Abstract: Disclosed are devices for determining an analyte concentration (e.g., glucose). The devices comprise a sensor configured to generate a signal associated with a concentration of an analyte and a sensing membrane located over the sensor. The sensing membrane comprises a biointerface layer which interfaces with a biological fluid containing the analyte to be measured. The biointerface layer comprises a biointerface polymer, wherein the biointerface polymer comprises polyurethane and/or polyurea segments and one or more zwitterionic repeating units. The biointerface layer increases sensor longevity and decrease sensor inaccuracy by inhibiting accumulation of cells, proteins, and other biological species on the outermost layers of the sensor.

Abstract: Disclosed are devices for determining an analyte concentration (e.g., glucose). The devices comprise a sensor configured to generate a signal associated with a concentration of an analyte and a sensing membrane located over the sensor. The sensing membrane comprises an enzyme layer, wherein the enzyme layer comprises an enzyme and a polymer comprising polyurethane and/or polyurea segments and one or more zwitterionic repeating units. The enzyme layer protects the enzyme and prevents it from leaching from the sensing membrane into a host or deactivating.

Abstract: Intravaginal drug delivery device comprising at least one pharmaceutically active substance, and a polyurethane copolymer, wherein the copolymer has the structure according to formula (I): Also, method comprising administering one or more pharmaceutically active substances to a patient in need thereof.

Abstract: The present disclosure relates to a needle including a wall structure, a cutting edge and a blunt contour. The needle advantageously can be used to deliver a sensor (such as a glucose or other analyte sensor) through an outer skin layer and into a sensor depth in a less invasive way than prior art needles. The size of the cutting edge is balanced against a portion of the distal wall structure that has blunt contours. Thus, the needle is capable of cutting the more durable outer skin layer (first phase) and then progressively stretching open the cut for further advancement into the subcutaneous layer (second phase). When the needle is sufficiently advanced, it is retracted leaving the sensor in a desired position. Early testing has shown a reduction of “dip and recover” from glucose sensors delivered using the needle.

Abstract: The present disclosure relates to a needle including a wall structure, a cutting edge and a blunt contour. The needle advantageously can be used to deliver a sensor (such as a glucose or other analyte sensor) through an outer skin layer and into a sensor depth in a less invasive way than prior art needles. The size of the cutting edge is balanced against a portion of the distal wall structure that has blunt contours. Thus, the needle is capable of cutting the more durable outer skin layer (first phase) and then progressively stretching open the cut for further advancement into the subcutaneous layer (second phase). When the needle is sufficiently advanced, it is retracted leaving the sensor in a desired position. Early testing has shown a reduction of “dip and recover” from glucose sensors delivered using the needle.

Abstract: The present disclosure relates to a needle including a wall structure, a cutting edge and a blunt contour. The needle advantageously can be used to deliver a sensor (such as a glucose or other analyte sensor) through an outer skin layer and into a sensor depth in a less invasive way than prior art needles. The size of the cutting edge is balanced against a portion of the distal wall structure that has blunt contours. Thus, the needle is capable of cutting the more durable outer skin layer (first phase) and then progressively stretching open the cut for further advancement into the subcutaneous layer (second phase). When the needle is sufficiently advanced, it is retracted leaving the sensor in a desired position. Early testing has shown a reduction of “dip and recover” from glucose sensors delivered using the needle.

Abstract: The invention is directed to an intravaginal drug delivery device comprising at least one pharmaceutically active substance, and a polyurethane copolymer, wherein the copolymer has the structure according to formula (I): The invention is further directed to administering one or more pharmaceutically active substances to a patient in need thereof.

Abstract: Intravaginal drug delivery device comprising at least one pharmaceutically active substance, and a polyurethane copolymer, wherein the copolymer has the structure according to formula (I): Also, method comprising administering one or more pharmaceutically active substances to a patient in need thereof.

Abstract: Sensor devices including dissolvable tissue-piercing tips are provided. The sensor devices can be used in conjunction with dissolvable needles configured for inserting the sensor devices into a host. Hardening agents for strengthening membranes on sensor devices are also provided. Methods of using and fabricating sensor devices are also provided.

Abstract: Polymer surface modification method comprising the steps of first forming a surface of primary reactive end groups tethered to the polymer chain ends during fabrication of an article, and then modifying the reactive surface with bio-active molecules, hydrophilic and hydrophobic monomers, oligomers, or polymers to attain specific surface properties. Alternatively, a multifunctional coupling agent can be used to couple the primary reactive group to a second reactive group capable of reacting with a functional group associated with bio-active molecules, hydrophilic and hydrophobic monomers, oligomers, and polymers to attain specific surface properties. The invention involves bringing reactive endgroups to the surface with surface active spacer attached to the polymer chain end. The surface active spacer allows the migration and enrichment of reactive end groups to the surface during fabrication.

Abstract: Sensor devices including dissolvable tissue-piercing tips are provided. The sensor devices can be used in conjunction with dissolvable needles configured for inserting the sensor devices into a host. Hardening agents for strengthening membranes on sensor devices are also provided. Methods of using and fabricating sensor devices are also provided.

