An Effective Amperometric Biosensor Based on Gold Nanoelectrode Arrays
© to the authors 2008
Received: 21 October 2008
Accepted: 25 November 2008
Published: 9 December 2008
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© to the authors 2008
Received: 21 October 2008
Accepted: 25 November 2008
Published: 9 December 2008
A sensitive amperometric biosensor based on gold nanoelectrode array (NEA) was investigated. The gold nanoelectrode array was fabricated by template-assisted electrodeposition on general electrodes, which shows an ordered well-defined 3D structure of nanowires. The sensitivity of the gold NEA to hydrogen peroxide is 37 times higher than that of the conventional electrode. The linear range of the platinum NEA toward H2O2is from 1 × 10−6to 1 × 10−2 M, covering four orders of magnitudes with detection limit of 1 × 10−7 M and a single noise ratio (S/N) of four. The enzyme electrode exhibits an excellent response performance to glucose with linear range from 1 × 10−5to 1 × 10−2 M and a fast response time within 8 s. The Michaelis–Menten constantk m and the maximum current densityi maxof the enzyme electrode were 4.97 mM and 84.60 μA cm−2, respectively. This special nanoelectrode may find potential application in other biosensors based on amperometric signals.
Biosensors based on electrochemistry are now attracting considerable attention as potential successors to a wide range of analytical techniques due to their unique properties of specificity [1–3]. The key aspect of an electrochemical biosensor is the generation or modulation of electrical current in an electronic circuit between the bio-reaction or bio-recognition systems and the electronic elements. The high demand for selection and sensation requires not only the appropriate biological macromolecules with high active, but also the suitable substrates with biocompatible surroundings and efficient transport of electrons, but it is difficult for conventional electrodes to satisfy the demands. To that end, specific materials and structures with novel biocompatibility, stability, and electron transport property are demanded, for example, the intensively investigated nanomaterials [4, 5].
Nanomaterials, especially the one-dimensional nanostructures such as carbon nanotubes (CNT)  and metal , semiconductor , or conducting polymer  nanowires or nanotubes, are particularly attractive for biosensor application due to their unique advantages including high surface-to-volume ratio, elevated electrochemical activity, and eminent electron communication features. Usually, nanotubes and nanowires are incorporated into the functional systems by a variety of methods, such as solution evaporation , sol–gel encapsulation , and polymer-assisted dispersion . These methods generally result in disarrayed and layered films with the absorbed catalytic enzyme sites partially blocked and the substrate transport to the enzymes hindered , leading to a low amperometric responses upon bio-electrocatalysed oxidation or reduction of the analyte. To overcome this problem, perpendicularly aligned nanotube or nanowire arrays can be formed as sensing devices [7, 14, 15], which will lead to an increment of enzyme content associated with the electrode surface, an improvement of electrical communication between the redox center and the electrode, and thus an enhancement of the transduced amperometric signal.
Metal gold is one of the mostly used noble metals in biosensors; several reports have demonstrated that gold nanoparticles may be used as a hopping bridge of electrons generated from the enzyme catalytic redox reaction [16–18]. Besides facilitating the transfer of electrons, gold nanoparticles can also provide a biocompatible environment for proteins, since they are not toxic to the biological systems [19, 20]. Gold nanoparticles are an excellent candidate for replacing potentially harmful mediators in the construction of biosensors.
In this paper, we fabricated the gold nanoelectrode array (NEA) in the template of polycarbonate (PC) membranes. Free standing nanostructured gold nanowire arrays were obtained by direct electrodepositing on the conventional gold electrode, analogous to ultramicroelectrode ensembles reported by Penner et al. . The whole system can be considered as a modified electrode consisting of millions of nanowires which contact well with the substrate electrode; the diameter of each nanowire is about 450 nm and the length is even 4 μm. The 3D nanowire array results in large electroactive surface area, which is about five times as large as the conventional gold electrode. The high electroactive surface can not only enhance the sensitivity to hydrogen peroxide, but also provide large space for the loading of the enzymes. Considering the advantages of NEA and biocompatibility of metal gold, we put the gold NEA into the use of enzymes biosensors, which showed high sensitivity and wide linear range.
