Electrocatalytic h2 o2 amperometric detection using goldnanotube electrode ensembles


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Electrocatalytic h2 o2 amperometric detection using goldnanotube electrode ensembles

  1. 1. Analytica Chimica Acta 525 (2004) 221–230 Electrocatalytic H2 O2 amperometric detection using gold nanotube electrode ensembles Marc Delvauxa , Alain Walcariusb , Sophie Demoustier-Champagnea,∗ a Unit´ de Physique et de Chimie des Hauts Polym` res, Universit´ Catholique de Louvain, Place Croix du Sud, 1, e e e B-1348 Louvain-la-Neuve, Belgium b Laboratoire de Chimie Physique et Microbiologie pour l’Environnement, Unit´ Mixte de Recherche UMR 7564, CNRS, e Universit´ H. Poincar´ Nancy I, 405, Rue de Vandoeuvre, F-54600 Villers-les Nancy, France e e Received 5 March 2004; received in revised form 23 August 2004; accepted 23 August 2004 Available online 13 September 2004Abstract Arrays of nanoscopic gold tubes were prepared by electroless plating of the metal within the pores of nanoporous polycarbonate track-etched membranes. A procedure for fabricating an ensemble of enzyme-modified nanoelectrodes has been developed based on the efficientimmobilization of horseradish peroxidase (HRP) to the gold nanotubes array using self-assembled monolayers (mercaptoethylamine ormercaptopropionic acid) as anchoring layers. Hydrogen peroxide (H2 O2 ) was determined electrochemically by using gold nanoelectrodeensembles (NEE) functionalized or not in phosphate buffer solution (PB) with or without a mediator (hydroquinone, H2 Q). Bare NEE displaysa remarkable sensitivity (14 ␮A mM−1 in H2 Q at −0.1 V versus Ag/AgCl) compared to a classical gold macroelectrode (0.41 ␮A mM−1 ).The gold nanoparticles that form the tubular structure act as excellent catalytic surfaces towards the oxidation and the reduction of H2 O2 . TheHRP modified NEE presents a slightly lower sensitivity (9.5 ␮A mM−1 ) than bare NEE. However, this system presents an enhanced limit ofdetection (up to 4 × 10−6 M) and a higher selectivity towards the detection of H2 O2 over a wide range of potentials. The lifetime, fabricationreproducibility and measurement repeatability of the HRP enzyme electrode were evaluated with satisfactory results.© 2004 Elsevier B.V. All rights reserved.Keywords: Gold nanoelectrodes; Immobilized enzyme; Horseradish peroxidase; Hydrogen peroxide; Amperometric detection1. Introduction electrode sensitive to interferences from many electroactive species in real samples such as ascorbic and uric acids. Con- The detection and quantitative determination of hydro- sequently, a lot of work has focused on developing suitablegen peroxide is of practical importance in food, pharmaceu- electrocatalytic surfaces where these reactions proceed at re-tical, chemical, biochemical, industrial and environmental duced voltages. The usually small size metal particles (Pt,analyses. Numerous methods have been developed for this Pd, Ru, Rh, Ir, Au, Cu, etc.) allow a preferential oxidationpurpose, including spectrometry [1–3], chemiluminescence or reduction of hydrogen peroxide [14–20] without requiring[4–6], titrimetry [7,8] and electrochemistry [9–13]. additional reagents. In numerous papers [21–25], bimetallic Direct electrochemical detection of H2 O2 has been made alloys dispersed in a matrix (C paste, sol–gel, etc.) are nec-via its oxidation or reduction at a variety of electrode mate- essary to enhance the electrocatalytic detection of H2 O2 andrials but the detection requires operation at a relatively high biosensing of glucose or other analytes without sacrificingoverpotential (e.g. 0.7 V versus SCE for Pt), which makes the the selectivity. An attractive alternative approach is to exploit the high ∗ Corresponding author. Tel.: +32 10 473560. substrate specificity and the high activity of enzymes as bi- E-mail addresses: walcariu@lcpe.cnrs-nancy.fr (A. Walcarius), ological catalyst. Amperometric biosensors based on elec-demoustier@poly.ucl.ac.be (S. Demoustier-Champagne). tronic transfer between immobilized peroxidases, which0003-2670/$ – see front matter © 2004 Elsevier B.V. All rights reserved.doi:10.1016/j.aca.2004.08.054
  2. 2. 222 M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230catalysed the reduction of hydrogen peroxide, and the elec- both bare Au nanotubes and HRP modified Au nanotubestrode is promising for the fabrication of simple and low cost have been evaluated with and without a redox mediator. Theenzyme sensors. Horseradish peroxidase (HRP), a heme con- stability, repeatability and selectivity of the nanotubes-basedtaining glycoproteine, is the most thoroughly studied and sensors have also been investigated.used enzyme in the development of enzyme-based H2 O2 am-perometric sensors. Many approaches can be used for the immobilization of 2. Experimental sectionHRP on electrodes such as physical adsorption onto the sur-face of the electrode (e.g. pretreated carbon or graphite elec- 2.1. Reagents and solutionstrodes, Pt) [26–28], coverage with a polymer (conducting ornon-conducting) into which peroxidase molecules are phys- All materials and reagents were used as commer-ically or chemically attached and entrapment in bulk modi- cially received. Horseradish peroxidase (HRP, EC,fied composite electrodes, where HRP are distributed in the Type VI), 3-mercaptopropionic acid (MPA, >99%), 2-mixture (graphite oil paste, synthetic lipid films, redox hy- mercaptoethylamine (MPE, cysteamine, >98%) were pur-drogel [29–31]). Another approach has been developed by chased from Sigma–Aldrich. Hydroquinone (H2 Q, 99%), 4-Willner et al. [32,33] using self-assembled monolayers as an- acetaminodophenol (AC, 96%), uric acid (UA, >99%) andchor layer for the immobilization of biomolecules. Currently, l(+)-ascorbic acid (AA, 96%) were received from Acros.the well-characterized SAMs on metal electrodes are widely Ethanol (HPLC grade) and hydrogen peroxide (min. 27%)used for the immobilization, orientation and organization of were from Merck.biomolecules at interface. SAMs offer the analytical advan- Glutaraldehyde (GA, 