Abstract
We present a new biosensor for hydrogen peroxide (H2O2) detection. The biosensor was based on the immobilization of horseradish peroxidase (HRP) enzyme on layered double hydroxides- (LDH-) modified gold surface. The hydrotalcite LDH (Mg2Al) was prepared by coprecipitation in constant pH and in ambient temperature. The immobilization of the peroxidase on layered hybrid materials was realized via electrostatic adsorption autoassembly process. The detection of hydrogen peroxide was successfully observed in PBS buffer with cyclic voltammetry and the chronoamperometry techniques. A limit detection of 9 μM of H2O2 was obtained with a good reproducibility. We investigate the sensitivity of our developed biosensor for H2O2 detection in raw milk.
1. Introduction
Horseradish peroxidase (HRP) is a glycoprotein with four lysine residues for conjugation to a labeled molecule. It produces a colored, fluorimetric, or luminescent derivative of the labeled molecule when incubated with a proper substrate, allowing it to be detected and quantified. Horseradish peroxidase was often used in conjugates to determine the presence of a molecular target and was also commonly used in techniques such as ELISA and Immunohistochemistry. Horseradish peroxidase is ideal in many respects for these applications because it is smaller, more stable, and less expensive than other popular alternatives such as alkaline phosphatase. Conductor’s polymers and magnetic nanoparticles were used in the fabrication of various types of HRP-based biosensors [1, 2]. To stabilize the immobilized enzyme in the matrix of film, glutaraldehyde (GA) is usually employed as a bifunctional agent to cross-link enzyme molecules [3–6], but the cross-linking efficiency under standard conditions is not always satisfactory [6, 7], which results in the lower sensitivity and poor stability of the resulting biosensor. It was established that cationic clays and especially anionic ones or layered double hydroxides were considered as a new class of materials with a high trapping potential of molecules of different sizes and that they form hybrid materials. Indeed, these materials present very attractive advantages such as a low cost of purification or synthesis and their biocompatibility. Furthermore, the bi-dimensional structure of LDHs with the general formula: [8, 9] present additional advantages relatively to cationic clays. LDHs can be synthesized using the same protocol, and the obtained materials have a large range of physicochemical properties. A wide varieties of LDHs can be achieved by changing the anionic ion A (CO3 2−, SO4 2−, HPO4 2−, NO3 −, F−, Cl−, Br−, and I−) or the metallic divalent (M2+ : Mg, Zn, Ni, Co, Pd, etc.) or trivalent ions (M3+ : Al, Cr, Fe, V, etc.). This type of material presents high anionic-exchanging capacities by changing the divalent and trivalent ion ratio () and adjusting the interlayer anions to intercalate different molecules [3–10]. Therefore, this kind of materials can be considered very attractive for new hybrid biomaterials development and for functionalized surfaces for ionic and biologic detection [10–12]. It has been previously shown that immobilization of urease in LDH is of high interest for the fabrication of biosensors [12]. The panel of applications of these materials is very large; they can be used for monitoring food process, diagnosis and medical monitoring, or for therapeutic and pharmaceutical applications such as the encapsulation of active molecules for drugs [13–15] or radioactive substances.
In this work, we present a new biosensor for hydrogen peroxide (H2O2) detection based on layered double hydroxides (LDH) layer. The biosensor was based on the immobilization of horseradish peroxidase (HRP) enzyme on LDH-modified gold surface. The hydrotalcite LDH (Mg2Al) was prepared by coprecipitation in constant pH and in ambient temperature. The immobilization of the peroxidase in layered hybrid materials was realized via electrostatic adsorption autoassembly process. The detection of hydrogen peroxide was successfully observed in PBS buffer with cyclic voltammetry and the chronoamperometry techniques.
2. Experimental Setup
2.1. Reagents and Apparatus
The hybrid biomembranes Enzyme/LDH were prepared in two steps: the LDH synthesis, followed by the peroxidase immobilization. We synthesized hydrotalcite LDH by coprecipitation method at constant pH and temperature. The ratio volume of solutions of MgCl3 and AlCl3 0.1 M was fixed at 2 in order to obtain a final LDH of Mg2AlCO3. Mg2AlCO3 LDH was prepared according to the process described by Baccar et al. [16]. We added drop to drop and under vortex agitation the solution of AlCl3 and the MgCl2. The pH reaction of coprecipitation was fixed at pH 8 by adding a basic solution of NaOH (NaOH 2 M + Na2CO3 0.125 M). The final solution obtained was washed with milli-Q water and filtered to eliminate the ions chlorides, then dried at 100°C in dark during 12 hours, and finally crushed.
2.2. Gold Cleaning and Functionalization
The gold electrodes (1 cm × 1 cm) were fabricated at the National Center of Microelectronics of Barcelona (Spain). Evaporated gold (~300 nm thickness) was deposited on silicon, using a titanium under layer (~30 nm thickness) as substrate. Before modification, the gold electrodes were cleaned in acetone solution for 20 min with ultrasonic bath. After that, they were dried under a nitrogen flow and then dipped for 10 min into “piranha solution” 7 : 3 (v/v) 96%H2SO4/30%H2O2. Finally, the gold substrates were rinsed 2 to 3 times with ultrapure water and immediately immersed in an ethanol solution. After cleaning, the gold electrodes were immediately placed on an electrochemical cell. For DHL deposition on gold electrodes, a drop (approximately 10 μL by cm2) of dispersed LDH (Mg2Al 2.5 mg/mL) in deionised water (milli-Q) was deposited and coated by spin coating at less than 1000 rms/min during 10 s and about 4000 rms/min during 30 s. After that, a drop (approximately 10 μL by 1 cm2) of HRP (equal to 0.250–0.330 Units) dispersed in milli-Q water was deposited in surface and dried at 4°C overnight. Finally, the nonbounded enzymes were eliminated by washing samples with a solution of 20 mM PBS. After testing, the samples were stored in a solution of 20 mM PBS, pH 7.4 at 4°C.
