, 2013Dexcom, Inc.System and methods for processing analyte sensor dataUS8447376May 21, 2013Dexcom, Inc.Analyte sensorUS8449464May 28, 2013Dexcom, Inc.Analyte sensorUS8452368May 28, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8457708Jun 4, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8463350Jun 11, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8465425Jun 18, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8469886Sep 23, 2009Jun 25, 2013Dexcom, Inc.Signal processing for continuous analyte sensorUS8473021Jul 31, 2009Jun 25, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8475373Jul 17, 2008Jul 2, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8478377Nov 7, 2008Jul 2, 2013Dexcom, Inc.Analyte sensorUS8480580Apr 19, 2007Jul 9, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8483791Apr 11, 2008Jul 9, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8483793Oct 29, 2010Jul 9, 2013Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS8491474Jan 27, 2011Jul 23, 2013Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8509871Oct 28, 2008Aug 13, 2013Dexcom, Inc.Sensor head for use with implantable devicesUS8515516Mar 10, 2005Aug 20, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8515519Feb 26, 2009Aug 20, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8532730Oct 4, 2006Sep 10, 2013Dexcom, Inc.Analyte sensorUS8542122Jan 17, 2013Sep 24, 2013Abbott Diabetes Care Inc.Glucose measurement device and methods using RFIDUS8548551May 14, 2010Oct 1, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8548553Jun 22, 2012Oct 1, 2013Dexcom, Inc.System and methods for processing analyte sensor dataUS8560037Mar 26, 2010Oct 15, 2013Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS8560039Sep 17, 2009Oct 15, 2013Dexcom, Inc.Particle-containing membrane and particulate electrode for analyte sensorsUS8562528Nov 7, 2008Oct 22, 2013Dexcom, Inc.Analyte sensorUS8562558Jun 5, 2008Oct 22, 2013Dexcom, Inc.Integrated medicament delivery device for use with continuous analyte sensorUS8565848May 7, 2009Oct 22, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8565849May 14, 2010Oct 22, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8571625May 14, 2010Oct 29, 2013Dexcom, Inc.Transcutaneous analyte sensorUS8579816Jan 7, 2010Nov 12, 2013Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS8588882Dec 16, 2009Nov 19, 2013Dexcom, Inc.System and methods for processing analyte sensor dataUS8591455Feb 20, 2009Nov 26, 2013Dexcom, Inc.Systems and methods for customizing delivery of sensor dataUS8597189Mar 3, 2009Dec 3, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8611978Jan 7, 2010Dec 17, 2013Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS8612159Feb 16, 2004Dec 17, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8615282Feb 22, 2006Dec 24, 2013Dexcom, Inc.Analyte sensorUS8617071Jun 21, 2007Dec 31, 2013Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8622905Dec 11, 2009Jan 7, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8622906Dec 21, 2009Jan 7, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8626257Nov 7, 2008Jan 7, 2014Dexcom, Inc.Analyte sensorUS8641619Dec 21, 2009Feb 4, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8649841Apr 3, 2007Feb 11, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8652043Jul 20, 2012Feb 18, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8657745Oct 16, 2008Feb 25, 2014Dexcom, Inc.Signal processing for continuous analyte sensorUS8657747Apr 5, 2011Feb 25, 2014Dexcom, Inc.Systems and methods for processing analyte sensor dataUS8660627Mar 17, 2009Feb 25, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8663109Mar 29, 2010Mar 4, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8666469Nov 16, 2007Mar 4, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8668645Jan 