25% in water, Sigma), 1-ethyl-3-tages of reducing the non-faradic backgrounds currents by (3-dimethylaminopropyl)carbodiimide hydrochloride (EDC,preventing close approach of solvents and ions to the elec- Acros), 2-(N-(morpholino)ethanesulfonic acid (MES, Acros)trode surface, provide a high degree of reproducibility and al- and N-hydroxysuccinimide (NHS, Acros) were used for co-low the immobilization, of a variety of biomolecules through valent coupling of enzymes. The phosphate buffer (PB) con-different functional head groups close to the electrode surface tained 0.1 M KH2 PO4 and 0.1 M K2 HPO4 .with a high degree of reproducibility. The accurate concentration of H2 O2 solution was deter- Gold electrodes have been increasingly used in designing mined by titration with potassium permanganate solution.electrochemical biosensors. However, enzyme immobiliza- Pure water, obtained by means of Millipore MilliQ water pu-tion on flat gold surfaces often suffers from low amounts rification set, was used throughout.of biomolecules and poor electrical contact to the transducer.Currently, most efforts are directed to two new directions: (1) 2.2. Electrochemical devices preparationproduction of composite electrodes made of gold nanoclus-ters and immobilized enzymes, which exploit the enhanced 2.2.1. Construction of gold nanotubes arrayscatalytic activity of the gold nanoparticles [34–40], and (2) Track-etched polycarbonate (PC) membranes with a porethe three-dimensional structuration of gold electrodes with density of 1 × 108 pores/cm2 , a pore diameter of 460 nmnanometer-sized dimensions for biosensor applications (e.g. and a thickness of 20 ␮m realized by the procedure devel-microporous gold electrodes [41], nanopatterning of porous oped in our lab [46] were used as templates. Electroless goldgold films [42] or gold nanoelectrode ensembles [43,44]). was deposited on the pore walls and both faces of the mem-Very recently, we reported on the fabrication of ensembles of brane according to the procedure described earlier [45]. Thegold nanotubes, aligned parallel to each other and presenting temperature of the deposition solution was 4 ◦ C. After de-uniform size and shape by electroless plating of gold into the position of gold for 17 h, the pore radius of the membranepores of nanoporous polycarbonate track-etched membranes was reduced to 320 nm. The gold-coated membrane (PC/Au)(nano-PTM) [45]. These nano-PTM are realized by an im- was immersed in 25% nitric acid for 12 h to clean the surfaceproved procedure developed in our lab [46]. By this template and remove any residual Ag, rinsed thoroughly with watermethod, it is possible to prepare cylindrical metallic nan- and dried in air. In order to avoid creeping of the solution be-otubes with an outer diameter ranging from 15 to 1000 nm tween the Au nanotubes and the PC pore walls, the samplesand an inner diameter that can be varied at will by modify- were heated above the glass-transition temperature (150 ◦ C)ing the gold deposition time. Arrays of gold nanotubes were of the PC for 15 min.functionalized through the immobilization of GOx enzymesusing SAMs as anchor layer. The resulting biosensor showed 2.2.2. Construction of HRP modified gold nanotubesa remarkable sensitivity to glucose in batch and in flow in- arraysjection amperometric measurements [47,48]. In this paper, The gold substrates were first freed from contaminants bywe report on the unique properties of gold tubes nanoelec- UV/ozone treatments and then immersed in ethanol to removetrodes ensembles for the electrochemical detection of H2 O2 . any gold oxide deposit before monolayer assembly. The func-HRP was immobilized within gold nanotubes through func- tionalized thiols assemblies were spontaneously adsorbed bytionalized alkylthiol SAMs. The analytical performances of immersing the membrane containing gold nanotubes into
  3. 3. M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230 223dilute (2 × 10−3 M) MPE or MPA solutions of absolute 100/206) spectrometer from Fisons, operating at a pressureethanol. in the low 10−8 Torr range, equipped with an aluminum an- After deposition overnight to ensure a complete coverage, ode and a quartz monochromator. Spectra were recorded at athe substrates were thoroughly rinsed with absolute ethanol takeoff angle of 35◦ (angle between the plane of the sampleand dried under a stream of nitrogen. surface and the entrance of the lens of the analyser). Curve The MPE-modified electrodes were activated for 2 h in fitting has been done using a Gaussian–Lorentzian (85–15%)a solution of GA (commercial solution diluted 100 times linear combination and a linear background.in phosphate buffer) at room temperature. The surface wasrinsed with buffer and immediately placed in a solution ofHRP (1 mg/ml) in PB for 2 h. The resulting enzyme-modified 3. Results and discussionnanoelectrodes are further noted PC/Au/MPE/GA/HRP. The terminal carboxylic acid groups of MPA-gold sur- 3.1. Fabrication and characterization of goldfaces were modified by dipping in a MES buffer solution nanoelectrodes arrays(pH = 3.5) containing 2 mM EDC and 5 mM NHS for 2 h. Af-ter being rinsed with buffer, the MPA–NHS ester monolayers Electroless plating of gold was carried out within the poreswere allowed to react for 2 h with a solution of PB containing of polycarbonate nano-PTM with a pore size of 460 nm, a1 mg/ml of the enzyme. The resulting enzyme-modified na- pore density of 1 × 108 pores cm−2 and a thickness of 20 ␮m,noelectrodes are further noted PC/Au/MPA/EDC,NHS/HRP. following the procedure described elsewhere [45]. FEG-SEM image (Fig. 1), recorded after dissolution of the PC membrane2.3. Instrumentation and measuring procedures in CH2 Cl2 , clearly shows that nanotubes running the entire thickness of the membrane are so obtained. Indeed gold de- Amperometric experiments were performed using an position proceeds from the activated pore walls rather thanEG&G Princeton Research 273A potentiostat/galvanostat. a base layer of metal. As a result, there is no competitionElectrochemical experiments were