Abstract: A method for factory calibration of a sensor of a CGM system is disclosed. A processor receives an enzyme membrane thickness after each dip of a working wire according to first parameters. The processor receives a glucose limiting membrane thickness after each dip of the working wire according to second parameters. The processor determines a working wire diameter, and includes the membrane thicknesses. The processor in communication with the CGM system, automatically generates a correlation between the first and the second parameters to at least one of a factory sensitivity and a drift profile. The drift profile predicts a sensitivity of the sensor over time. The processor associates the at least one of the factory sensitivity or the drift profile with the sensor. The sensor outputs a glucose reading during in-vivo use based on the at least one of the factory sensitivity or the drift profile.

Abstract: A method for factory calibration of a sensor of a CGM system is disclosed. A processor receives an enzyme membrane thickness after each dip of a working wire according to first parameters. The processor receives a glucose limiting membrane thickness after each dip of the working wire according to second parameters. The processor determines a working wire diameter, and includes the membrane thicknesses. The processor in communication with the CGM system, automatically generates a correlation between the first and the second parameters to at least one of a factory sensitivity and a drift profile. The drift profile predicts a sensitivity of the sensor over time. The processor associates the at least one of the factory sensitivity or the drift profile with the sensor. The sensor outputs a glucose reading during in-vivo use based on the at least one of the factory sensitivity or the drift profile.

Abstract: A glucose-specific sensor has a glucose limiting layer (GLL), an enzyme layer and an interference layer. The GLL comprises polyurethane with a molecular weight greater than 100,000 Daltons that is physically crosslinked with a water-soluble polymer having a molecular weight greater than 100,000 Daltons. The interference layer has a polymer formed from pyrrole, phenylenediamine (PDA), aminophenol, aniline, or combinations thereof. Methods for making a glucose-specific sensor include mixing a monomer with a solvent to form a monomer solution, applying the monomer solution to a substrate and electropolymerizing the monomer to form a polymer on the substrate. The polymer is an interference layer for the glucose-specific sensor. An enzyme layer is formed on the interference layer, and a glucose limiting layer is formed on the enzyme layer.

Abstract: A metabolic analyte sensor includes a substrate having an electrically conductive surface, an interference layer on the conductive surface, an enzyme layer on the interference layer, and a glucose limiting layer on the enzyme layer. The interference layer or the enzyme layer is configured such that the metabolic analyte sensor has an improved performance characteristic after sterilization compared to before sterilization. A packaged continuous metabolic monitor includes a sealed container; a metabolic sensor in the sealed container for insertion into a patient after the metabolic sensor is removed from the sealed container, the metabolic sensor comprising a conductive surface and an enzyme layer; electronic operating circuitry in the sealed container and coupled to the metabolic sensor; and a residue of a sterilizing gas in the metabolic sensor. The sealed container, the metabolic sensor and the electronic operating circuitry are sterilized together in the sealed container using the sterilizing gas.