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Rhodium Nanoparticles and Halloysite Nanoclay as Electrode Modifiers for Electroanalytical Determination of Paracetamol

Despite the known side effects of liver damage, among other issues, paracetamol (N-acetyl-p-aminophenol) continues to be one of the most commonly used drugs worldwide for conditions such as pain and fever and it is often purchased without medical prescription. It is usually administered as a tablet, but it is also available as solutions, suppositories and intravenous preparations. In addition, paracetamol is often taken in association with other drugs like caffeine, tramadol and codeine [1-3].


Introduction
Despite the known side effects of liver damage, among other issues, paracetamol (N-acetyl-p-aminophenol) continues to be one of the most commonly used drugs worldwide for conditions such as pain and fever and it is often purchased without medical prescription. It is usually administered as a tablet, but it is also available as solutions, suppositories and intravenous preparations. In addition, paracetamol is often taken in association with other drugs like caffeine, tramadol and codeine [1][2][3].
Given its chemical, commercial and medical significance, several methods of analysis have been developed to determine its content accurately in multiple kinds of samples. Analytical techniques such as spectrophotometry [4][5][6], chromatography [7][8] and mass spectrometry [9][10] have been employed in the determination of paracetamol, as well as electrochemical techniques [11][12][13] which offer a reliable, fast and simple method of analysis with no need for complicated sample preparation procedures.
Among other areas of research, electroanalytical sensors have been constructed in order to enhance analytical parameters using diverse components. In this context, nanomaterials are notable for their unique electrical, optical and magnetic properties [14][15]. Several different nanomaterials have been synthesised and applied in the construction of electrochemical sensors. A series of metallic nanoparticles stabilized in a zwitterionic surfactant (ImS3-14) was found to be suitable for this purpose, due to the metallic nature and small size of the particles and because the stabilizer itself, i.e., the zwitterionic surfactant, can be used as a modifier for electrochemical sensors [16][17][18][19].
Halloysite nanoclay (HNC) also attracts interest not only due to its effect in enhancing analytical parameters for electrochemical sensors, but also because it is widely available, cost effective and biodegradable [20,21]. The aim of this study was to investigate the suitability of a sensor constructed with a mixture of halloysite nanoclay and rhodium nanoparticles stabilized in zwitterionic surfactant (Rh-(ImS3-14)) for paracetamol determination.

Instrumentation
The voltammetric experiments were carried out using an Autolab PGSTAT204 potentiostat (Eco Chemie, The Netherlands). The measurements were performed in an electrochemical cell containing 10mL of supporting electrolyte using a threeelectrode system: platinum wire as the auxiliary electrode, Ag/ AgCl (3.0mol L -1 ) as the reference electrode, and the proposed sensor as the working electrode (HNC-Rh-(ImS3-14)/GCE). All measurements were carried out at room temperature (25°C) and no deoxygenation procedures were taken.
Electrochemical impedance spectrometry (EIS) experiments were performed using an Autolab PGSTAT128N potentiostat (Eco Chemie, The Netherlands). For both potentiostats, the software Nova 1.10 was used to collect and evaluate the electrochemical data. Spectrophotometric measurements were performed with a Cary 60 UV-Vis spectrometer (Agilent Technologies, USA). Profilometric measurements were taken on a Dektak XT profilometer (Bruker). Transmission electron microscopy (TEM) analysis was performed on a JEOL JEM-1011 TEM microscope operating at 100 kV at LCME/UFSC, Florianópolis, Brazil.

Sample preparation
Ten tablets containing 750mg of paracetamol purchased from a local drugstore were macerated. From the resulting powder an aliquot (150mg) was dissolved in 2.5mL of 0.1mol L -1 NaOH, 5mL of water were added and the resulting mixture was agitated for 15 min. After the agitation, the mixture was diluted with water in a 10mL volumetric flask and the mixture was then filtered. From the liquid part of the filtered mixture, 1mL was transferred to a 10mL volumetric flask, along with 1mL of 0.1mol L -1 NaOH, and the volume completed with water. The resulting solution was transferred to an amber flask and kept under refrigeration.

HNC-Rh-(ImS3-14) sensor construction
An aliquot (100µL) of the Rh-(ImS3-14) solution was mixed with 100mg of halloysite nanoclay and the resulting suspension (HNC-Rh-(ImS3-14)) was stirred using a vortex mixer for 1min. A glassy carbon electrode (GCE) was polished using an aqueous alumin a (0.05µm) suspension for 2min. It was then immersed in deionized water and sonicated for 5 min. The electrode was dried and 2µL of the (HNC-Rh-(ImS3-14)) suspension were deposited on the clean surface employing the drop coating method. The solvent (chloroform) was left to evaporate at room temperature and the modified GCE was used as the working electrode.

