Short communicationChemical and biological sensing applications based on graphene field-effect transistors
Introduction
Systems for detecting simple biomolecules have become increasingly important in the field of life sciences. Generally, optical detection methods are used in conventional biosensors. Although optical detection is extremely sensitive, this approach needs expensive instruments, professional knowledge of labeling processes, fluorescent dyes and complex experimental techniques. Electrical detection of biomolecules by using nanomaterials such as silicon nanowiress (Cui et al., 2001, Elfström et al., 2008) and carbon nanotubes (Sánchez-Acevedo et al., 2009, Kim et al., 2009, Maehashi et al., 2007, Maehashi et al., 2009, Okuno et al., 2007) have been intensively investigated in past decade with respect to application to diagnostic biochips. Among these biosensing techniques using carbon nanotubes are among the most promising candidates for label-free biosensing, owing to their high aspect ratio and outstanding electrical characteristics. Several label-free biosensors based on carbon nanotube technology have been reported, including electrical detection of bisphenol A (Sánchez-Acevedo et al., 2009), a prostate cancer marker (Kim et al., 2009, Okuno et al., 2007) and immunoglobulins (Maehashi et al., 2007, Maehashi et al., 2009). However, controlling the diameter of carbon nanotubes remains a critical issue, because the electrical characteristics of carbon nanotubes strongly depend on their diameter and metal work function (Chen et al., 2005). At present, diameter-controlled carbon nanotube growth has not been successfully achieved.
Graphene, which consists of single to several layers of crystalline carbon, can potentially be used to address these problems. Graphene is a zero-gap semiconductor whose conduction band and valence band are connected at the K-point. Therefore, the transport characteristics of graphene exhibit distinctive ambipolar behavior with high minimum conductivity. Single-layer graphene has extremely high carrier mobility (>20,000 cm2/Vs at room temperature) with large carrier concentrations (∼1012 cm−2); furthermore, the material consists of highly stable, perfectly two-dimensional carbon crystal (Geim and Novoselov, 2007, Novoselov et al., 2004). Graphene is expected to have potential applications in next-generation high-speed logic devices (Lin et al., 2009). In particular, chemical and biological sensors based on graphene technologies has advanced rapidly in recent years, owing to the high stability of the material. Sensors using graphene or graphene oxide have been developed for the electrochemical detection of glucose (Kang et al., 2009, Shan et al., 2010), and solution pH sensors using few-layer epitaxial graphene on a 6H–SiC substrate have been demonstrated (Ang et al., 2008). Binding reactions occur close to the surface of graphene field-effect transistors (G-FETs); accordingly, detection of gas molecules (Schedin et al., 2007) and biomolecules (Mohanty and Berry, 2008, Ohno et al., 2009) has been reported. In graphene, high carrier mobility is only achieved in single-layer graphene due to its linear energy dispersion at K-point (Nagashio et al., 2008). Since the sensitivity using FET-based chemical and biological sensors depend on their transconductance (=∂ID/∂VG = CGVDμ; where CG and μ are the gate capacitance and field-effect mobility, respectively), G-FETs with single-layer graphene are thought to be suitable for the sensing devices.
In the present study, we carried out highly sensitive solution pH sensing and monitoring of the charge-type dependence of protein adsorptions onto the surface of graphene using single-layer G-FETs. As results, the lowest detection limit (signal/noise = 3) of the change in solution pH value was estimated to be 0.025 and the G-FETs could be electrically distinguished between positive and negative charged proteins in a buffer solution, indicating the high potential of G-FETs for applications in chemical and biological sensors.
Section snippets
Materials
Natural graphite used in this work was kindly provided by Nippon Graphite Industries Ltd. (Shiga, Japan). Phthalate buffer solution of pH 4.0, phosphate buffer solution of pH 6.8 and borate buffer solution of pH 9.3 was purchased from Horiba Ltd. (Kyoto, Japan). Solutions of various pH values were prepared by mixing a 10 mM phthalate buffer solution of pH 4.0, a 10 mM phosphate buffer solution of pH 6.8 and a 10 mM borate buffer solution at pH 9.3. Bovine serum albumin (BSA), which was used as the
Solution pH sensor
The drain current (ID) of the G-FET in buffer solution at various pH values is plotted against top-gate voltage (VTGS) at source-drain voltage of 0.1 V in Fig. 3A. For all devices, ID decreased as VTGS increased, and then ID subsequently increased, indicating the typical ambipolar characteristics derived from the band structure of the graphene (Novoselov et al., 2004). In this work, we used the pH range from 4.04 to 8.16 because the pH range have been often used for the biosensing. The G-FET
Conclusion
We have investigated chemical and biological sensors using G-FETs. Single-layer graphene was obtained by a micromechanical cleavage method. Changes in the solution pH were electrically detected with a lowest detection limit (signal/noise = 3) of the 0.025. In addition, the G-FETs clearly detected the different charge types of a biomolecule owing to its isoelectric point. G-FETs are promising devices for highly sensitive chemical and biological sensors.
Acknowledgments
This research was partially supported by the Core Research for Evolutional Science and Technology (CREST), the Japan Science and Technology Corporation (JST) and a Grant-in-Aid for Scientific Research on Priority Areas (No. 19054011) and Young Scientists (B) (No. 22760541) from the Ministry of Education, Culture, Sports, Science, and Technology of Japan.
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