3, 2003Mar 11, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8670815Apr 30, 2007Mar 11, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8672844Feb 27, 2004Mar 18, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8672845Mar 25, 2010Mar 18, 2014Dexcom, Inc.Systems and methods for processing analyte sensor dataUS8676287Dec 11, 2009Mar 18, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8688188Jun 30, 2009Apr 1, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8688386Jun 30, 2010Apr 1, 2014Lifescan, Inc.Analyte testing method and device for calculating basal insulin therapyUS8690775Apr 11, 2008Apr 8, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8700117Dec 8, 2009Apr 15, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8721545Mar 22, 2010May 13, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8721585Mar 30, 2012May 13, 2014Dex Com, Inc.Integrated delivery device for continuous glucose sensorUS8731630Mar 22, 2010May 20, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8734346Apr 30, 2007May 27, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8734348Mar 17, 2009May 27, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8738109Mar 3, 2009May 27, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8744545Mar 3, 2009Jun 3, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8747315Sep 23, 2009Jun 10, 2014Dexcom. Inc.Signal processing for continuous analyte sensorUS8750955 *Nov 2, 2009Jun 10, 2014Dexcom, Inc.Analyte sensorUS8758323Jul 29, 2010Jun 24, 2014Tandem Diabetes Care, Inc.Infusion pump system with disposable cartridge having pressure venting and pressure feedbackUS8761856Apr 27, 2012Jun 24, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8771187May 31, 2011Jul 8, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8774886Oct 4, 2006Jul 8, 2014Dexcom, Inc.Analyte sensorUS8774887Mar 24, 2007Jul 8, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8774888Jan 20, 2010Jul 8, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8777853Apr 4, 2012Jul 15, 2014Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8788006Dec 11, 2009Jul 22, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8788007Mar 8, 2012Jul 22, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8788008May 31, 2011Jul 22, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8790260Oct 14, 2009Jul 29, 2014Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8792953Mar 19, 2010Jul 29, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8792954Mar 19, 2010Jul 29, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8792955Jun 9, 2011Jul 29, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8795177Jan 14, 2009Aug 5, 2014Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8801610Jul 24, 2009Aug 12, 2014Dexcom, Inc.Signal processing for continuous analyte sensorUS8801611Mar 22, 2010Aug 12, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8801612Apr 27, 2012Aug 12, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8808182Apr 27, 2012Aug 19, 2014Dexcom, Inc.System and methods for processing analyte sensor dataUS8808228Jun 5, 2008Aug 19, 2014Dexcom, Inc.Integrated medicament delivery device for use with continuous analyte sensorUS8812072Apr 17, 2008Aug 19, 2014Dexcom, Inc.Transcutaneous medical device with variable stiffnessUS8812073Jun 1, 2010Aug 19, 2014Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8821400Feb 9, 2011Sep 2, 2014Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8821433May 22, 2012Sep 2, 2014Tandem Diabetes Care, Inc.Insulin pump having basal rate testing featuresUS8825127May 14, 2010Sep 2, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8828201Jul 1, 2010Sep 9, 2014Dexcom, Inc.Analyte sensors and methods of manufacturing sameUS8840553Feb 26, 2009Sep 23, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8843187Jun 