Preparation and characterization of the (HNC-Rh-(ImS3-14)) dispersion
The (HNC-Rh-(ImS3-14)) suspension was characterized by TEM. The sample for TEM analysis was prepared by deposition of the chloroform (HNC-Rh-(ImS3-14)) dispersion on a carboncoated copper grid. Figure 1A shows the halloysite nanoclay nanotubes well dispersed in the sample as well as the size range as predicted by the manufacturer. At a greater magnification ( Figure 1B), it can be observed that the surfactant-stabilized Rh NPs are also well dispersed in the halloysite nanoclay dispersion.
The histogram constructed from the measurement of the Rh nanoparticles observed in the TEM images ( Figure 2) shows that they are very small, despite being polydispersed in terms of size. They are roughly spherical in shape with diameters ranging from 5 to 11nm, based on the measurement of around 300 nanoparticles. The thickness of the (HNC-Rh-(ImS3-14)) film on the GCE was determined, in triplicate, by profilometry measurements. Under the optimum conditions of construction, the average thickness obtained for the film was 7.80±2.43 µm.

Electrochemical response
An electrochemical impedance spectroscopy (EIS) assay was performed in order to compare the resistance of the surface of the proposed sensor to that of Rh-(ImS3-14)/GCE and bare GCE in the presence of Fe(CN) 6 3-/4- (Figure 3). From the semicircular portion of the Nyquist plots, which corresponds to the charge transfer resistance (R ct ), the effect of each modifier on this process can be observed. The R ct values calculated for the electron transfer resistance were 1.74kΩ for the bare GCE, 614Ω for the Rh-(ImS3-14)/GCE and 409Ω for the HNC-Rh-(ImS3-14)/GCE.
Thus, R ct is lower when using the Rh-(ImS3-14)/GCE system in comparison to the bare GCE and the addition of halloysite nanoclay causes a further decrease in R ct , which is consistent with results reported in the literature [21]. The electrode area was determined by cyclic voltammetry at scan rates varying from 10 to 200mV s -1 using Fe(CN) 6 3-/4-5 mmol L -1 in KCl 0.1 mol L -1 as the probe and the Randles-Sevcik formula: Where I p refers to the peak current, n is the number of electrons transferred, A is the surface area of the electrode, D is the diffusion coefficient (D = 6.7 x 10 -6 cm 2 s -1 ) [22], C is the concentration (9.9 x 10 -5 mol L -1 ), n is the number of electrons (n=1). From the slope of the plot I p vs v 1/2 , the electroactive area was calculated for the proposed sensor (A=0.0406cm 2 ) to and for bare GCE (A=0.0217cm 2 ). Hence, it can be concluded that the proposed sensor almost doubles the electroactive area of the electrode.
The effect on the paracetamol peak current of each component on the GCE surface was also evaluated. It can be observed from Figure 4 that the addition of each component contributes to the enhancement of the peak current. The peak displacement observed when the surfactant (ImS3-14) and the Rh NPs stabilized in the surfactant are added, is slightly reversed by the presence of the halloysite nanoclay, which indicates a catalytic effect on the paracetamol oxidation. Given the results obtained from the EIS study and the electrode area determination, it can be concluded that the enhancement of the oxidation peak is due to a combination of a lower charge transfer resistance and the increased electroactive surface area due to the presence of the modifiers.