carried out in a conven- between elongating the tubules and closure of the tubules totional one-compartment cell with a three-electrode configu- form solid fibers. Increasing the plating time leads to a thick-ration holding 20 ml of the supporting electrolyte (phosphate ening of the tubules walls [45]. In this work, a depositionbuffer, PB or PB + 0.1 mM hydroquinone, H2 Q). The three- time of 17 h at 4 ◦ C was employed leading to the formationelectrode system consisted of gold nanotubes arrays placed of open nanoscopic channels with a thickness of 70 nm andbetween an Au disk and an O-ring with a surface area of a length of 20 ␮m. This deposition time is a good compro-0.071 cm2 as working electrode, an Ag/AgCl reference elec- mise between the need to have a void space inside the tubestrode and a Pt foil as counter electrode. large enough to allow the immobilization of a huge amount For comparison, a conventional Au foil electrode from of biomolecules and the need to have a mechanically sta-Goodfellow was also used as working electrode. We further ble system, robust enough to be used as an electrochemicalcall this conventional electrode “macroelectrode”. Gold films biosensor. A too thin gold layer cannot efficiently protect thewere cleaned by cycling potentials continuously between PC membrane against degradation by the reagents used in the−0.2 and 1.4 V versus Ag/AgCl in 0.1 M sulfuric acid at a different steps of functionalization.scan rate of 100 mV/s until reproducible scans were recorded. For amperometric experiments at controlled potential, thebackground current was allowed to decay to a steady valuebefore aliquots of stock hydrogen peroxide solution wereadded. All experiments were carried out at room tempera-ture. The solutions were purged with purified nitrogen for atleast 20 min to remove oxygen prior to each series of mea-surements. A magnetic stirrer and a stirring bar provided con-vective transport for the electrochemical experiments. Characterization of the morphology of gold nanotubes wascarried out by scanning electron microscopy (SEM) using ahigh resolution FEG digital scanning microscope 982 geminifrom LEO, operating at 1 kV. After Au electroless deposition,the templating membranes were dissolved by dipping themfor 2 min in dichloromethane. The free Au nanotubes werethen recovered from the solution by filtration through a silvermembrane, copiously rinsed with dichloromethane to removeany residual PC and then analysed using FEG-SEM. The surface chemical composition was determined at each Fig. 1. FE-SEM image of an array of Au nanotubes, recorded after dissolu-step of functionalization by XPS using a SSIX probe (SSX tion of the PC template membrane.
  4. 4. 224 M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230 Fig. 2. FE-SEM images of (a) the surface morphology of Au electroless deposited on nanoporous membranes (b) the surface of the commercial gold foil. The surface of a commercial gold foil was imaged by SEM responses of PC/Au/MPE/GA/HRP, bare PC/Au and bare Au(Fig. 2) in order to compare its morphology and roughness film (Goodfellow) to the injections of 5 × 10−4 M H2 O2 werewith the surface of electroless gold deposited on a PC mem- measured at different potentials in the range +0.3 to −0.8 Vbrane. Images in this figure are depicted at the same magnifi- versus Ag/AgCl in PB and PB + H2 Q (0.1 mM) solutionscation (50 000×) in order to emphasize the important differ- (Fig. 3a and b, respectively). Each point in both graphs isence in roughness between the two types of Au electrodes. the mean response of three consecutive additions of H2 O2 . AThe roughness of the electroless gold surface is much higher continuous increase of the reduction current up to −0.8 V wasthan that of evaporated gold foil. Indeed, gold nanotubes are observed for the three studied systems. However, significantmade of discrete gold particles with an average size of 30 nm. differences were observed between these three types of elec-Considering their high surface to volume ratio, these gold trodes. Indeed, Fig. 3 clearly shows that gold nanoparticlesnanoparticles are interesting materials for the catalytic ac-tion towards the electrooxidation and the electroreduction ofhydrogen peroxide. Hou et al. [49] demonstrated that suchroughly Au surfaces remained however compatible with theformation of densely packed alkylthiol SAMs. In our previousarticles [47,48], we also showed that glucose oxidase couldbe efficiently fixed on electroless gold surface using SAMs asanchoring layers. In this work, a similar procedure was usedto immobilize HRP within gold nanotube arrays. Two typesof thiol-functionalized monolayers (MPE and MPA) wereemployed as base nanoglue interfaces to link the enzymeto the electrode support. In the system modified with NH2terminated thiol (PC/Au/MPE), the HRP molecules were at-tached by using glutaraldehyde as linking agent. The covalentattachment of HRP to the carboxylic terminated SAM wasachieved via carbodiimide activation (EDC + NHS) of thecarboxylic acids to a reactive intermediate that can undergonucleophilic attack by amine moieties on free lysine chains ofthe enzyme. At the end of the functionalization pathways, thepresence of HRP enzyme immobilized on both types of sur-faces was clearly confirmed by XPS. Indeed, modificationsin the C1s region and the increase of N1s and O1s peak areaswith the concomitant reduction of the Au4f and S2p peaks arein agreement with the fixation of amino acids side chains ofa polypeptide backbone.3.2. Influence of gold surface on the electrochemical Fig. 3. Hydrodynamic voltammograms obtained using (᭹) bare Au, ( ) PC/Au/MPE/GA/HRP and ( ) PC/Au as working electrode for the analysisbehavior of hydrogen peroxide of 5.0 × 10−4 M hydrogen peroxide samples. (a) Electrolyte solution: 1.0 × 10−1 M phosphate buffer (pH = 7.2); (b) electrolyte solution: 1.0 × 10−1 M The hydrodynamic voltammograms for H2 O2 detection phosphate buffer (pH = 7.2) with addition of 1.0 × 10−4 M hydroquinoneat various gold electrodes were investigated. The steady-state in the medium.