1, 2010Sep 23, 2014Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS8845536Apr 11, 2007Sep 30, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8858434Mar 10, 2005Oct 14, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8880137Apr 18, 2003Nov 4, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8882741Apr 30, 2012Nov 11, 2014Dexcom, Inc.Integrated delivery device for continuous glucose sensorUS8886272Feb 22, 2006Nov 11, 2014Dexcom, Inc.Analyte sensorUS8886273Nov 7, 2008Nov 11, 2014Dexcom, Inc.Analyte sensorUS8911367Mar 26, 2007Dec 16, 2014Dexcom, Inc.Analyte sensorUS8911369Dec 15, 2008Dec 16, 2014Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS8915849Feb 3, 2009Dec 23, 2014Dexcom, Inc.Transcutaneous analyte sensorUS8915850Mar 28, 2014Dec 23, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8920319Dec 28, 2012Dec 30, 2014Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8920401Apr 30, 2012Dec 30, 2014Dexcom, Inc.Integrated delivery device for continuous glucose sensorUS8926561Jul 29, 2010Jan 6, 2015Tandem Diabetes Care, Inc.Infusion pump system with disposable cartridge having pressure venting and pressure feedbackUS8926585Mar 30, 2012Jan 6, 2015Dexcom, Inc.Integrated delivery device for continuous glucose sensorUS8929968Jul 19, 2010Jan 6, 2015Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS8974386Nov 1, 2005Mar 10, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS8974387Jun 30, 2010Mar 10, 2015Lifescan Scotland LimitedAnalyte testing method and device for diabetes managementUS8986209Jul 13, 2012Mar 24, 2015Dexcom, Inc.Transcutaneous analyte sensorUS9011331Dec 29, 2004Apr 21, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9011332Oct 30, 2007Apr 21, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9014773Mar 7, 2007Apr 21, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9020572Sep 10, 2010Apr 28, 2015Dexcom, Inc.Systems and methods for processing, transmitting and displaying sensor dataUS9042953Mar 2, 2007May 26, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9044199Mar 10, 2005Jun 2, 2015Dexcom, Inc.Transcutaneous analyte sensorUS9050413Apr 30, 2012Jun 9, 2015Dexcom, Inc.Integrated delivery device for continuous glucose sensorUS9055901Sep 14, 2012Jun 16, 2015Dexcom, Inc.Transcutaneous analyte sensorUS9060742Mar 19, 2010Jun 23, 2015Dexcom, Inc.Transcutaneous analyte sensorUS9066694Apr 3, 2007Jun 30, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9066695Apr 12, 2007Jun 30, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9066697Oct 27, 2011Jun 30, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9072477Jun 21, 2007Jul 7, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9078607Jun 17, 2013Jul 14, 2015Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9078608Jul 13, 2012Jul 14, 2015Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS9078626Mar 31, 2011Jul 14, 2015Dexcom, Inc.Transcutaneous analyte sensorUS9107623Apr 15, 2009Aug 18, 2015Dexcom, Inc.Signal processing for continuous analyte sensorUS9119528Jan 16, 2013Sep 1, 2015Dexcom, Inc.Systems and methods for providing sensitive and specific alarmsUS9119529Jan 16, 2013Sep 1, 2015Dexcom, Inc.Systems and methods for dynamically and intelligently monitoring a host's glycemic condition after an alert is triggeredUS9131885Jul 1, 2010Sep 15, 2015Dexcom, Inc.Analyte sensors and methods of manufacturing sameUS9135402Oct 24, 2008Sep 15, 2015Dexcom, Inc.Systems and methods for processing sensor dataUS9143569Feb 20, 2009Sep 22, 2015Dexcom, Inc.Systems and methods for processing, transmitting and displaying sensor dataUS9149219Feb 9, 2011Oct 6, 2015Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS9149233Jun 13, 2012Oct 6, 2015Dexcom, Inc.Systems and methods for processing sensor dataUS9149234 *Jun 13, 2012Oct 6, 