Tatsuya Hoshino

Amperometric biosensor based on multilayer containing carbon nanotube, plasma-polymerized film, electron transfer mediator phenothiazine, and glucose dehydrogenase.

We report on a novel fabrication approach of amperometric biosensor based on multilayer films containing carbon nanotubes (CNT), a nano-thin plasma-polymerized film (PPF), electron transfer mediator phenothiazine (PT), and enzyme glucose dehydrogenase (GDH). The configuration of the electrochemical electrode is sequentially composed of sputtered gold, acetonitrile PPF, PT, GDH, and acetonitrile PPF (denoted as PPF/GDH/PT/CNT/PPF/Au). First PPF deposited on Au acts as a permselective membrane and as a scaffold for CNT layer formation. Second PPF directly deposited on GDH acts as a matrix for enzyme immobilization. To facilitate the electrochemical communication between the CNT layer and GDH, CNT was treated with nitrogen plasma. The electron transfer mediator PT plays a role as the mediator in which the electron caused by enzymatic reaction transports to the electrode. The synergy between the mediator and CNT provides benefits in terms of lowering the operational potential and enhancing the sensitivity (current). The optimized glucose biosensor revealed a sensitivity of 5.1 ± 0.9 μA mM(-1) cm(-2) at + 0.2V vs. Ag/AgCl, linear dynamic range of 4.9-19 mM, and a response time of 5 ± 1 s. Unlike conventional wet-chemical processes that are incompatible with mass production techniques, this dry-chemistry procedure has great potential for enabling high-throughput production of bioelectronic devices. Furthermore, those devices can be applied and expands for the cell biological functional field as a useful, helpful, or indispensable tool.

Enzyme biosensor based on plasma-polymerized film-covered carbon nanotube layer grown directly on a flat substrate

We report a novel approach to fabrication of an amperometric biosensor with an enzyme, a plasma-polymerized film (PPF), and carbon nanotubes (CNTs). The CNTs were grown directly on an island-patterned Co/Ti/Cr layer on a glass substrate by microwave plasma enhanced chemical vapor deposition. The as-grown CNTs were subsequently treated by nitrogen plasma, which changed the surface from hydrophobic to hydrophilic in order to obtain an electrochemical contact between the CNTs and enzymes. A glucose oxidase (GOx) enzyme was then adsorbed onto the CNT surface and directly treated with acetonitrile plasma to overcoat the GOx layer with a PPF. This fabrication process provides a robust design of CNT-based enzyme biosensor, because of all processes are dry except the procedure for enzyme immobilization. The main novelty of the present methodology lies in the PPF and/or plasma processes. The optimized glucose biosensor revealed a high sensitivity of 38 μA mM(-1) cm(-2), a broad linear dynamic range of 0.25-19 mM (correlation coefficient of 0.994), selectivity toward an interferent (ascorbic acid), and a fast response time of 7 s. The background current was much smaller in magnitude than the current due to 10 mM glucose response. The low limit of detection was 34 μM (S/N = 3). All results strongly suggest that a plasma-polymerized process can provide a new platform for CNT-based biosensor design.

Electronically type-sorted carbon nanotube-based electrochemical biosensors with glucose oxidase and dehydrogenase.

An electrochemical enzyme biosensor with electronically type-sorted (metallic and semiconducting) single-walled carbon nanotubes (SWNTs) for use in aqueous media is presented. This research investigates how the electronic types of SWNTs influence the amperometric response of enzyme biosensors. To conduct a clear evaluation, a simple layer-by-layer process based on a plasma-polymerized nano thin film (PPF) was adopted because a PPF is an inactive matrix that can form a well-defined nanostructure composed of SWNTs and enzyme. For a biosensor with the glucose oxidase (GOx) enzyme in the presence of oxygen, the response of a metallic SWNT-GOx electrode was 2 times larger than that of a semiconducting SWNT-GOx electrode. In contrast, in the absence of oxygen, the response of the semiconducting SWNT-GOx electrode was retained, whereas that of the metallic SWNT-GOx electrode was significantly reduced. This indicates that direct electron transfer occurred with the semiconducting SWNT-GOx electrode, whereas the metallic SWNT-GOx electrode was dominated by a hydrogen peroxide pathway caused by an enzymatic reaction. For a biosensor with the glucose dehydrogenase (GDH; oxygen-independent catalysis) enzyme, the response of the semiconducting SWNT-GDH electrode was 4 times larger than that of the metallic SWNT-GDH electrode. Electrochemical impedance spectroscopy was used to show that the semiconducting SWNT network has less resistance for electron transfer than the metallic SWNT network. Therefore, it was concluded that semiconducting SWNTs are more suitable than metallic SWNTs for electrochemical enzyme biosensors in terms of direct electron transfer as a detection mechanism. This study makes a valuable contribution toward the development of electrochemical biosensors that employ sorted SWNTs and various enzymes.

Amperometric Biosensor Based on Carbon Nanotube Functionalized by Redox Plasma-Polymerized Film

A novel fabrication approach for the amperometric biosensor based on multilayer films containing carbon nanotubes (CNT), a plasma-polymerized film (PPF), and enzyme glucose oxidase (GOD) is reported. The configuration of the electrochemical electrode is sequentially composed of sputtered gold, lower acetonitrile PPF, CNT, redox PPF, GOD, and upper acetonitrile PPF (denoted as PPF/GOD/Redox-PPF/CNT/PPF/Au). The lower acetonitrile PPF deposited on Au acts as a permselective membrane, and as a scaffold for CNT layer formation. The upper acetonirile PPF directly deposited on GOD acts as a matrix for enzyme immobilization. The redox PPF polymerized by a monomer of dimethlyaminomethlyferrocene (DAF) is directly deposited onto CNTs. The surface of the functionalized CNT has redox sites of ferrocene groups that shuttle electrons from CNTs to the sensing surface of the Au electrode. The synergy between the redox PPF and CNT provides benefits in terms of lowering the operational potential and enhancing the sensitivity (current). The optimized glucose biosensor revealed a sensitivity of 2.0 µA mM-1 cm-2 at +0.4 V vs Ag/AgCl, a linear dynamic range of 4.9–27 mM, and a response time of 5 s.