  5. 5. M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230 225deposited PC membrane (PC/Au) have a remarkable electro- in PB and H2 Q solutions. These high faradic-to-capacitivecatalytic action towards the reduction of H2 O2 throughout all current ratios should give better properties, e.g. a lower limitthe investigated range of potentials both in phosphate buffer of detection for the resulting biosensor.and in hydroquinone solutions. Nano-PC/Au also catalysesthe hydrogen peroxide oxidation (data not shown), although 3.3. Electrode response characteristicsthis effect is less pronounced than in the case of H2 O2 re-duction. On the contrary, with or without any mediator in 3.3.1. Calibration of the sensorsthe solution, the response to hydrogen peroxide at bare Au In order to confirm the catalytic action of the electro-macroelectrode was very low. less gold nanoparticles deposited on PC membrane, the am- The sensitivity of the enzyme-modified nanoelectrodes perometric response to injections of H2 O2 on bare PC/Au,(PC/Au/MPE/GA/HRP) is between the sensitivity of bare Au PC/Au/MPE/GA/HRP and bare Au macroelectrode weremacroelectrode and that of nano-PC/Au. This lower sensitiv- compared at several fixed potentials (+0.1, 0, −0.1, −0.2,ity of the HRP modified Au nanotubes compared to bare Au and −0.5 V versus Ag/AgCl) in both PB and H2 Q solutions.nanotubes arises from the coverage of the gold nanoparti- In all cases, when an aliquot of H2 O2 was added into thecles by HRP molecules that considerably reduce the electro- solution, the reductive current rose steeply to reach a sta-less Au active electrode area. The advantages to functional- ble value. However, the response time and the amplitude ofize the gold electroless surface by fixation of HRP is however the current change were drastically different on each typedemonstrated in Fig. 4a and b, where the faradic-to-capacitive of electrode. PC/Au and PC/Au/MPE/GA/HRP systems ex-ratios for the different electrodes in a potential range from hibited a rapid and sensitive response to changes of H2 O2+0.3 to −0.8 V are reported. These graphs show that thanks concentration. These sensors reached 95% of the steady-to a low background current, the enzyme-modified nano- state current in less than 11 s for PC/Au and in only 8 selectrode (PC/Au/MPE/GA/HRP) gives the highest ratios for PC/Au/MPE/GA/HRP, indicating the excellent electro-throughout nearly all the investigated potential range, both catalytic behavior of the gold nanotubes electrode. The very fast response time of the enzyme-modified nanoelectrode may also be attributed to the favorable nano-environment of the nanotubes system that could contribute to stabilize the bi- ological activity of the HRP to a large extent. At the bare Au macroelectrode, a much longer response time of about 35 s was obtained and very much lower sensitivity was observed. All sensors (PC/Au/MPE/GA/HRP, bare PC/Au and bare Au macroelectrode) were tested by performing calibration curves for H2 O2 under the same experimental conditions. All the calibration curves were obtained at each potential and for each sensor by the measurement of at least 10 ad- ditions of H2 O2 . Fig. 5 depicts typical calibration curves for one representative electrode, the PC/Au/MPE/GA/HRP sensor, in the presence of hydroquinone by applying sev- eral potential values. The response increases with the ap- plied potential and is linear within the whole investigatedFig. 4. Faradic-to-capacitive current ratios obtained using (᭹) bare Au, ( )PC/Au/MPE/GA/HRP and ( ) PC/Au as working electrode for the analysisof 5.0 × 10−4 M hydrogen peroxide samples. (a) Electrolyte solution: 1.0 × Fig. 5. Hydrogen peroxide calibration plots obtained at detection poten-10−1 M phosphate buffer (pH = 7.2); (b) electrolyte solution: 1.0 × 10−1 M tial going from 0.1 to −0.5 V vs. Ag/AgCl using PC/Au/MPE/GA/HRP asphosphate buffer (pH = 7.2) with addition of 1.0 × 10−4 M hydroquinone working electrode in a 1.0 × 10−1 M deaerated phosphate buffer solutionin the medium. containing 1.0 × 10−4 M hydroquinone.