2015Dexcom, Inc.Systems and methods for processing sensor dataUS9155496Feb 18, 2011Oct 13, 2015Dexcom, Inc.Low oxygen in vivo analyte sensorUS9155843Jul 26, 2012Oct 13, 2015Dexcom, Inc.Integrated delivery device for continuous glucose sensorUS9192328Sep 23, 2009Nov 24, 2015Dexcom, Inc.Signal processing for continuous analyte sensorUS9211377Jul 29, 2010Dec 15, 2015Tandem Diabetes Care, Inc.Infusion pump system with disposable cartridge having pressure venting and pressure feedbackUS9220449Jul 9, 2013Dec 29, 2015Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS9237864Jul 1, 2010Jan 19, 2016Dexcom, Inc.Analyte sensors and methods of manufacturing sameUS9247900Jun 4, 2013Feb 2, 2016Dexcom, Inc.Analyte sensorUS9247901Aug 2, 2006Feb 2, 2016Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS9282895Dec 10, 2013Mar 15, 2016Pacesetter, Inc.Method and implantable system for blood-glucose concentration monitoring using parallel methodologiesUS9282925Mar 25, 2010Mar 15, 2016Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS9314196Sep 7, 2012Apr 19, 2016Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS9320466Oct 18, 2013Apr 26, 2016Dexcom, Inc.Analyte sensorUS9326714Jun 29, 2010May 3, 2016Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9326716Dec 5, 2014May 3, 2016Abbott Diabetes Care Inc.Analyte monitoring device and methods of useUS9328371Jul 16, 2013May 3, 2016Dexcom, Inc.Sensor head for use with implantable devicesUS9339222May 31, 2013May 17, 2016Dexcom, Inc.Particle-containing membrane and particulate electrode for analyte sensorsUS9339238May 16, 2012May 17, 2016Dexcom, Inc.Systems and methods for processing sensor dataUS9351668Oct 12, 2009May 31, 2016Dexcom, Inc.Signal processing for continuous analyte sensorUS9351677Mar 4, 2013May 31, 2016Dexcom, Inc.Analyte sensor with increased reference capacityUS9364173 *Sep 23, 2009Jun 14, 2016Dexcom, Inc.Signal processing for continuous analyte sensorUS20050027463 *Aug 1, 2003Feb 3, 2005Goode Paul V.System and methods for processing analyte sensor dataUS20050043598 *Aug 22, 2003Feb 24, 2005Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20050096511 *Nov 30, 2004May 5, 2005Fox James K.System for monitoring physiological characteristicsUS20050143635 *Dec 3, 2004Jun 30, 2005Kamath Apurv U.Calibration techniques for a continuous analyte sensorUS20060020190 *Mar 10, 2005Jan 26, 2006Dexcom, Inc.Transcutaneous analyte sensorUS20060036139 *Mar 10, 2005Feb 16, 2006Dexcom, Inc.Transcutaneous analyte sensorUS20060036142 *Mar 10, 2005Feb 16, 2006Dexcom, Inc.Transcutaneous analyte sensorUS20060142651 *Feb 22, 2006Jun 29, 2006Mark BristerAnalyte sensorUS20060183984 *Feb 22, 2006Aug 17, 2006Dobbles J MAnalyte sensorUS20060258929 *Mar 9, 2006Nov 16, 2006Goode Paul V JrSystem and methods for processing analyte sensor data for sensor calibrationUS20060270923 *May 23, 2006Nov 30, 2006Brauker James HAnalyte sensorUS20070016381 *Sep 1, 2006Jan 18, 2007Apurv KamathSystems and methods for processing analyte sensor dataUS20070032706 *Aug 2, 2006Feb 8, 2007Apurv KamathSystems and methods for replacing signal artifacts in a glucose sensor data streamUS20070038044 *Jun 1, 2006Feb 15, 2007Dobbles J MAnalyte sensorUS20070149874 *Mar 7, 2007Jun 28, 2007Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20070163880 *Mar 1, 2007Jul 19, 2007Dexcom, Inc.Analyte sensorUS20070173708 *Jun 1, 2006Jul 26, 2007Dobbles J MAnalyte sensorUS20070179370 *Apr 3, 2007Aug 2, 2007Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20070191699 *Apr 3, 2007Aug 16, 2007Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20070197889 *Feb 22, 2006Aug 23, 2007Mark BristerAnalyte sensorUS20070203408 *Apr 30, 2007Aug 30, 2007Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20070203410 *Apr 30, 2007Aug 30, 