The track-etch polycarbonate membranes (PC membranes) with a pore diameter of 450 nm as template were purchased from Whatman (USA), the plating agent of gold sodium sulfite (Na3Au(SO3)2, 50 g/L) was provided by Changzhou Chemical Research Institute, sodium sulfite (Na2SO3, 99.5%), sodium hydroxide (NaOH, 99.5%), dichloromethane (CH2Cl2, 99.5%), potassium hexacyanoferrate (III) (K3Fe(CN)6, 99.5%), potassium hexacyanoferrate (II) (K4Fe(CN)6, 99.5%), bovine serum albumin (BSA), glutaraldehyde (25%) andd(+)-glucose (99.5%) were all purchased from Sinopharm Chemical Reagent Co., Ltd, China, and glucose oxidase (GOD, EC 126.96.36.199, from Aspergillus niger, 15,200 units/g solid) was bought from Sigma. A 1/15 M phosphate buffer (PB, pH 6.98) solution which prepared using Na2HPO4and KH2PO4was employed as supporting electrolyte during the electrochemical measurements. All other chemicals were reagent grade and all solutions were prepared from double-distilled water.
The cyclic voltammetry (CV) measurements and amperometric response measurements of NEA was performed on a Solartron electrochemical interface (Model 1287) while the electrochemical impedance spectrum (EIS) measurements were carried out on the Solartron impedance/gain-phase analyzer (Model 1260). A conventional three-electrode system was used in all the above measurements. NEA and NEA/GOD were used as working electrode, Ag/AgCl was used as reference electrode, and a spiral platinum wire acted as a counter electrode. The CVs and EISs were recorded in 5 mM [Fe(CN)6]3−/4−containing 0.1 M KCl. The potential amplitude was kept as 10 mV and the measured frequency range was 10−1–105 Hz in EIS experiments. All measurements were carried out at room temperature.
Before modification, the NEA was washed successively using Piranha (3:1 v/v mixture of concentrated H2SO4and H2O2), ethanol, and water. The GOD was immobilized on the NEA and Au electrodes by first forming a GOD/BSA solution comprising of glucose oxidase (10 mg/ml) and bovine serum albumin (5 mg/ml) dissolved in buffer. Then 2 μL glutaraldehyde was added to 10 μL GOD/BSA solution and mixed rapidly. About 3 μL of the intermixture was cast onto the electrode, and air dried at 4 °C.
The simulated curves based on the equivalent electrical circuit in Fig. 6fit well with the experimental EIS spectra. TheR ctof the NEA/GOD electrode is 453 Ω, which is apparently smaller than that of the Au/GOD electrode (3,362 Ω). The CPE of the NEA/GOD electrode is 3.1 μF, which is smaller than that of the Au/GOD electrode (4.9 μF). This can be ascribed to the structural difference of the electrodes. The surface of the bare Au electrode is flat, which can be described as two dimensions, while the nanowire array electrode fills three dimensions. The GOD spread as a compact film on the bare Au electrode, while it can fill in the space of nanowires on the NEA electrode. The gold nanowires effectively improved the conductivity of the NEA/GOD electrode and thus decreased the charge-transfer resistance. The special structure of the NEA/GOD electrode also led to a small CPE. The EIS analysis indicates that the three-dimensional structure of the NEA/GOD electrode is advantageous for the charge-transfer, which is an excellent characteristic for amperometric biosensors.
where i s is the steady-state current, C g is the concentration of glucose, k m is the apparent Michaelis–Menten constant and i max is the maximum current. From the curve of the i s −1 versus C g −1, based on the experimental data from Fig. 7b, the apparent Michaelis–Menten constant k m and the maximum current density i max were estimated to be 4.97 mM and 84.60 μA cm−2. The small k m means that the immobilized GO x possesses a high enzymatic activity and the proposed electrode exhibits a high affinity for glucose . The GOD/NEA enzyme electrode also shows high stability for glucose detection, which retains about 80% of its original response after 3 months of storage. The decrease of response to glucose may be due to the loss of the activity of the immobilized glucose oxidase, since the gold NEA electrode shows excellent stable performance on measuring hydrogen peroxide.
In this work, we prepared a novel gold NEA that shows better electrochemical properties than conventional Au electrode. Biosensors based on this nanostructure have improved analytical performances compared to the conventional electrode. Specifically, the biosensor shows a wider linear response to glucose in the range from 1 × 10−5to 1 × 10−2 M and a higher maximum current density. A fast response time within 8 s and a very high response current density of 84.60 μA cm−2were achieved. The apparent ichaelis–Menten constant of 4.97 mM also shows good affinity to glucose. The above facts indicate that the gold nanowire array electrode may be also used in the fabrication of other biosensors based on oxidases, such as biosensors for choline, cholesterol, and alcohol.
The research was partially financially supported from the Nation Natural Science of China (20571082, 50772125), the Science and Technology Commission of Shanghai (08JC1420700), and the National High Technology Research and Development Program of China.