  6. 6. 226 M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230concentration range (5 × 10−5 to 3 × 10−3 M). Some cali-bration curves were also recorded for the different sensorson wider H2 O2 concentration ranges (1 × 10−5 to 15 ×10−3 M), in both PB solutions and in PB+H2 Q medium, ata detection potential of −0.1 V. For a better characteriza-tion of the enzyme-modified nanotube-based bioelectrode,the response of the PC/Au/MPA/EDC,NHS/HRP biosen-sor, in PB + H2 Q, was also evaluated. As expected fromprevious results, higher sensitivity for the reduction of hy-drogen peroxide was obtained with all the sensors basedon gold nanoparticles (PC/Au, PC/Au/MPE/GA/HRP andPC/Au/MPA/EDC,NHS/HRP). On the other hand, very lowcurrent responses to H2 O2 injection were obtained at the goldmacroelectrode. The PC/Au/MPE/GA/HRP biosensor provides a linearcurrent response to hydrogen peroxide in H2 Q over a con- Fig. 6. Sensitivity of the amperometric response to hydrogen peroxide ascentration range of 1 × 10−5 to 6 × 10−3 M with a a function of the applied potential for the (b, c) PC/Au/MPE/GA/HRP, (a)sensitivity of 9.5 ␮A mM−1 . In PB solution, the dynamic PC/Au/MPA/EDC,NHS/HRP, (d, e) PC/Au and the (f, g) Au macroelectrode sensor. Electrolyte solution 1.0 × 10−1 M deaerated phosphate buffer withrange is extended up to 10 mM but the sensitivity decreases and without 1.0 × 10−4 M hydroquinone.to a value of 1.5 ␮A mM−1 . A signal saturation was ob-served at H2 O2 concentration higher than 6 × 10−3 M. Thiscan be attributed to the saturation of the enzyme-substrate [50] brought new information about the control of the sur-or enzyme-mediator kinetic or may be due to the forma- face state of a polycrystalline gold. The need for operating attion, at high [H2 O2 ], of the enzymatically inactive form high overvoltage induces the application of potential valuesof peroxidases denoted compound III (oxidation state + 6). at which the interference of other electroactive substances in app real samples is maximized. In the detection potential rangeThe apparent Michaelis–Menten constant (Km ) of HRP atPC/Au/MPE/GA/HRP was calculated to be 7.6 mM accord- of −0.1 to −0.5 V, the highest sensitivities are obtained withing to the Lineweaver–Burk equation. This value is slightly the bare PC/Au system, independently on the presence or ab-higher than 3.69 mM reported for the nano-Au particle/m- sence of the H2 Q mediator in the solution. The high surfacephenylenediamine polymer film system [38] and 2.3 mM area of gold nanotubes compared to the macroscopic goldfor the HRP/Au colloid self-assembled monolayer electrode foil, conjugated to the high roughness of the gold electroless app surface lead to an obvious increase of the efficient area of the[28]. The higher Km value of HRP at our nanotubes-basedsystem could reflect diffusional limitations of the substrate electrode surface. Bare PC/Au nanoelectrode can thus be use-within the nanotubes. ful as a probe for a direct electrochemical determination of The other type of enzyme-modified nanoelectrodes H2 O2 . Nevertheless, it is important to point out that the best(PC/Au/MPA/EDC,NHS/HRP) showed similar results with limits of detection were achieved with the enzyme-modifieda sensitivity of 11.3 ␮A mM−1 at −0.1 V in H2 Q solution. nanoelectrodes, because of higher faradic-to-capacitive cur-As stated previously, the need for a mediator to enhance the rent ratios (Fig. 4). Indeed, the best limits of detection are 4 ×sensor sensitivity is no longer required when using the un- 10−6 and 8 × 10−5 M, based on signal-to-noise of three, formodified PC/Au electrode. the PC/Au/MPE/GA/HRP and PC/Au systems, respectively, The sensitivity values, calculated by the slope of each while only 10−3 M was reached with the Au macroelectrodecalibration curve in the linear range, of the different sen- device.sors at several applied potentials and for different solutioncompositions (PB or PB + H2 Q) are shown in Fig. 6. Bare 3.3.2. Mechanism of the electron transfer on HRPAu macroelectrode presents the poorest response to H2 O2 . modified electrodesThe response of such probe is at least five times lower than As already mentioned, the determination of H2 O2 wasthat of the H2 O2 sensor based on bare PC/Au throughout performed either in the presence of a charge transfer mediator,the investigated potential range. The limit of detection for hydroquinone, or in its absence. For bare PC/Au electrode andthis system is only 8 × 10−4 M at an applied potential of bare Au macroelectrode, the presence of the mediator has a−0.2 V in hydroquinone solution. This poor response on the rather weak effect on the detection of H2 O2 . On the othergold macroelectrode is not surprising, because of the large hand, the enzyme-modified nanoelectrodes show a largelyoverpotentials associated to both oxidation and reduction of enhanced sensitivity when adding the hydroquinone mediatorthis analyte on Au surfaces. The electrochemical detection in the medium. The catalytic process of HRP immobilizedof hydrogen peroxide on gold has often been neglected in onto gold surfaces can be expressed as follow [51]:the literature because of lack of proper surface control andmechanistic understanding. Only Kauffmann and coworkers HRP(Fe3+ ) + H2 O2 → compound I + H2 O (1)
