Direct Electrochemistry of Catalase Immobilized at Polymerized-SnO₂ Multiporous Modified Electrode for an Amperometric H₂O₂ Biosensor Volume 3 - Issue 4

Samiul Alim, Jaya Vejayan and AKM Kafi*

• Faculty of Industrial Sciences & Technology, University Malaysia Pahang, Malaysia

Received: March 16, 2018;   Published: April 10, 2018

Corresponding author: AKM Kafi, Faculty of Industrial Sciences & Technology, University Malaysia Pahang, Kuantan 26300, Malaysia

DOI: 10.26717/BJSTR.2018.03.000942

Abstract PDF

A novel amperometric H₂O₂ biosensor based on immobilization of catalase with polymerized MPNFs of SnO₂ onto glassy carbon electrode with chitosan have been proposed in this work. Multiporous nanofibers of SnO₂ were synthesized by electrospinning method from the tin precursor by controlling the concentration followed by polymerized with aniline. Catalase was then co-immobilized with the polymerized nanofibers on the surface of glassy carbon electrode by using chitosan. The polymerized MPNFs of SnO₂ play a significant role in facilitating the electron exchange between the electroactive center of catalase and the electrode surface. Cyclic Voltammetry and amperometry were used to study and optimize the performance of the fabricated H₂O₂ biosensor. The PANI/SnO₂-NFs/Catalase/Ch/GCE biosensor displayed a linear amperometric response towards the H₂O₂ concentration range from 10 to 120 μM with a detection limit of 0.6 μ M (based on S/N=3). Furthermore, the biosensor reported in this work exhibited acceptable stability, reproducibility, and repeatability.

Keywords: Catalase; SnO₂; Polyaniline; H₂O₂ Sensing

Abbreviations: CV: Cyclic Voltammetric; PVP: Polyvinylpyrrolidone; DMF: Dimethylformamide; HCl: Hydrochloric Acid; NaOH: Sodium Hydroxide

H₂O₂ is engendered by normal cellular metabolism as a signaling molecule for signal transduction, second messengers and growth factors [1,2]. Moreover, H₂O₂ can pierce freely into almost any cellular compartments through membranes, and it can induce oxidative stress causing the deterioration of lipids, proteins, and DNA, as well as some diseases ranging from cancer to neurodegenerative disorder like Parkinson's or Alzheimer disease [3-5]. H₂O₂ also has application in various fields like pharmaceutical, food and environmental analysis [6-8]. Therefore, the selective detection of H₂O₂ is essential and numerous methods have been proposed for the last decades to ensure the reliable and fast detection of H₂O₂ such as colorimetry [9], fluorescence [10], chemiluminescence [11], electron spin resonance [12], electrochemical biosensing [13], etc., whereas, electrochemical biosensing is the most attractive choice [14].

In the promptly progressing area of biosensors, clamping bio molecules with complex molecular structure with transducer devices is the most crucial issue to resolve for researchers [15,16]. The passage of electrons is the major drawback in direct electron transfer between these unconventional partners, whereas, effective electrical contact between the active site of an enzyme/protein and the electrode surface is the cornerstone of any amperometric biosensor [17]. The active redox sites of enzymes/proteins are buried deeply within the insulated shell of the immobilized protein and thus in the far distance from the surface of electrode [18,19]. Numerous studies have been conducted till now to accelerate the direct electron transfer. Immobilization of the enzymes on different substrates like nonmaterial is one of the most effective ways [20]. Being inspired by the distinctive features of nanostructured materials like regular structure, excellent chemical and thermal stability, different types of nonmaterial-based biosensors have secured much attention for their uses in the health and environment.

