In order to reduce the amount of silver（Ag）filler in the conductive epoxy adhesive composition, a mixture paste of epoxy/block copolymer blend with in-situ formed silver filler was prepared. First, polymethyl methacrylate（PMMA）-b-poly n-butyl acrylate（PnBA）-b-PMMA triblock copolymer was dissolved in a liquid amine hardener, while heating. Meanwhile, silver carbonate was reduced with a small amount of alkylamine to prepare Ag nanofiller slurry. The conductive epoxy composite paste was obtained by blending both with epoxy oligomer and removing the solvent. Electron microscopic observation for the cured composites revealed that the blend matrix formed co-continuous phase structure with PnBA phases having a thickness of several tens of nanometers. The alkylamine-coated Ag nanofillers were selectively placed in the PnBA continuous phase. As a result, electrical conductivity was detected in the composition with even low Ag filler content（5 vol%），due to the formation of conductive channels at the low filler content. Hansen solubility parameters（HSPs）of epoxy/amine reactants, PnBA, and alkylamine-coated Ag fillers were measured and the mechanism of the selective placement of Ag fillers was discussed in terms of the affinity between the components.

Second-generation acrylic adhesive （SGA）has excellent characteristics such as rapid curing at room temperature and high strength after curing, and is widely used in the assembly process of manufactured products. SGA is highly suitable material for stress analysis with cohesive zone model of adhesion structure because the fracture during the adhesion tests often occurs in the adhesive layer. It is important to understand the fracture process under various stress states of the material in order to obtain the proper analytical results. This study aims to investigate the fracture process of the SGA bonded scarf joints with steel substrate using acoustic emission（AE）and strain distribution during the strength tests and fractographic analysis. Microscopic observation of the fractured surface showed that cracks occurred in the acrylic-rich phase along the substrate surface and was followed with crack propagation thorough the elastomer-rich phase for all scarf angles. Shear-induced plastic deformation during the crack propagation in the elastomer-rich phase expanded with increasing scarf angle. A large number of AE signals with higher energy were detected in specimens with scarf angles of 0°and 30°, but there are fewer in specimens with scarf angles of 60°and 90°. This phenomenon suggests that AE signals with higher energy are correlated to occurrence of crack in acrylic-rich phase. The fractured surface, AE generation, and strain distribution changed significantly when the specimen had a scarf angle of 60°or more, and the fracture mode transitioned from tensile-dominated type to sheardominated type.

The creation of antifouling materials is required in various fields such as the environment, energy, and medicine. In particular, biocompatible materials that do not adsorb biological components or induce biological reactions are indispensable to ensure the performance and safety of medical devices during treatments. Biomimetic science, which mimics the structure and molecular functions of living organisms, has produced highly functional materials. It has been realized a polymer that does not induce biological fouling by molecular design mimics the structure of cell membranes. A polymer that possesses a representative phospholipid polar group, phosphorylcholine group, 2-methacryloyloxyethyl phosphorylcholine（MPC）polymer is one of the excellent examples. The interface between the MPC polymer surface and the aqueous phase has a characteristic water structure that can inhibit the formation of protein adsorption layers and cell adhesion. This is due to a phosphorylcholine group in the MPC polymer. The MPC polymer has been widely used as a surface treatment material for medical devices worldwide. Moreover, biomimetic chemistry using the catechol group is also described to bind the MPC polymer to the surface of medical devices in a stable and simple process.