  7. 7. M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230 227compound I + H2 Q → compound II + BQ (2) tween the active center of HRP and the electrode and/or from the direct reduction of H2 O2 at the remaining gold surface.compound II + H2 Q → HRP(Fe 3+ ) + BQ + H2 O (3) According to the high faradic-to-capacitive current ratio obtained for the PC/Au/MPE/GA/HRP sensor in phosphatenet reaction : BQ + 2e− + 2H+ → H2 Q buffer (Fig. 4a), it is possible that a certain amount of HRPwhere compound I (oxidation state + 5) and II (oxidation participates in direct electron transfer with the electrolessstate + 4) represent the enzyme intermediates in the reaction gold surface. In this case, the enzyme immobilized on theand H2 Q and BQ represent hydroquinone and benzoquinone, electrode is oxidized by hydrogen peroxide according to reac-respectively. In the first two electrons transfer step, H2 O2 is tion (1) and then subsequently reduced by electrons providedreduced to water and the HRP is oxidized to compound I. by an electrode as described in reaction (4):Compound I is then reduced in a one electron step to form compound I + 2e− + 2H+ → HRP(Fe3+ ) + H2 O (4)compound II, and then compound II is reduced to the orig-inal form of HRP by the redox mediator (H2 Q). The BQ is This direct electron transfer, which is usually less efficientsubsequently reduced to H2 Q by a rapid reaction involving than mediated electron transfer can also be present in thethe consumption of two electrons from the electrode. The enzyme electrode used in hydroquinone solution. Indeed,resulting cathodic currents are therefore correlated with the Lindgren et al. [52] have demonstrated that both direct andconcentration of both hydrogen peroxide and mediator in the mediated electron transfers can simultaneously occur in ansolution. The dependence of the amperometric determination enzyme-modified electrode. Not all the HRP molecules wereof H2 O2 on the concentration of the mediator was investi- equally involved in these two processes. In their work, thegated. Fig. 7 shows that the response of the enzyme elec- high percentage (40–50%) of the HRP able to participatetrode to 5 × 10−4 M H2 O2 at an applied potential of −0.1 V in direct electron transfer has been ascribed to phenolic andincreases sharply as the concentration of hydroquinone in- quinoidal groups present in carbon-based electrodes, whichcreases and then leveled off at 1 × 10−4 M H2 Q. At low me- mimicked the structure of the electron donor substrates of per-diator concentration, the current response is limited by the oxidases. In our system, the use of SAM allowing the immobi-enzyme-mediator kinetic. When the mediator concentration lization of enzymes in close contact with the active surface ofis high, the current response becomes limited by the enzyme- the electrode, as well as the use of gold nanotubes that createsubstrate kinetics. a confined environment surrounding the enzyme molecules, In our enzyme-modified nanoelectrodes, it is difficult could facilitate the direct electron transfer between the activeto distinguish between the electrocatalytic action of gold center of the biomolecule and the gold surface.nanoparticles and a direct electron transfer between the hemegroup of HRP and the gold nanoparticles on the reduction 3.3.3. Repeatability and reproducibility of the HRPof H2 O2 . Indeed, from previous results [47], we know that enzyme electrodethe use of short alkyl chain thiols on gold electroless sur- The repeatability of the PC/Au/MPE/GA/HRP system wasface does not lead to a complete coverage of the surface. A tested both in H2 Q (0.1 mM) and in PB solution at −0.1 V.part of the underlying electrode, which was estimated at 24% The relative standard deviations determined for 10 successivefrom cyclic voltammetry measurements, is still available af- injections of a 2.5 × 10−4 M H2 O2 sample was 8 and 7% inter functionalization for the direct electrochemical reduction H2 Q and PB, respectively. At the same applied potential, theof H2 O2 . The signal-response for the enzyme electrode in PB calculated RSD for the PC/Au system was slightly higher, butsolution can thus come from the direct electron transfer be- always below 15%. The electrode-to-electrode reproducibil- ity was estimated from the response to 2.5 × 10−4 M H2 O2 at nine different biosensors in PB and PB + H2 Q solutions and at several fixed potentials (0, −0.2, and −0.5 V). The relative standard deviations are: 14, 9 and 11% at a detection potential of 0, −0.2 and −0.5 V in PB + 0.1 mM H2 Q and 15 and 10% at a potential of −0.2 and −0.5 V in PB. These results show that good reproducibility and repeatability are reached with the enzyme-modified nanoelectrodes (PC/Au/MPE/GA/HRP system). 3.3.4. Storage stability of the HRP enzyme electrode The storage stability was investigated by measuring every week over a 5 months period, the response to 2.5 × 10−4 MFig. 7. Variation of the amperometric response of PC/Au/MPE/GA/HRP H2 O2 of a PC/Au/MPE/GA/HRP biosensor at −0.1 V. HRPelectrode for the analysis of 5.0 × 10−4 M hydrogen peroxide as a functionof the hydroquinone concentration in phosphate buffer. Applied potential: has been found to be very stable in solution [10] so the HRP−0.1 V. biosensor was stored in PB at 4 ◦ C between each measure-