One of the most striking nanostructured materials is tin oxide (SnO₂) which has been used as nanotubes, nanoparticles, nanowires, and nanorods [21,22]. Nanostructured SnO₂ possesses high surface area, nontoxicity, excellent biocompatibility, catalytic activity and chemical stability [23] which makes it suitable for various applications such as solar cells, electrochemistry, and biosensor [24-26]. We have fabricated a new one-dimensional nano-morphology of SnO₂ recently with the higher surface area and enhanced electron mobility characteristics, named as multiporous nanofibers (MPNFs). It was synthesized through electrospinning method by controlling the tin precursor concentration [27]. This potential nanofiber can be transcended in contrast with other conventional nanofibers and nanowires if used in biosensing. Moreover, incorporation of a polymer such as polyaniline (PANI) with this nanofiber can intensify its electrical conductivity along with some other characteristics like mechanical flexibility, thermal and chemical stability [28,29] which can be an incentive for the advancement of the biosensor.

Catalase is a heme-containing homotetrameric enzyme can resist the accumulation of H₂O₂ and fortifies cellular organelles and tissues from the damage caused by peroxide. This enzyme has been extensively used in biosensor and selective determination of H₂O₂ [30,31]. In this work, we have developed a new electrode modified with the organization of Polyaniline-SnO₂ NF-catalase enzyme on glassy carbon electrode by using chitosan. Followed by the synthesis of SnO₂ NF, polyaniline (PANI) has been polymerized on SnO₂ to develop SnO₂-PANI composite. The proposed modified electrode was then applied for H₂O₂ biosensing. To the best of our knowledge for the first time, polymerized multiporous nanofibers of SnO₂ and chitosan composite has been used to study direct electrochemistry of catalase enzyme and used in selective and reliable detection of ^H2°2.

Reagents and Materials

Tin chloride pentahydrate (SnCl₄.5H₂O), polyvinylpyrrolidone (PVP) and dimethylformamide (DMF) were bought from Sigma. Catalase, chitosan and a stock solution of H₂O₂ (30 wt %) were also purchased from Sigma and used as received and preserved at 4oC. Aniline monomer (99.5%) and ammonium persulfate (APS, 98%) were obtained from E. Merck (Germany). The pure water (18 MΩ. cm) used to prepare all solutions in this work was purified with the Nanopure ® water system. All other reagents were of analytical grade, and 0.01 M Phosphate buffer of pH 7.0 was freshly prepared every time before use. 1.0 M hydrochloric acid (HCl) or I. 0 M sodium hydroxide (NaOH) was used in order to procure the desired pH of phosphate buffer.

Fabrication of the SnO₂ Nanofiber

Multiporous SnO₂ nanofiber was fabricated according to the procedure described in our previous work [26]. To sum up, the starting reagents were tin chloride pentahydrate (SnCl₄.5H₂O), polyvinylpyrrolidone (PVP), dimethylformamide (DMF) and ethanol, whereas, 3 g of PVP was dissolved in an equal volume ratio (1:1) of ethanol and DMF and different concentrations of the tin precursor were dissolved to this solution at room temperature until the solution become transparent. The concentrations of tin precursor used in fabrication were 5.5mM, 7mM, 8.5mM, 10mM,II. 5mM and were labeled as C0, C1, C2, C3 and C4, respectively. For electrospinning, the viscosity of the solution was measured with a rheometer (LVDV III Ultra, Brook eld Co., USA) and the solutions were then transferred to a plastic syringe with steel needles and the procedure was operated by the following parameters:

a. applied voltage, 25 kV,

b. The injection rate, 0.6 mL h^-1,

c. The distance between the collector and the tip of the needle, 20cm

d. Humidity, 40-45%, and

e. 1200 rpm speed of the rotating collector. Solid nanofibers were then collected from the collector and annealed at 600 °C temperature for 3 hour at heating rate 0.5 °C per minute.