2.3. Cyclic Voltammetry and Chronoamperometry
Cyclic voltammetry and chronoamperometry measurement were performed at room temperature in a conventional voltammetric cell with a three-electrode configuration using Autolab impedance analyzer (Eco Chemie, The Netherland). The gold electrode (0.16 cm2) was used as working electrode and platinum (1 cm2) and Ag/AgCl electrodes were used as counter and reference electrodes, respectively. All cyclic voltammetry measurements were carried out with scan rate of 75 mV/s in PBS at pH 7 and in Faraday cage. More details can be found in [17].
2.4. Atomic Force Microscopy and Impedance Spectroscopy
Atomic Force microscopy was performed using a Dimension 3100 (Veeco) Atomic Force Microscope operating in tapping mode. The impedance analysis was performed with the Autolab 302 N impedance analyzer (Eco Chemie, The Netherland) in the frequency range 0.05 Hz–100 kHz, using a modulation voltage of 10 mV. More details on electrochemical impedance spectroscopy can be found in [18–20].
3. Results and Discussions
3.1. Gold Electrode Functionalization
Cyclic voltammetry is an electrochemical technique which can be used to study the kinetic of redox reactions of materials, their insulating and conducting properties. Cyclic voltammograms of the gold electrode (Figure 1(a)) show a reversible wave which is the typical behavior of gold surface in PBS buffer. After modification of the gold surface with the LDH membrane, the current increases due to the high conductivity properties of the LDH layer and anion exchange (Figure 1(a)). Typical Nyquist plots for gold electrode and gold electrode with LDH layer from 50 mHz to 100 KHz at 0.2 V potential (versus Calomel electrode) in PBS were shown in Figure 1(b). Impedance spectra were interpreted through equivalent circuits representing the different processes involved in the description of the system with discrete electric elements [20, 21]. The semicircle diameter of impedance spectra represents the charge transfer resistance, . This resistance controls the electron transfer kinetics of the ions at the electrode interface. Figure 1(c) shows the atomic force microscopy image of gold surface treated with LDH in tapping mode. It shows a homogenous surface with roughness less than 1 nm. The same observation was observed with scanning electron microscopy (SEM) in [22].
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3.2. HRP Immobilization
Figure 2(a) shows the cyclic voltammogram of gold electrode functionalized with LDH layer before and after HRP immobilization. We observe a decrease of the current for positive potential after HRP immobilization. The peak at 350 mV corresponds to the oxidation potential of HRP. Figure 2(b) shows the Nyquist diagram of impedance measurement at fixed potential (0.2 V) for gold electrode with LDH and with HRP enzyme. The increase of the charge transfer resistance is due to the success immobilization of the HRP enzyme. This result confirms the result obtained with cyclic voltammetry.
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3.3. Biosensors Applications
Figure 3(a) shows the cyclic voltammogram of the gold electrode functionalized with HRP enzyme before and after injection of H2O2. Upon the addition of the hydrogen peroxide to the electrochemical cell, the oxidation peak (at 350 mV) appears, showing a typical electron transfer between the H2O2 and the HRP molecule: The chronoamperometry can be used to explore the current response of the biosensor in presence of the hydrogen peroxide. Figure 3(b) shows the chronoamperometry curve of functionalized electrode with HRP at a fixed potential of 350 mV after H2O2 injections. The current increases with increasing H2O2 concentration which agrees with result shown in Figure 3(a). The addition of the hydrogen peroxide to the buffer solution increases the steady state current. Figure 3(c) shows the calibration curves of the biosensor exposed to different concentration of hydrogen peroxide obtained from Figure 3(a) (at a potential of 350 mV). The curves were represented by a linear regression (between 0 to 200 μM), and a best sensitivity was obtained. A limit detection of 9 μM of H2O2 was obtained with a good reproducibility for the developed biosensor. Moreover, we investigate the sensitivity of our developed biosensor for H2O2 detection in raw milk. Figure 3(c) shows the calibration curve obtained in raw milk after H2O2 injection. It shows a lower sensitivity due to coexisting electroactive species such as casein (and other proteins) in raw milk.
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4. Conclusion
In this work, we present new biosensors for the detection of hydrogen peroxide (H2O2) with LDH functionalized layer. The biosensor was developed by the immobilization of horseradish peroxidase (HRP) enzyme on LDH-modified gold electrode. The deposition of LDH layer and HRP enzyme was verified with cyclic voltammetry and impedance spectroscopy. The detection of hydrogen peroxide was successfully observed in PBS using the cyclic voltammetry and the chronoamperometry techniques. A limit detection of 9 μM of H2O2 was obtained with a good reproducibility. We investigate the sensitivity of our developed biosensor for H2O2 detection in raw milk.