2007Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20070203411 *Apr 30, 2007Aug 30, 2007Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20070208244 *Apr 11, 2007Sep 6, 2007Brauker James HTranscutaneous analyte sensorUS20070208245 *Apr 11, 2007Sep 6, 2007Brauker James HTranscutaneous analyte sensorUS20070208246 *Apr 11, 2007Sep 6, 2007Brauker James HTranscutaneous analyte sensorUS20070208247 *Apr 30, 2007Sep 6, 2007Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20070225675 *Feb 28, 2007Sep 27, 2007Mark Ries RobinsonBlood Analyte DeterminationsUS20070249920 *Jun 21, 2007Oct 25, 2007Abbott Diabetes Care, Inc.Analyte monitoring device and methods of useUS20070255347 *Oct 30, 2006Nov 1, 2007Medtronic, Inc.Inhibition of stimulation notificationUS20070276209 *Apr 22, 2005Nov 29, 2007Fumiaki EmotoBlood-Sugar Level Measuring DeviceUS20080014913 *Jul 11, 2007Jan 17, 2008Jason BalanCellular mobile modbus data collectionUS20080027290 *Jul 25, 2007Jan 31, 2008Terry Keith BryantBase station for retrieving data from and programming a medical deviceUS20080033254 *Jun 13, 2007Feb 7, 2008Dexcom, Inc.Systems and methods for replacing signal data artifacts in a glucose sensor data streamUS20080083617 *Oct 1, 2007Apr 10, 2008Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS20080086039 *Oct 30, 2007Apr 10, 2008Abbott Diabetes Care, Inc.Analyte Monitoring Device And Methods Of UseUS20080086042 *Mar 26, 2007Apr 10, 2008Dexcom, Inc.Analyte sensorUS20080091096 *Nov 16, 2007Apr 17, 2008Abbott Diabetes Care, Inc.Analyte Monitoring Device and Methods of UseUS20080092638 *Oct 2, 2007Apr 24, 2008Bayer Healthcare LlcWireless analyte monitoring systemUS20080108942 *Mar 26, 2007May 8, 2008Dexcom, Inc.Analyte sensorUS20080139910 *Dec 6, 2006Jun 12, 2008Metronic Minimed, Inc.Analyte sensor and method of using the sameUS20080189051 *Apr 7, 2008Aug 7, 2008Dexcom, Inc.System and methods for processing analyte sensor dataUS20080194936 *Apr 14, 2008Aug 14, 2008Dexcom, Inc.System and methods for processing analyte sensor dataUS20080194938 *Apr 17, 2008Aug 14, 2008Dexcom, Inc.Transcutaneous medical device with variable stiffnessUS20080197024 *Mar 25, 2008Aug 21, 2008Dexcom, Inc.Analyte sensorUS20080200789 *Mar 25, 2008Aug 21, 2008Dexcom, Inc.Analyte sensorUS20080200791 *Mar 25, 2008Aug 21, 2008Dexcom, Inc.Analyte sensorUS20080208025 *May 1, 2008Aug 28, 2008Dexcom, Inc.Low oxygen in vivo analyte sensorUS20080214915 *Apr 11, 2008Sep 4, 2008Dexcom, Inc.Transcutaneous analyte sensorUS20080214918 *Apr 28, 2008Sep 4, 2008Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS20080220403 *Feb 15, 2008Sep 11, 2008Ohio UniversitySystem and method for managing diabetesUS20080242961 *Jun 11, 2008Oct 2, 2008Dexcom, Inc.Transcutaneous analyte sensorUS20080262469 *Jun 5, 2008Oct 23, 2008Dexcom. Inc.Integrated medicament delivery device for use with continuous analyte sensorUS20080275313 *Jul 17, 2008Nov 6, 2008Dexcom, Inc.Transcutaneous analyte sensorUS20080287765 *Jul 29, 2008Nov 20, 2008Dexcom, Inc.Integrated receiver for continuous analyte sensorUS20080287766 *Jul 29, 2008Nov 20, 2008Dexcom, Inc.Integrated receiver for continuous analyte sensorUS20080296155 *May 1, 2008Dec 4, 2008Dexcom, Inc.Low oxygen in vivo analyte sensorUS20080306368 *Aug 21, 2008Dec 11, 2008Dexcom, Inc.System and methods for processing analyte sensor dataUS20080306435 *Jun 5, 2008Dec 11, 2008Dexcom, Inc.Integrated medicament delivery device for use with continuous analyte sensorUS20090018424 *Mar 25, 2008Jan 15, 2009Dexcom, Inc.Analyte sensorUS20090030294 *Oct 7, 2008Jan 29, 2009Dexcom, Inc.Implantable analyte sensorUS20090036753 *Jul 31, 2007Feb 5, 2009King Allen BContinuous glucose monitoring-directed adjustments in basal insulin rate and insulin bolus dosing formulasUS20090036758 *Oct 16, 2008Feb 5, 2009Dexcom, Inc.Signal