Abstract: Polymer surface modification method comprising the steps of first forming a surface of primary reactive end groups tethered to the polymer chain ends during fabrication of an article, and then modifying the reactive surface with bio-active molecules, hydrophilic and hydrophobic monomers, oligomers, or polymers to attain specific surface properties. Alternatively, a multifunctional coupling agent can be used to couple the primary reactive group to a second reactive group capable of reacting with a functional group associated with bio-active molecules, hydrophilic and hydrophobic monomers, oligomers, and polymers to attain specific surface properties. The invention involves bringing reactive endgroups to the surface with surface active spacer attached to the polymer chain end. The surface active spacer allows the migration and enrichment of reactive end groups to the surface during fabrication.

Abstract: Sensor devices including dissolvable tissue-piercing tips are provided. The sensor devices can be used in conjunction with dissolvable needles configured for inserting the sensor devices into a host. Hardening agents for strengthening membranes on sensor devices are also provided. Methods of using and fabricating sensor devices are also provided.

Abstract: Silicone containing reactive monomers with hydrophilic end-groups of formula I useful in the manufacture of biocompatible medical devices are disclosed, wherein R1 is H or CH3, a is 0 or 1, p is an integer from 1 to 6, q is an integer from 1 to 3 and for each q, the end groups R51, R52, R53 are independently an alkyl, alkyl ether, trimethylsiloxy group, or a substituted or non-substituted aromatic group and at least one of them has a hydrophilic group attached, preferably to the terminal end of R51, R52, R53, X is O or NR54, where R54 is H or a monovalent alkyl group with 1 to 4 carbons, n is an integer from 1 to 100, R2 and R3 are independently an alkyl, alkyl ether, or a substituted or non-substituted aromatic group, preferred R2 and R3 include methyl, ethyl, and phenyl, L is a divalent linker comprising substituted and unsubstituted alkylene groups having 1-14 carbon atoms, which may be straight or branched, substituted and unsubstituted alkoxy groups having 2-12 carbons, polyethers, oxazolines, and substi

Abstract: The invention is directed to an intravaginal drug delivery device comprising at least one pharmaceutically active substance, and a polyurethane copolymer, wherein the copolymer has the structure according to formula (I): The invention is further directed to administering one or more pharmaceutically active substances to a patient in need thereof.

Abstract: Polymers having the formula R(LE)X wherein R is a polymeric core having a number average molecular weight of from 5000 to 7,000,000 daltons and x endgroups, E is an endgroup that is covalently linked to polymeric core R by linkage L, L is a divalent oligomeric chain having at least 5 identical repeat units that is capable of self-assembly with L chains on adjacent molecules of the polymer, and the moieties (LE)X in the polymer may be the same as or different from one another. Monomers, oligomers, or other reactive structures otherwise analogous to known Self Assembled Monolayers but with at least one reactive chemical group capable of binding them to the terminus of a polymer, so that the thiol-free SAM analogue becomes the self-assembling surface modifying endgroup of that polymer, may be designed. Use of the polymer to fabricate a configured article from the surface-modified polymer or to fabricate a coating or topical treatment on an article made from another material.

Abstract: Polymer surface modification method comprising the steps of first forming a surface of primary reactive end groups tethered to the polymer chain ends during fabrication of an article, and then modifying the reactive surface with bio-active molecules, hydrophilic and hydrophobic monomers, oligomers, or polymers to attain specific surface properties. Alternatively, a multifunctional coupling agent can be used to couple the primary reactive group to a second reactive group capable of reacting with a functional group associated with bio-active molecules, hydrophilic and hydrophobic monomers, oligomers, and polymers to attain specific surface properties. The invention involves bringing reactive endgroups to the surface with surface active spacer attached to the polymer chain end. The surface active spacer allows the migration and enrichment of reactive end groups to the surface during fabrication.

Abstract: Polymers with non-leaching antimicrobial activity and their use as surface coatings or bulk resins for medical devices. The antimicrobial polymers are prepared with antimicrobial moieties covalently bonded to a polymer chain end or to a polymer backbone at a side chain end. The antimicrobial moiety-containing endgroups include surface active (or surface assembling) moieties which promote enrichment of antimicrobial endgroups at the polymer surface and thus formation of an antimicrobially active surface. Polymers with built-in antimicrobial endgroups can be used as bulk resins, as antimicrobial additives, or as infection preventative coatings in the manufacture of medical devices (e.g., catheters, vascular access devices, peripheral lines, IV sites, drains, gastric feeding and tubes, and other implantable devices).

Abstract: Single ion conductors comprising polymer electrolytes prepared by grafting a salt compound onto a comb-branch polymer or dendrimer are disclosed having superior properties.

Abstract: Medical device, prosthesis, or packaging assembly made up of polymer body comprising at least one polymer having the formula R(LE)x wherein R is a polymeric core having a number average molecular weight of from 5000 to 7,000,000 daltons, and having x endgroups, x is an integer?1, E is an endgroup which is covalently linked to polymeric core R by linkage L, L is a divalent oligomeric chain which has at least 5 repeat units and which can self-assembly with L chains on adjacent molecules of the polymer, and moieties L and/or E in the polymer(s) may be the same as or different from one another in composition and/or molecular weight. The polymer body includes plural polymer molecules located internally within the body, at least some of which internal polymer molecules have endgroups that form a surface of the body. The surface endgroups include at least one self-assembling moiety.