  8. 8. 228 M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230 1.0 × 10−3 /2.0 × 10−4 1.2 × 10−3 PB + H2 Q 0.4 2.3 × 10−3 /2.0 × 10−4 at leastFig. 8. Selectivity of the PC/Au/MPE/GA/HRP sensor as a function of the 2.3 × 10−3applied potential; comparison of the amperometric current obtained for (a)5.0 × 10−4 M ascorbic acid, (b) 5.0 × 10−4 M H2 O2 and (c) a + b + 5.0× 10−4 M uric acid + 5.0 × 10−4 M acetaminophen (blend). Electrolyte PB Aumedium: 1.0 × 10−1 M phosphate buffer with addition of 1.0 × 10−4 M 1hydroquinone. 1.0 × 10−4 /5.0 × 10−3 at least Analytical characteristics for the PC/Au/MPE/GA/HRP, the PC/Au and Au sensors at −0.1 V vs. Ag/AgCl in PB and in PB + 1.0 × 10−4 M H2 Qment. After five measurements, the electrode response wasdecreased by 18% due to the desorption of enzyme moleculesthat were only physisorbed on the surface. After 5 months ofstorage, the biosensor retained about 70% of its original re-sponse. The PC/Au/MPE/GA/HRP biosensor is thus quite 1.3 × 10−4 PB + H2 Qefficient for retaining the activity of HRP. This could be dueto the strong interaction between the enzyme and the gold 14nanoparticles within the nanotubes. 3.0 × 10−4 /5.0 × 10−3 at least3.3.5. Interference study Despite the low applied potential, many compounds mayinterfere at the electrode surface, because HRP has a broadsubstrate activity. As one of our final goal is to fabricate abi-enzymatic nanotubes-based biosensors including oxidases 3.0 × 10−4that produce H2 O2 and the HRP to measure for instance, glu- PC/Aucose in different types of samples, we have investigated, in the 10.5 PBpotential range +0.4 to −0.8 V the interference of uric acid(UA), ascorbic acid (AA) and acetaminophen (AC), which are 1.0 × 10−5 /6.0 × 10−3common metabolites in blood samples. The interference wasevaluated for the three systems: PC/Au/MPE/GA/HRP, barePC/Au and bare Au macroelectrode sensors by measuring the 9.2 × 10−6 PB + H2 Qcurrent response obtained for each interfering substances inPB in the presence or not of H2 Q. Fig. 8 shows the current 9.5response recorded at the PC/Au/MPE/GA/HRP sensor PB +H2 Q solution to the injection of 5.0 × 10−4 M AA (a), 5.0 PC/Au/MPE/GA/HRP 4 × 10−5 /1.0 × 10−4× 10−4 M H2 O2 (b) and a blend of 5.0 × 10−4 M AA, 5.0× 10−4 M H2 O2 , 5.0 × 10−4 M UA and 5.0 × 10−4 M AC(c). It clearly appears that, in the potential range from 0 to 2.0 × 10−5−0.8 V, these substances do not significantly interfere withthe electrode response to H2 O2 . Only ascorbic acid, which 1.5 PBhas a low oxidation potential, causes the electrode to de-viate by more than 74% of its original value in the anodic (␮A mM−1 )branch (at potential > +0.1 V). The bare PC/Au electrode Detection limit (M) Linear range (M)shows the same behavior than PC/Au/MPE/GA/HRP systemthroughout the whole investigated potential range, except that Electrolyte Sensitivityuric acid produces an anodic signal at 0 and −0.1 V in both Table 1electrolyte solutions. This results in a low negative interfer-ence, less than 18% (decrease in the cathodic response) in
  9. 9. M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230 229the cathodic mode of the sensor operation. On the bare Au Acknowledgementsmacroelectrode, the effect of interfering compounds is morepronounced. Ascorbic acid is oxidizable on the electrode SD-C thanks the Belgian National Fund for Scientific Re-over a larger potential range (from +0.4 to −0.1 V) while search (FNRS) for her research associate position. MD isUA and AC give anodic and cathodic currents, respectively, ` a fellow of “Fonds pour la formation a la recherche dansfrom −0.1 to −0.6 V. The presence of these compounds in l’industrie et dans l’agriculture” (FRIA, Belgium). The “Ser-the sample can produce a large deviation in the current re- vices F´ d´ raux des Affaires Scientifiques, Techniques et Cul- e esponse (e.g. 78% decrease signal at −0.3 V in phosphate turelles” are thanked for their financial support in the framebuffer). of the “Pole d’Attraction Interuniversitaire” (IAP network P5/03).4. Conclusions References Arrays of gold nanotubes were prepared through the elec-troless deposition of gold within the nanopores of polycar- [1] C. Matsubara, N. Kawamoto, K. Takamura, Analyst (1992) 117.bonate track-etched membranes. The versatility of the pro- [2] M. Shiga, M. Saito, K. Kina, Anal. Chim. Acta 153 (1983) 191.cess, the possibility to bend the nanotubes and to use them [3] P.A. Clapp, D.F. Evans, T.S.S. Sheriff, Anal. Chim. Acta 218 (1989)in various configurations, as well as the high surface area of 331. [4] K. Nakashima, K. Maki, S. Kawaguchi, S. Akiyma, Y. Tsukamoto,these new materials make them very attractive for the fabri- I. Kazuhiro, Anal. Sci. 7 (1991) 709.cation of biosensors. [5] B. Olsson, Anal. Chim. Acta 136 (1983) 113. Enzyme-modified nanoelectrodes arrays were constructed [6] M. Aizawa, Y. Ikariyama, H. Kuno, Anal. Lett. 17 (1984) 555.by the covalent immobilization of HRP on pre-formed self- [7] E.C. Hurdis, H. Romeyn, Anal. Chem. 26 (1954) 320.assembled monolayers onto the gold surface. Ensembles of [8] A.I. Vogel, Textbook of Quantitative Inorganic Analysis, Longman, New York, 1978.bare gold nanotubes as well as ensembles of HRP modified [9] M. Vreeke, R. Maidan, A. Heller, Anal. Chem. 64 (1992) 3084.nanotubes were used as working electrodes for the direct elec- [10] T. Ruzgas, E. Cs¨ regi, J. Emneus, L. Gorton, G. Marko-Varga, Anal. otrochemical detection of hydrogen peroxide. The analytical Chim. Acta 330 (1996) 123.performances obtained in PB solutions (with and without the [11] M.G. Garguilo, N. Huynh, A. Proctor, A.C. Michael, Anal. Chem.H2 Q mediator), for the PC/Au, the PC/Au/MPE/GA/HRP 65 (1993) 523. [12] J. Li, S.N. Tan, H.L. Ge, Anal. Chim. Acta 335 (1996) 137.and a commercial gold foil (Au) sensors under the same ex- [13] M. Gerlache, Z. Senturk, G. Quarin, J.