Abstract
Electronic detection of biomolecules, although still in its early stages, is gradually emerging as an effective alternative to optical detection methods. We describe field effect transistor devices with carbon nanotube conducting channels that have been developed and used for biosensing and biodetection. Both transistors with single carbon nanotube conducting channels and devices with nanotube network conducting channels have been fabricated and their electronic characteristics examined. The devices readily respond to changes in the environment, and such effects have been examined using gas molecules and coatings with specific properties. Device operation in (conducting) buffer and in a dry environment—after buffer removal—is also discussed. Applications in the biosensing area are illustrated with three examples: the investigation of the interaction between devices and biomolecules, the electronic monitoring of biomolecular processes, and attempts to integrate cell membranes with active electronic devices.
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Notes
Comment on 20, Balavoine et al (1999) Angew Chem Int Edit 38:1912 (Helical crystallization of proteins on carbon nanotubes: a first step towards the development of new biosensors): Of course, proteins are easily immobilized on other surfaces, including the silicon substrate onto which the nanotube conducting channels are deposited. The presence of biomolecules on a surface that does not participate in the conduction process will, however, not influence the device’s characteristics.
Comment on 29, Bradley et al (2004) Nano Lett 4:253 (Charge transfer from adsorbed proteins): The number of amine groups can also be estimated using a simple model in which roughly spherical proteins cover the top half of the cylindrical nanotube. The proteins are assumed to coat the available nanotube surface with amine groups proportional to the surface area in contact. The nanotube under consideration here has a diameter of 24 nm (as reflected in the small bandgap observed in Fig. 7a), so that the surface area in contact with each 5 nm protein is π/2×2.4×5 nm2. Each protein surface contains 100 amine groups distributed over the 5 nm sphere, so that on average each protein contacts the nanotube with 20 amine groups. Since the proteins are 5 nm in diameter, we assume that 200 proteins are adsorbed on the 1 mm nanotube. Thus the monolayer of adsorbed protein contacts the nanotube with 4000 adsorbed amine groups, again in good agreement with what one finds by examining the transistor charge characteristics
Detailed experiments performed by us (M. Briman and G. Gruner, to be published) using a setup similar to described in [41, 42] demonstrate that conduction through the buffer leads to negligible effect. The transistor characteristics, however, depend on the pH, and such dependence has to be taken into account when the effect of biomolecules on the transistor characteristics is evaluated.
This asymmetry is reflected in the large amount of charge induced in mixed-orientation devices, since without an asymmetry, the charge induced by equal amounts of cytoplasmic-oriented and extracellular-oriented PM should cancel.
The background charge due to the phosphate heads of the lipids is 0.2 electrons per square nanometer [25], which is too weak to explain the charge induced in our devices.
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Acknowledgements
Many of the experiments reported here were performed by K. Bradley, M. Briman, A. Star, and the devices were fabricated by J.C. Gabriel and D. Hecht. This work was partially supported by the National Science Foundation Grant no. 0415130. Many of the experiments were performed at Nanomix Inc., the company where the author was Chief Scientist.
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Gruner, G. Carbon nanotube transistors for biosensing applications. Anal Bioanal Chem 384, 322–335 (2006). https://doi.org/10.1007/s00216-005-3400-4
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DOI: https://doi.org/10.1007/s00216-005-3400-4