Synthesis of Polyaniline (PANI) and PANI-SnO₂-NFs

Followed by the fabrication of SnO₂-NFs, polyaniline (PANI) has been polymerized on SnO₂ using chemical oxidation polymerization method to construct PANI-SnO2-NF composite [32]. For the synthesis of polyaniline, Aniline (0.1M) and ammonium persulphate (0.1M) were dissolved separately in 0.1 M HCl solution and stirred for 1 h. 5mL of HCL (0.1M) and 5 mL of 0.1 M aniline monomer were then mixed in 1:1 ratio. 5% solution of oxidant APS prepared in 0.1 M HCl was added dropwise to the above mixture until well-dispersed solution by keeping the temperature about 0-5 °C under continuous stirring. After 3 h, a reasonable degree of polymerization (a greenish black precipitate) was obtained. The precipitate produced in the reaction was separated by filtration, repeatedly washed with distilled water until the pH reached at 7.0 and dried under vacuum for 24 h.

SnO₂ nanofibers (30mg) were suspended individually in 0.1 M HCl (13 mL) solution and sonicated for 1 h to minimize aggregation of SnO₂ nanofibers. 10 mL aniline (in 0.1 M HCl) solution and 10 mL SnO₂ nanofibers suspension were mixed and further sonicated for 30 min. 10mL APS solution was then slowly added dropwise to well-dispersed suspension mixture with vigorously continuous stirring at 0-5 °C. The mixture colour turns to greenish after adding APS and stirrer is continued to about 5 h. The mixture was then kept overnight to settle the precipitate. A good degree of composite polymerization was perceived after that. The precipitate was washed on the next day with distilled water for several times until pH 7.0, dried in the vacuum oven at 60 °C for 3 h before it was pounded to powder.

Fabrication of Biosensor

A stock solution of 10 mg of PANI/SnO₂ NF was prepared in 100μl phosphate buffer, and the stock solution of 2 mg/ml of catalase was made in phosphate buffer (pH 7.0). A glassy carbon electrode (3 mm of diameter) was polished with alumina powder (0.05μM), rinsed thoroughly with deionized water and acetone subsequently, and then dried at room temperature. Finally, 5μL of PANI/SnO₂ NF the stock solution and 5μL of catalase from the stock solution were co-immobilized onto the glassy carbon electrode together with 2μL of 2mg/ml of chitosan (Ch). The electrodes used for comparison were fabricated in the same way with only SnO₂ NF and only catalase. All the resulting electrodes are denoted as PANI/ SnO₂NF/Catalase/Ch/GC, PANI/SnO₂NF/Ch/GC and Catalase/Ch/ GC respectively. All the electrodes were stored at 4 °C in 0.1 M phosphate buffer at pH 7.0 when not in use.

Morphological and Electrochemical Characterization

Morphological characterization of synthesized nanofiber was evaluated by field emission scanning electron microscopy (JEOL- USA). The electrochemical measurements were carried out by using Potentiostat PARSTAT 2273 on a CHI (630B) workstation. A three- electrode system was employed, whereas, a modified electrode as the working electrode, a platinum wire as a counter electrode and an Ag/AgCl was used as reference electrode. Cyclic voltammetric (CV) measurements were carried out in 0.1 M phosphate buffer by scanning the electrode potential in the range between 0.2 and -0.6V versus Ag/AgCl. Amperometric responses were measured in 0.1 M phosphate buffer stirred by a magnetic stirrer. All electrolytes were deoxygenated before experiments by bubbling ultra-pure nitrogen for 15 min and the relative measurements were carried out at room temperature.

Surface characterization of multiporous SnO₂ Nanofiber

Field emission scanning electron microscopy (FESEM) was employed to study the morphological characteristics of the MPNFs of SnO₂. Figure 1 delineates the morphology of MPNFs of SnO₂. The acquired multiporous SnO₂ nanofiber possessed a fibrous structure according to the FESEM image in all the areas with fiber-fiber interconnections. We have already deliberated about the MPNFs of SnO₂ in our previous work whereas, MPNFs were fabricated with grains size of 5-15 nm and they were smaller than the grain size of the PNFs (15-25 nm) [23].

Figure 1: (a) SEM image of the MPNFs of SnO₂.