-M. Kauffmann, Electroanal-perimental conditions are summarized in Table 1. The bare ysis 9 (14) (1997) 1088.PC/Au sensor displays the best sensitivity to H2 O2 . Com- [14] J. Wang, N. Naser, L. Angnes, H. Wu, L. Chen, Anal. Chem. 64pared to a commercial gold foil (macroelectrode) of the same (1992) 1285. [15] J. Wang, J. Liu, L. Chen, F. Lu, Anal. Chem. 66 (1994) 3600.geometrical area, the signal is enhanced by a factor of 10. [16] J. Wang, F. Lu, L. Angnes, J. Liu, H. Sakslund, Q. Chen, M. Pedrero,This improvement is attributed to the exceptional catalytic L. Chen, O. Hammerich, Anal. Chim. Acta 305 (1995) 3.activity of the gold nanoparticles. This is in complete agree- [17] J. Wang, G. Rivas, M. Chicharro, Electroanalysis 8 (1996) 434.ment with the development of metallized carbon transduc- [18] G. Rivas, M. Rodriguez, Electroanalysis 13 (2001) 1179.ers by Wang et al. [14–16] where the remarkable selectiv- [19] S.A. Miscoria, G.D. Barrera, G.A. Rivas, Electroanalysis 14 (2002) 981.ity of metal-dispersed carbon transducers allows tuning of [20] J. Li, L.-T. Xiao, X.-M. Liu, G.-M. Zeng, G.-H. Huang, G.-L. Shen,the operating potential to the region (+0.1 to −0.2 V) where R.-Q. Yu, Anal. Bioanal. Chem. 376 (2003) 902.unwanted reactions do not occur. This high selectivity is at- [21] R. Parsons, T. VanderNoot, J. Electroanal. Chem. 257 (1988) 9.tributed to their strong, preferential, electrocatalytic action [22] D.F. Koch, D.A. Rand, R. Woods, J. Electroanal. Chem. 70 (1976)of the metallic particles towards the detection of enzymat- 73. [23] J. Wang, P. Pamidi, C. Cepria, Anal. Chim. Acta 330 (1996) 151.ically liberated hydrogen peroxide. Such transducer elim- [24] J. Liu, F. Lu, J. Wang, Electrochem. Comm. 1 (1999) 341.inates major electroactive interferences in the first place, [25] F. Xu, L. Wang, M. Gao, L. Jin, J. Jin, Talanta 57 (2002) 365.and hence circumvents the need for anti-interference lay- [26] P.D. Sanchez, P.T. Blanco, J.M.F. Alvarez, M.R. Smyth, R.ers. O’Kennedy, Electroanalysis 2 (1990) 303. The signal-response is slightly lower in the case of the [27] J.Z. Zhang, B. Li, Z.X. Wang, G.J. Cheng, S.J. Dong, Anal. Chim. Acta 388 (1999) 71.PC/Au/MPE/GA/HRP bioelectrode, due to a decrease of the [28] Y. Xiao, H.-X. Ju, H.-Y. Chen, Anal. Biochem. 278 (2000) 22.active surface area. However this latter biosensor exhibits a [29] C. Lei, Z. Zhang, H. Liu, J. Kong, J. Deng, Anal. Chim. Acta 332better limit of detection and a better selectivity, which makes (1996) 73.it promising material for the construction of a H2 O2 biosen- [30] Y. Miao, S.N. Tan, Anal. Chim. Acta 437 (2001) 87.sor. Its low cost, ease of fabrication, fast response time, as well [31] B. Liu, Y. Cao, D. Chen, J. Kong, J. Deng, Anal. Chim. Acta 478 (2003) 59.as good reproducibility and repeatability, offer additional ad- [32] I. Willner, E. Katz, A. Riklin, R. Kasher, J. Am. Chem. Soc. 114vantages. Furthermore, in the absence of mediator, the direct (1992) 10965.electrochemistry of HRP offers an opportunity to build up a [33] I. Willner, E. Katz, B. Willner, Sens. Update 4 (1999) 45.reagentless biosensor. [34] S. Bharathi, Anal. Commun. 35 (1998) 29.
  10. 10. 230 M. Delvaux et al. / Analytica Chimica Acta 525 (2004) 221–230[35] S. Bharathi, M. Nogami, O. Lev, Langmuir 17 (2001) 2602. [45] S. Demoustier-Champagne, M. Delvaux, Mater. Sci. Eng. C 15[36] J. Jia, B. Wang, A. Wu, G. Cheng, Z. Li, S. Dong, Anal. Chem. 74 (2001) 269. (2002) 2217. [46] H. Hanot, E. Ferain, R. Legras, Patent WO0149403 (2001).[37] J. Li, L.T. Xiao, X.M. Liu, G.M. Zeng, G.H. Huang, G.L. Shen, [47] M. Delvaux, S. Demoustier-Champagne, Biosens. Bioelectron. 18 R.Q. Yu, Anal. Bioanal. Chem. 376 (2003) 902. (2003) 943.[38] S.Q. Liu, H.X. Ju, Anal. Biochem. 307 (2002) 110. [48] M. Delvaux, S. Demoustier-Champagne, A. Walcarius, Electroanal-[39] S. Seradilla Razola, B. Lopez Ruiz, N. Mora Diez, H.B. Mark Jr., ysis 16 (2004) 190. J.-M. Kauffmann, Biosens. Bioelectron. 17 (2002) 921. [49] Z. Hou, N.L. Abbott, P. Stroeve, Langmuir 14 (1998) 3287.[40] Y. Xiao, H.-X. Ju, H.-Y. Chen, Anal. Chim. Acta 391 (1999) 73. [50] M. Gerlache, S. Girousi, G. Quarin, J.-M. Kauffmann, Electrochim.[41] M.W. Ducey, M.E. Meyerhoff, Electroanalysis 10 (1998) 157. Acta 43 (1998) 3467.[42] C. Padeste, S. Kossek, H.W. Lehmann, C.R. Musil, J. Gobrecht, L. [51] J. Everse, K.E. Everse, M.B. Grisham, Peroxidases in Chemistry and Tiefenauer, J. Electrochem. Soc. 143 (1996) 3890. Biology, CRC Press, Boca Raton, 1991.[43] B. Brunetti, P. Ugo, L.M. Moretto, C.R. Martin, J. Electroanal. [52] A. Lindgren, M. Tanaka, T. Ruzgas, L. Gorton, I. Gazaryan, Chem. 491 (2000) 166. K. Ishimori, I. Morishima, Electrochem. Comm. 1 (1999)[44] V.P. Menon, C.R. Martin, Anal. Chem. 67 (1995) 1920. 171.