An all-solution electrode fabrication process is provided. The process comprises the steps of: i) preparing and activating a shrinkable polymer substrate for deposition of a a) conductive film; ii) modifying the substrate to incorporate a linker; iii) immobilizing particles of a conductive material on the linkers of the substrate to form a conductive film on the substrate; and vi) heating the modified substrate to a temperature sufficient to cause contraction of the polymer substrate and to result in micro- and/or nano-texturing in the conductive film. The process advantageously yields a novel multi-scale electrode device comprising a polymer substrate; and a textured electro-conductive film linked to the substrate.

A sensor device is for detecting metal. The sensor device may have a substrate, an electrode on the substrate, and a biopolymer-metal composite film on the electrode. The biopolymer-metal composite film may include a metal and a biopolymer. The sensor device may further have circuitry coupled to the electrode and configured to apply a sensing signal to the electrode.

An electrocardiography patch is provided. A backing has an elongated strip with a midsection connecting two rounded ends. The midsection tapers in from each of the rounded ends and is narrower than each of the two rounded ends. Each electrode, of a pair of electrodes, is positioned on one of the rounded ends of the backing, on a contact surface, to capture electrocardiographic signals. A flex circuit is coupled to each of the electrodes. A non-conductive receptacle is affixed on an outer surface of the backing, opposite the contact surface. Electrical contacts are provided on a surface of the non-conductive receptacle opposite the backing. A battery is provided on the outer surface of the backing and a processor is powered by the battery to write the electrocardiographic signals into memory.

A method for producing an analyte sensor is disclosed. A first substrate having a first side and a second side is provided. The second side has a first layer having a first conductive material. A second substrate having a first side and a second side is provided. The first side has a second layer having a second conductive material. The second side of the second substrate has a third layer having a third conductive material. A conductive preparation is applied onto at least one of the first side of the first substrate and the third layer or a portion thereof to form a conductive preparation layer. The conductive preparation has conductive particles and a polymeric binder. The first side of the first substrate is laminated with the second side of the second substrate. An analyte sensor is obtained.

An electrocardiography patch is provided. A backing includes two rounded ends connected by a middle section that is narrower than the two rounded ends. An electrode is positioned on a contact surface of the backing on each rounded end. A circuit trace is electrically coupled to each of the electrodes. A battery is positioned on an outer surface of the backing, opposite the contact surface, on one of the rounded ends.

An electrocardiography monitor is provided. A sealed housing includes one end wider than an opposite end of the sealed housing. Electronic circuitry is provided within the sealed housing. The electronic circuitry includes an electrographic front end circuit to sense electrocardiographic signals and a micro-controller interfaced to the electrocardiographic front end circuit to sample the electrocardiographic signals. A buzzer within the housing outputs feedback to a wearer of the sealed housing.

The present disclosure relates to systems, devices, and methods for nucleic acid sequencing including polynucleotide strands having a nucleotide(s) modified with a redox label(s) attached thereto or capable of receiving the modified nucleotide(s) with a redox label(s) attached thereto. The systems, devices, and methods include a dielectric member with an attached translocating protein positioned between oxidizing and reducing electrodes. The oxidizing and reducing electrodes generate an electrical field extending to a reaction area where the translocation of the polynucleotide strand through the protein occurs such the modified nucleotide(s) with redox label(s) attached thereto are identified by changes in current flow in the oxidizing and reducing electrodes, wherein the changes identify electron transfer from the reducing electrode, to redox label, and to oxidizing electrode when the modified nucleotide with a redox label covalently bonded to the nucleoside base of the modified nucleotide of the polynucleotide strand is at the reaction area.

An electrochemical oxygen sensor includes a sensing surface having a working electrode and a reference electrode, a hydrophilic layer formed from an oxygen diffusion-limiting layer emulsion overlaying the working electrode and a hydrophobic membrane formed from a hydrophobic solution disposed over the hydrophilic layer. The hydrophilic layer contains an epoxy network and a hydrophilic polymer. The hydrophobic layer contains an acetate copolymer and a cross-linking agent that reacts with the liquid epoxy resin in the hydrophilic layer forming the epoxy network where the hydrophobic member is water vapor and oxygen permeable.

An electrocardiography patch is provided. A backing includes an elongated strip with a midsection connecting two rounded ends. The midsection tapers in from each end and is narrower than each of the two ends. An electrode is positioned on each end of the backing on a contact surface to capture electrocardiographic signals. A circuit trace electrically is coupled to each of the electrodes in the pair. A battery is provided on an outer surface of the backing opposite the contact surface. Memory is provided on the outer surface of the backing to store data regarding the electrocardiographic signals. A processor is powered by the battery to write the data into the memory.

The presence of oxygen or red blood cells in a sample applied to an electrochemical test strip that makes use of a reduced mediator is corrected for by an additive correction factor that is determined as a function of the temperature of the sample and a measurement that reflects the oxygen carrying capacity of the sample. The measured oxygen carrying capacity can also be used to determine hematocrit and to distinguish between blood samples and control solutions applied to a test strip.