processing for continuous analyte sensorUS20090043240 *Apr 23, 2008Feb 12, 2009Mark Ries RobinsonMethod and apparatus for blood transport using a pressure controller in measurement of blood characteristicsUS20090043541 *Oct 16, 2008Feb 12, 2009Dexcom, Inc.Signal processing for continuous analyte sensorUS20090048535 *Sep 25, 2007Feb 19, 2009Mark Ries RobinsonDetecting Cross-contamination in Blood Measurements with a Multilumen CatheterUS20090054754 *Aug 8, 2008Feb 26, 2009Mcmahon DaveClinician-controlled semi-automated medication managementUS20090062635 *Nov 3, 2008Mar 5, 2009Dexcom, Inc.Signal processing for continuous analyte sensorUS20090076361 *Nov 18, 2008Mar 19, 2009Dexcom, Inc.Transcutaneous analyte sensorUS20090088615 *Sep 30, 2008Apr 2, 2009Mark Ries RobinsonIndwelling Fiber Optic Probe for Blood Glucose MeasurementsUS20090099436 *Dec 15, 2008Apr 16, 2009Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS20090124877 *Jan 14, 2009May 14, 2009Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20090124878 *Jan 14, 2009May 14, 2009Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20090124879 *Jan 14, 2009May 14, 2009Dexcom, Inc.Transcutaneous analyte sensorUS20090124964 *Nov 7, 2008May 14, 2009Dexcom, Inc.Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion deviceUS20090131769 *Nov 7, 2008May 21, 2009Dexcom, Inc.Analyte sensorUS20090131776 *Nov 7, 2008May 21, 2009Dexcom, Inc.Analyte sensorUS20090131777 *Nov 7, 2008May 21, 2009Dexcom, Inc.Analyte sensorUS20090137887 *Nov 7, 2008May 28, 2009Dexcom, Inc.Analyte sensorUS20090156919 *Feb 26, 2009Jun 18, 2009Dexcom, Inc.Transcutaneous analyte sensorUS20090156975 *Nov 30, 2008Jun 18, 2009Mark Ries RobinsonRobust System and Methods for Blood AccessUS20090163790 *Jan 23, 2009Jun 25, 2009Dexcom, Inc.Transcutaneous analyte sensorUS20090192366 *Oct 24, 2008Jul 30, 2009Dexcom, IncSystems and methods for processing sensor dataUS20090192380 *Oct 24, 2008Jul 30, 2009Dexcom, Inc.Systems and methods for processing sensor dataUS20090192722 *Oct 24, 2008Jul 30, 2009Dexcom, Inc.Systems and methods for processing sensor dataUS20090192745 *Jul 30, 2009Dexcom, Inc.Systems and methods for processing sensor dataUS20090192751 *Oct 24, 2008Jul 30, 2009Dexcom, Inc.Systems and methods for processing sensor dataUS20090203981 *Apr 15, 2009Aug 13, 2009Dexcom, Inc.Signal processing for continuous analyte sensorUS20090204341 *Apr 15, 2009Aug 13, 2009Dexcom, Inc.Signal processing for continuous analyte sensorUS20090216103 *May 7, 2009Aug 27, 2009Dexcom, Inc.Transcutaneous analyte sensorUS20090242425 *Mar 25, 2008Oct 1, 2009Dexcom, Inc.Analyte sensorUS20090287074 *Nov 19, 2009Dexcom, Inc.Analyte sensorUS20090299162 *Dec 3, 2009Dexcom, Inc.Signal processing for continuous analyte sensorUS20100010331 *Jan 14, 2010Dexcom, Inc.Signal processing for continuous analyte sensorUS20100010332 *Sep 23, 2009Jan 14, 2010Dexcom, Inc.Signal processing for continuous analyte sensorUS20100022855 *Sep 23, 2009Jan 28, 2010Dexcom, Inc.Signal processing for continuous analyte sensorUS20100030053 *Feb 4, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100030484 *Feb 4, 2010Dexcom, Inc.Signal processing for continuous analyte sensorUS20100035334 *Dec 8, 2008Feb 11, 2010Eiji OkudaBiological sample measurement apparatusUS20100036215 *Feb 11, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100036216 *Oct 14, 2009Feb 11, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100036222 *Oct 14, 2009Feb 11, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100036223 *Feb 11, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100036224 *Oct 14, 2009Feb 11, 2010DecCom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100036225 *Oct 14, 2009Feb 11, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100041971 *Feb 18, 