Briefly, a sensor for a continuous biological monitor is provided for measuring the level of a target analyte for a patient. The sensor has a working wire and a reference wire, where the working wire has an analyte limiting layer that passes more than 1 in 1000 analyte molecules from the patient to the an enzyme layer. The enzyme layer has an enzyme entrapped in a polyurethane cross-linked with acrylic polyol. As free electrons are generated, a conductor transfers the electrons to the biological monitor. In some cases, the sensor may be constructed without the use of any expensive platinum.

The present disclosure presents glucose sensing methods and systems. One such system comprises an electrospun-nanofibrous-membrane (ENFM)-based amperometric glucose sensor integrated on a silicon chip, in which the glucose sensor has a working electrode, a reference electrode, and a counter electrode, wherein the working electrode comprises an ENFM-based sensing electrode. The system further comprises a potentiostat circuit integrated on the silicon chip such that the potentiostat circuit comprises a voltage control unit to control a voltage difference between the working electrode and the reference electrode and a transimpedance amplifier to measure a current flow between the working electrode and the counter electrode, in which a strength of the current flow corresponds to an amount of glucose present in a sample of blood on the glucose sensor.

A glucose monitoring method and a glucose sensor, both of which use glucose dehydrogenase having a Michaelis constant (Km) for xylose of 600 mM or more and 3000 mM or less, and a Km for glucose of 0.1 mM or more and 100 mM or less, which provide for evaluating FADGDH in an aqueous system while reducing the practical influence of FADGDH on D-xylose.

Disclosed herein is an analyte sensing biointerface that comprises a sensing electrode incorporated within a non-conductive matrix comprising a plurality of passageways extending through the matrix to the sensing electrode. Also disclosed herein are methods of manufacturing a sensing biointerface and methods of detecting an analyte within tissue of a host using an analyte sensing biointerface.

The present invention relates to a biosensor for determining an analyte comprising a substrate, a working electrode comprising an electrically conductive pad in conductive contact with a mediator layer, and an enzyme layer in diffusion-enabling contact with said mediator layer, wherein said mediator layer is an electrodeposited mediator layer, and wherein said mediator layer comprises, in an embodiment consists of, an electrocatalytic agent. The present invention further relates to a method for manufacturing a biosensor, comprising providing a substrate having at least one conductive pad, electrodepositing a mediator layer onto at least part of said conductive pad, wherein said mediator layer comprises, in an embodiment consists of, an electrocatalytic agent, and depositing an enzyme layer onto at least part of said mediator layer. Moreover, the present invention relates to uses and methods related to the biosensor of the present invention.

The present disclosure provides nanoparticle transducers and methods of use thereof for the detection of analyte concentrations in a fluid. Nanoparticle transducers can comprise a nanoparticle, such as a Pdot, coupled to an enzyme that catalyzes a reaction with the analyte. The nanoparticle transducers further comprise chromophores that emit fluorescence that varies as a function of the concentration of one of the elements of the reaction. The nanoparticle transducer thus changes fluorescence as the analyte concentration changes, transforming analyte concentration values into fluorescence intensities. The measurement of these intensities provides a measurement of the analyte concentration. The nanoparticle transducers are biocompatible, allowing for use in vivo, for the monitoring of analyte blood concentrations such as blood glucose concentrations.

The present invention relates to an enzymatic electrode comprising a conductive surface and wherein a conjugate comprising at least one enzyme molecule is covalently bound to the conductive surface. The electrode is suitable for continuous analyte monitoring, particularly for continuous glucose monitoring (CGM) with glucose oxidase (GOD) as enzyme molecule. Further, the invention relates to an electrochemical sensor for measuring the concentration of an analyte, e.g. glucose under in vivo conditions comprising the enzymatic electrode.

A method can include receiving, using one or more processors, a first record including a first data associated with a personal identification from a first database, receiving, using the one or more processors, a second record including a second data associated with a user identification from a second database, pairing, using the one or more processors, the first data and the second data based upon a shared data item contained in the first record and the second record, and displaying, using one or more processors, a report based upon the first data and the second data.

By using a mutant glucose oxidase comprising an amino acid sequence in which a residue corresponding to isoleucine at position 489 or arginine at position 335 in the amino acid sequence of SEQ ID NO:1 is substituted with an amino acid residue having a reactive functional group in a side chain, and binding an electron acceptor to the mutant glucose oxidase through the amino acid residue having a reactive functional group, an electron acceptor-modified glucose oxidase is obtained.

Analyte sensors and methods for fabricating analyte sensors are provided. In an exemplary embodiment, a method for fabricating a planar flexible analyte sensor includes sputtering platinum onto a polyester base layer to form a layer of platinum. The method includes patterning the layer of platinum to form working electrodes and additional electrodes. Further, the method includes forming an insulating dielectric layer over the base layer, wherein the insulating dielectric layer is formed with openings exposing portions of the working electrodes and portions of the additional electrodes. Also, the method includes partially singulating individual sensors from the base layer, wherein each individual sensor is connected to the base layer by a tab. The method further includes depositing an enzyme layer over the exposed portions of the working electrodes and coating the working electrodes with a glucose limiting membrane.