Electrochemical Measurement of the Modified Electrodes

Figure 2 elucidates the cyclic voltammograms (CVs) of the

a. bare,

b. PANI/SnO₂-NFs/Ch/GCE;

c. Catalase/Ch/GCE; and

d. PANI/SnO₂-NFs/Catalase/Ch/GCE electrodes recorded in a 0.1M phosphate buffer (pH 7.0) at a scan rate of 50mV/s. As expected, neither oxidation nor reduction peak appears in the CV of the bare electrode and PANI/SnO2-NFs/Ch/GCE electrode showed tiny redox peak. But a moderate reduction peak appears in the CV of the Catalase/Ch/GCE electrode.

Figure 2: Cyclic voltammograms response of
a. Bare GCE electrode;
b. PANI/SnO₂-NFs/Ch/GCE electrode;
c. Catalase/Ch/GCE electrode; and
d. PANI/SnO₂-NFs/Catalase/Ch/GCE electrode in 0.1 M phosphate buffer at pH 7.0 at a scan rate of 50mV/s.

This cathodic peak is attributed to the reduction of HRP at the underlying electrodes. However, a well-defined oxidation and reduction peak appear in the CV of the PANI/SnO₂-NFs/Catalase/ Ch/GCE electrode, whereas, the anodic and cathodic peak potentials are located at -0.1 V and -0.4 V respectively. Both the anodic and cathodic current is higher than both of the PANI/SnO₂-NFs/Ch/ GCE and Catalase/Ch/GCE electrode. The formal potential Ed |Ed = (E_pa + E_pc )/2was calculated to be -0.25 V. The information about electrochemical mechanism can be obtained from the relationship between peak current and scan rate [33]. The effect of the scan rates on the response of PANI/SnO₂-NFs/Catalase/Ch/GCE electrode was evaluated. The linear enhancement of both the oxidation and reduction peak current was observed with the increase of scan rates from 50 to 140 mV/s respectively (data not shown) which suggests that the nature of redox process in the electrode was surface controlled process [33]. The peak-to-peak difference also enhances evenly with the augmentation of scan rates. The results suggest the reduction of all the electroactive redox enzymes at the PANI/SnO₂- NFs/Catalase/Ch/GCE electrode on the forward cathodic scan [34].

Electrochemical response of the PANI/SnO₂-NFs/ Catalase/Ch/GCE Biosensor to H₂O₂

Figure 3 represents the cyclic voltammograms of the PANI/ SnO₂-NFs/Catalase/Ch/GCE electrode recorded in the absence and presence of 10 x 10^-5 M H₂O₂ in 0.1M Phosphate buffer at pH 7.0 at a scan rate of 50mV/s. As shown in the figure, the PANI/ SnO₂-NFs/Catalase/Ch/GCE electrode gives its diffusional redox wave in the absent of H₂O₂ in electrolyte (solid line), whereas, with the introduction of hydrogen peroxide to the solution, a sharp enhancement of cathodic current is appeared (dashed line) with a simultaneous decrease in the corresponding anodic peak. And this change indicates that the enhanced reduction current in the presence of H₂O₂ is due to the presence of heme redox active center of immobilized catalase on the fabricated electrode. The results illustrate that the immobilized catalase possessed excellent electrocatalytic activity towards H₂O₂ reduction.

Figure 3: Cyclic voltammograms response of the PANI/ SnO₂-NFs/Catalase/Ch/GCE electrode in the absence and presence (dashed line) of 2.0 x 10^-5 M H₂O₂ in 0.1M phosphate buffer at pH 7.0 at a scan rate of 50mV/s.

