A method of testing one or more analyte sensors each comprising a first electrode; a second electrode; and a material layer disposed on or above the first electrode; the method including (a) applying a voltage potential to the first electrode with respect to the second electrode; (b) measuring a test signal comprising an output current from the first electrode that results from the application of the voltage potential; (c) using the test signal from (b) to observe an electrical characteristic of the analyte sensor; and (d) correlating the electrical characteristic a parameter associated with an electrochemical response of the analyte sensor to an analyte, wherein the testing is under dry conditions without exposure of the electrodes to a fluid containing the analyte or an in-vivo environment containing the analyte.

The present invention relates to a method of a method of measuring a human body analyte concentration in an interstitial fluid, comprising the step of measuring a first electrical current I.sub.1 between a working electrode and a pseudo-reference electrode while applying a first potential between the working electrode and the pseudo-reference electrode, the first potential being less than a threshold potential, the magnitude of the first electrical current being greater than the magnitude of a predetermined first threshold current, and further measuring an output electrical current between the working electrode and the pseudo-reference electrode while applying a second electrical potential, the second electrical potential being greater than the first electrical potential.

Systems and methods for processing sensor data and self-calibration are provided. In some embodiments, systems and methods are provided which are capable of calibrating a continuous analyte sensor based on an initial sensitivity, and then continuously performing self-calibration without using, or with reduced use of, reference measurements. In certain embodiments, a sensitivity of the analyte sensor is determined by applying an estimative algorithm that is a function of certain parameters. Also described herein are systems and methods for determining a property of an analyte sensor using a stimulus signal. The sensor property can be used to compensate sensor data for sensitivity drift, or determine another property associated with the sensor, such as temperature, sensor membrane damage, moisture ingress in sensor electronics, and scaling factors.

A computer-implemented method for interpreting an electrochemical response, comprises the steps of: (a) providing an electrochemical response that is baseline-corrected; (b) identifying in the electrochemical response one or more peaks that exceed a predetermined height threshold and a predetermined prominence threshold, each identified peak having a peak position; (c) providing a predetermined peak position range for each of a plurality of analytes; and (d) attributing one or more of the analytes to the peaks identified in step b, by, for each peak, associating the peak with an analyte when the peak position falls within the predetermined peak position range for the analyte.

A method of measuring hematocrit is provided. The method for measuring hematocrit includes the following steps. A test strip is provided. The test strip includes a reaction region and a pair of electrodes disposed in the reaction region. A whole blood sample is entered to the reaction region. After the whole blood sample enters the reaction region, a plurality of sets of square wave voltages are intermittently applied to the pair of electrodes based on a square wave voltammetry method to obtain a plurality of feedbacks related to hematocrit. An interval between two adjacent sets of square wave voltages ranges from 0.1 seconds to 4 seconds. A feedback of an n-th set of square wave voltages is obtained to calculate a hematocrit value of the whole blood sample and n is a positive integer greater than 1. A hematocrit value is calculated according to the feedback.

Pre-connected analyte sensors are provided. A pre-connected analyte sensor includes a sensor carrier attached to an analyte sensor. The sensor carrier includes a substrate configured for mechanical coupling of the sensor to testing, calibration, or wearable equipment. The sensor carrier also includes conductive contacts for electrically coupling sensor electrodes to the testing, calibration, or wearable equipment.

An electrochemical sensor arrangement (10) for a breath alcohol measuring device (100), to a corresponding breath alcohol measuring device (100) as well as to a process for determining a vitality of electrodes of an electrochemical sensor. The electrochemical sensor arrangement comprises an electrochemical sensor with at least two electrodes (12, 14). The electrochemical sensor arrangement further comprises a heat source (16). The heat source is arranged such that it, upon activation, selectively heats one of the electrodes (12) of the electrochemical sensor.

Disclosed herein are compositions that include oxygen, a sugar or sugar alcohol, and an amino acid, wherein the amino acid is present in an amount sufficient to stabilize the oxygen. Also provided are aqueous diagnostic quality controls or calibration reagents and methods of stabilizing oxygen in a liquid solution.

Described herein are systems, assays, methods and compositions for identification of oxidase microbial redox-enzymes (MREs) specific to an analyte of interest from an environmental source. The technology relates to identification of analyte-responsive MREs that can quantify the concentration of a target analyte with high specificity and high sensitivity, for example, where the identified analyte-responsive redox-enzyme can be used to engineer an electrochemical biosensor.

A blood glucose test strip includes a base substrate, a calibration site, a test site and a non-volatile memory. The calibration site is disposed on the base substrate. A chemical reagent is applied on the calibration site. The test site is disposed on the base substrate. A chemical reagent is applied on the test site. The non-volatile memory is disposed on the base substrate. A calibration parameter is stored in the non-volatile memory. During a calibrating procedure, the calibration solution is dropped on the calibration site, a calibration parameter is calculated according to a first reaction result of the calibration solution and the chemical reagent, and the calibration parameter is stored in the non-volatile memory.