2010Dexcom, Inc.Implantable analyte sensorUS20100045465 *Feb 25, 2010Dexcom Inc.Signal processing for continuous analyte sensorUS20100049024 *Feb 25, 2010Dexcom, Inc.Composite material for implantable deviceUS20100063373 *Mar 11, 2010Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS20100076283 *Sep 17, 2009Mar 25, 2010Dexcom, Inc.Particle-containing membrane and particulate electrode for analyte sensorsUS20100081908 *Apr 1, 2010Dexcom, Inc.Analyte sensorUS20100081910 *Apr 1, 2010Dexcom, Inc.Analyte sensorUS20100094114 *Oct 9, 2009Apr 15, 2010Mark Ries RobinsonUse of multiple calibration solutions with an analyte sensor with use in an automated blood access systemUS20100114002 *Oct 10, 2009May 6, 2010O'mahony John JMethod and apparatus for an extracorporeal control of blood glucoseUS20100168535 *Feb 26, 2010Jul 1, 2010Mark Ries RobinsonMethods and apparatuses related to blood analyte measurement systemUS20100168545 *Jan 7, 2010Jul 1, 2010Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS20100168546 *Jan 7, 2010Jul 1, 2010Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS20100174158 *Jul 8, 2010Dexcom, Inc.Transcutaneous analyte sensorUS20100174163 *Mar 22, 2010Jul 8, 2010Dexcom, Inc.Transcutaneous analyte sensorUS20100179400 *Jul 15, 2010Dexcom, Inc.Signal processing for continuous analyte sensorUS20100179402 *Jul 15, 2010Dexcom, Inc.System and methods for processing analyte sensor data for sensor calibrationUS20100179406 *Jul 15, 2010DesCom, Inc.System and methods for processing analyte sensor dataUS20100179408 *Jul 15, 2010Dexcom, Inc.Systems and methods for processing analyte sensor dataUS20100179409 *Jul 15, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100185065 *Mar 26, 2010Jul 22, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS20100185069 *Jul 22, 2010Dexcom, Inc.Transcutaneous analyte sensorUS20100185070 *Jul 22, 2010Dexcom, Inc.Dual electrode system for a continuous analyte sensorUS20100185072 *Mar 23, 2010Jul 22, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS20100191082 *Mar 19, 2010Jul 29, 2010Dexcom, Inc.Transcutaneous analyte sensorUS20100198036 *Aug 5, 2010Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS20100214104 *Aug 26, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS20100217106 *Aug 26, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS20100217555 *Aug 26, 2010Dexcom, IncSystem and methods for processing analyte sensor dataUS20100217557 *Jan 20, 2010Aug 26, 2010Dexcom, Inc.System and methods for processing analyte sensor dataUS20100223013 *Sep 2, 2010Dexcom, Inc.Transcutaneous analyte sensorUS20100223022 *May 14, 2010Sep 2, 2010Dexcom, Inc.Transcutaneous analyte sensorUS20100223023 *Sep 2, 2010Dexcom, Inc.Transcutaneous analyte sensorUS20100235106 *May 25, 2010Sep 16, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100240975 *Sep 23, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100240976 *Sep 23, 2010Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20100259543 *Jun 25, 2010Oct 14, 2010E-San Ltd.Medical Data DisplayUS20100331648 *Sep 1, 2010Dec 30, 2010Dexcom, Inc.Calibration techniques for a continuous analyte sensorUS20100331654 *Jun 30, 2010Dec 30, 2010Lifescan Scotland Ltd.Systems for diabetes management and methodsUS20100332142 *Jun 30, 2010Dec 30, 2010Lifescan,Inc.Analyte testing method and device for calculating basal insulin therapyUS20100332445 *Jun 29, 2010Dec 30, 2010Lifescan, Inc.Analyte testing method and systemUS20110024307 *Jul 1, 2010Feb 3, 2011Dexcom, Inc.Analyte sensorUS20110027127 *Feb 3, 2011Dexcom, Inc.Analyte sensors and methods of manufacturing sameUS20110028815 *Jul 1, 2010Feb 3, 2011Dexcom, Inc.Analyte sensors and methods of manufacturing sameUS20110028816 *Jul 1, 2010Feb 3, 2011Dexcom, Inc.Analyte sensors and methods of manufacturing sameUS20110077493 *Jun 30, 2010Mar 31, 2011Lifescan Scotland Ltd.Analyte testing method and device for diabetes mangementUS20110118579 *May 19, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20110118580 *May 19, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20110124997 *May 26, 2011Dexcom, Inc.System and methods for replacing signal artifacts in a glucose sensor data streamUS20110130970 *Jun 2, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20110130971 *Jun 2, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20110137601 *Jun 9, 2011Dexcom, Inc.Systems and methods for replacing signal artifacts in a glucose sensor data streamUS20110152634 *Jun 23, 2011Jeff ThewMeasuring Human Biological Fluid LevelsUS20110152642 *Dec 18, 2009Jun 23, 2011Mak Ries RobinsonDetection of bubbles during hemodynamic monitoring when performing automated measurement of blood constituentsUS20110178378 *Jul 21, 2011Dexcom, Inc.Transcutaneous analyte sensorUS20110205064 *Aug 25, 2011Lifescan Scotland Ltd.Analyte testing method and system with high and low blood glucose trends notificationUS20110218414 *Sep 8, 2011Dexcom, Inc.Systems and methods for processing analyte sensor dataUS20110231140 *Sep 22, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS20110231141 *Sep 22, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS20110231142 *Sep 22, 2011Dexcom, Inc.System and methods for processing analyte sensor dataUS20110282327 *Nov 17, 2011Echo Therapeutics, Inc.System and method for continuous non-invasive glucose monitoringUS20120165695 *Dec 22, 2011Jun 28, 2012Widex A/SEeg monitoring apparatus and method for presenting messages thereinUS20120220847 *Nov 4, 2010Aug 30, 2012Aimedics Pty LtdAlarm systems using monitored physiological data and trend difference methodsUS20120227737 *May 15, 2012Sep 13, 2012Medtronic Minimed, Inc.Analyte sensor and method of using the sameUS20120302855 *Nov 29, 2012Dexcom, Inc.Systems and methods for processing sensor dataUS20150141763 *Mar 12, 2014May 21, 2015Honeywell International Inc.Non-invasive blood glucose concentration sensing using light modulationUS20150201846 *Jul 22, 2013Jul 23, 2015Medbright Medical Solutions LtdDevice and method for providing information indicative of a stress situation in a humanUSRE43399Jun 13, 2008May 22, 2012Dexcom, Inc.Electrode systems for electrochemical sensorsUSRE44695May 1, 2012Jan 7, 2014Dexcom, Inc.Dual electrode system for a continuous analyte sensorDE102010027486A1 *Jul 16, 2010Apr 12, 2012L�ser Medizintechnik GmbHVerfahren zur �berwachung des medizinischen Zustandes eines PatientenEP2184694A3 *Mar 20, 2008May 11, 2016Lifescan, Inc.Communication medium for diabetes managementWO2008014320A2 *Jul 25, 2007Jan 31, 2008Carson Valley Research, LlcBase station for retrieving data from and programming a medical deviceWO2014205412A1 *Jun 20, 2014Dec 24, 2014Intuity Medical, Inc.Analyte monitoring system with audible feedback* Cited by examinerClassifications U.S. Classification600/365, 128/903, 600/309International ClassificationG06F19/00, A61B5/00Cooperative ClassificationA61B5/1468, A61B2560/045, G06F19/3418, A61B5/14532, A61B5/0002, A61B5/7275, A61B2560/0252, A61B5/1495, G06F19/3406, A61B5/1486, G06F19/3456, G06F19/3487, A61B2560/0223European ClassificationA61B5/145G, G06F19/34P, A61B5/1495, G06F19/34A, G06F19/34C, G06F19/34LLegal EventsDateCodeEventDescriptionOct 12, 2004ASAssignmentOwner name: MEDTRONIC MINIMED, INC., CALIFORNIAFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:SIDDIQUI, UZAIR;PATEL HIMANSHU P.;MASTROTOTARO, JOHN J.;AND OTHERS;REEL/FRAME:015238/0001;SIGNING DATES FROM 20040602 TO 20041006RotateOriginal ImageGoogle Home - Sitemap - USPTO Bulk Downloads - Privacy Policy - Terms of Service - About Google Patents - Send FeedbackData provided by IFI CLAIMS Patent Services