The impact of the applied electrode potential and pH of the phosphate buffer on the amperometric response of the PANI/SnO₂- NFs/Catalase/Ch/GCE electrode was evaluated to the introduction of 1 x 10^-5 M H₂O₂ in 0.1M phosphate buffer at pH 7.0 on the applied potential ranging from 0.3 to -0.6V. The reduction current increased when the applied potential was decreased from 0.3 to -0.4 V. Further reducing the applied potential from -0.4V leads to the declined amperometric response. The best current response was obtained at -0.4V and therefore, the potential -0.4 V was chosen as the working potential for this biosensor. The effect of pH on the amperometric response of the PANI/SnO₂-NFs/Catalase/Ch/ GCE electrode was also investigated in the presence of 1 x 10'⁵ M H₂O₂ in 0.1M Phosphate buffer while the pH was varied from 4.0 to 10.0. The maximum reduction current was achieved at a pH of 7.0. However, a decline of reduction current is obtained when the pH is further increased from 8.0 to 10.0. The current response is very low at the lower pH values (<4.0) of electrolytes which can be caused by the denaturation of bio molecules [35-37]. Therefore, the pH 7.0 was determined as the optimal pH value of electrolyte to obtain highest current response and it corroborates the concept that the pH range of 6.0-7.5 provides the optimum environment for enzymatic electrochemical reactions [35].

Amperometric Response of the Biosensor

The analytical property of PANI/SnO₂-NFs/Catalase/Ch/GCE was further investigated by the amperometric response towards the reduction of H₂O₂. The amperometric response of the PANI/ SnO₂-NFs/Catalase/Ch/GCE electrode has been investigated by successive accretion of H₂O₂ concentration in a stirred cell containing 0.1M phosphate buffer under the optimized pH and potential. Figure 4a shows the typical amperometric response of the PANI/ SnO₂-NFs/Catalase/Ch/GCE electrode for successive inclusion of H₂O₂ and the corresponding calibration plot for the amperometric response is shown in Figure 4b. The response current strikingly increases with the increase of H₂O₂ concentration. The response time for this fabricated electrode was very fast, reaching 95% of its maximum current response in about 5 s. The biosensor shows a linear response ranging from 10 to 120μ M concentrations of H₂O₂ with a correlation coefficient of 0.996 and the detection limit was determined to be 0.6μ M (based on S/N=3).

Figure 4: a. Amperometric response of PANI/SnO₂-NFs/Catalase/Ch/GCE electrode with total addition of 14 x 10-5 M of H₂O₂ in phosphate buffer at pH 7.0 at potential of -0.35 V.
b. Calibration plots for the proposed PANI/SnO₂-NFs/Catalase/Ch/GCE electrode.

Table 1: Suggests that the proposed biosensor offers satisfactory stability and acceptable reproducibility with lower detection limit.

Stability and Repeatability of the Biosensor

Stability and repeatability are among the most remarkable factor about any biosensor, which are ascribed on several strands. The long-term stability of this fabricated biosensor was assessed by storing the electrode in phosphate buffer (pH 7.0) at 40 C for 35 days and the electrode perpetuated 92% of its initial response to 1 x 10-5 M H₂O₂. The repeatability of the biosensor for current response was also evaluated and the relative standard deviation (R.S.D.) was 3.5% for 10 successive assays using the same enzyme electrode. A comparison of performances of this fabricated biosensor with other recent H₂O₂ biosensors fabricated with redox enzyme/protein and different nonmaterial has been summarized in Table 1 which suggests that the proposed biosensor offers satisfactory stability and acceptable reproducibility with lower detection limit [38-40].

The insight of this work has an impetus to investigate the direct electrochemistry of catalase on the electrode surface by immobilizing with the polymerized SnO₂ multiporous nanofibers (MPNFs) with its application in biosensing. The results demonstrated in this study corroborates that a well-defined redox peaks are capable of being formed from redox group of catalase and the fabricated electrode exhibits a high catalytic efficiency towards H₂O₂. Amperometric experiments were executed under optimal condition (pH 7.0 and applied potential -0.4V). The modified electrode exhibited a good catalytic response to H₂O₂ with a longer liner range 10-120 μM and a LOD of 0.6 μM. Moreover, the biosensor showed acceptable stability, reproducibility and repeatability. The overall capabilities of the fabricated biosensor indicate that it can be convenient in sensitive detection of H₂O₂ with its possible application in biomedical and industry; also, the multiporous SnO₂ nanofiber can be a promising nonmaterial for fabricating more advanced biosensor in future.

University Malaysia Pahang local research grants (RDU 1703176).

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