Optimization of sensor construction and experimental parameters
Studies were performed in order to determine the optimum amount of halloyiste nanoclay in relation to the (Rh-(ImS3-14)) solution as well as the number of layers of the suspension in the electrode surface that provides the highest electrochemical response for the paracetamol oxidation. Three different dispersions were prepared by adding varied volumes of the (Rh- (ImS3-14)) solution to a flask containing a fixed amount (1 mg) of halloysite nanoclay. The results show that the best ratio was obtained with the dispersion comprised of 100µL of (Rh- (ImS3-14)) solution per 1mg of halloysite nanoclay. Thus, this ratio was applied in the subsequent experiments.
The number of layers deposited on the GCE surface in relation to oxidation peak current was also investigated. It was found that with more than one layer of solution the electrochemical response decreased, probably due to a blocking effect. Consequently, experiments were performed applying one layer comprised of 2µL of the (HNC-Rh-(ImS3-14)) suspension onto the surface of the GCE.   Cyclic voltammetry (CV) was employed to investigate the influence of the pH on the peak currents for paracetamol oxidation ( Figure 5A). The pH was varied from 2.0 to 7.0 using 0.1mol L -1 acidified acetate buffer solution (pH 2.0-3.0), 0.1mol L -1 acetate buffer solution (pH 4.0-5.0) and 0.1mol L -1 phosphate buffer solution (pH 6.0-7.0). The optimum response was obtained in acetate buffer pH 5.0, where the potential was found to be 0.56 V and, therefore, this was chosen as the supporting electrolyte for subsequent studies.
The relation between the peak potential and pH ( Figure 5B) was found to be linear (r 2 = 0.98) with a slope of -37.03 mV/ pH, indicating a complex electron transfer reaction with an uneven number of protons and electrons exchanged, as reported previously in the literature [23]. From the cyclic voltammograms ( Figure 5C) it can also be concluded that the paracetamol in this system shows an evident oxidation peak and the reduction peak is almost absent, behaviour consistent with an irreversible system. For verification, the potential was plotted against the logarithm of the scan rate, which gave a straight line (E p =-0.52+0.04log v). Therefore, considering the observed variation in the potential in relation to the peak potential, the irreversibility of the system was confirmed. The plot of the logarithm of the anodic peak current vs. logarithm of the scan rate provided a straight line (log i p = -6.73+0.47log v) with a slope of 0.47. It can thus be concluded that the system is diffusion-controlled, since the value obtained for the slope is close to the theoretical value of 0.5 for a purely diffusioncontrolled processes in which the analyte diffuses to the electrode surface due to a concentration gradient [24].
In order to determine the best set of parameters to perform the analytical determination, three electroanalytical techniques -linear sweep voltammetry (LSV), square-wave voltammetry (SWV) and differential pulse voltammetry (DPV) were investigated and optimized. For the LSV evaluation, the parameter investigated was the scan rate (10, 25, 50 and 75mV s -1 ). The scan rate of 25mV s -1 was selected since this provided the greatest response and the best peak profile.
For the SWV optimization, three parameters were studied: scan increment (1-7mV), pulse amplitude (10-90mV) and frequency (10-40Hz). Noise was observed at higher values, thus limiting the study range. A scan increment of 5mV, pulse amplitude of 60mV and frequency of 10Hz were selected as the optimized parameters, since these values provided the best results in terms of peak current and voltammetric profile.
Lastly, the DPV technique and its parameters were assessed: scan increment (1-10mV), pulse amplitude (10-170mV) and time (0.1-0.7s). The best results were obtained at a scan increment of 6mV, pulse amplitude of 130mV and time of 0.8s. The figures of merit for each technique are shown in Table 1. The limits of detection and quantification were calculated according to the following equations: LOD = 3s/m; LOQ =10s/m Where s is the standard deviation of the y-intercept and m is the slope of the calibration curve. From the data observed in Table 1, it can be concluded that DPV provides the lowest limit of detection (LOD) and limit of quantification (LOQ) for the proposed sensor in the paracetamol determination, a result consistent with the literature [25]. The calibration curve obtained using this technique is shown in Figure 6.

Precision studies
Repeatability was evaluated with interday and intraday essays in acetate buffer (0.1mol L -1 , pH 4.0) containing 5.96µmol L -1 of paracetamol using DPV (increment 6mV, pulse amplitude 130mV and time 0.8s). Interday repeatability was assessed by evaluating the response of 10 different sensors built with three different GCEs in assays carried out on the same day. For each measurement a new sensor was constructed and the RSD was 5.57%. Intraday studies were carried out under the same conditions as the interday studies, performing 10 experiments on 3 different days with three different GCEs, making a total of 18 measurements. The RSD was 9.97 %. From the results, it can be concluded that the proposed sensor has good repeatability.

Interference studies
Experiments were performed aiming to determine the interference of other compounds in the analysis of paracetamol using the proposed sensor, by comparing the response for paracetamol when adding other substances in fixed amounts. The compounds selected were cellulose and starch, which are commonly employed as excipients. They were tested in the proportions of 1:1, 1:5 and 1:10, in relation to the amount of paracetamol, and they did not interfere with the peak currents for paracetamol due to their non-electroactive nature.
Caffeine, a compound commonly present in pharmaceutical preparations with paracetamol, was also tested for selectivity under the same conditions described for the previously mentioned substances. The results show that the interference of caffeine in relation to the peak currents for paracetamol is < 10%.
Based on these results, it can be concluded that the proposed method provides selectivity for the sample studied as well as for samples containing caffeine in their composition.

Analytical application of the proposed sensor
In order to evaluate the accuracy of the proposed method, an analytical determination was performed employing paracetamol tablets purchased in a local drugstore. The result obtained for the paracetamol content was 747.1±3.57mg. Thus, in comparison to the expected value of 750mg, the relative error was 1.67%, verifying that the proposed method has good accuracy. The percentage recovery ranged from 107.6 to 123.2%, which demonstrates the satisfactory accuracy of the proposed method.

Conclusion
The proposed sensor was found to be suitable for paracetamol determination since it provides peak enhancement due to a synergic effect between the Rh-(ImS3-14) nanoparticles and the HNC. It also exhibits good analytical parameters such as precision and accuracy. In addition, it can be concluded that the HNC-Rh-(ImS3-14) sensor presents good sensitivity and a low limit of detection in comparison to results recently published for similar studies ( Table 2). Given the fact that the sensor preparation is fast, easy and yields good analytical parameters, this represents a suitable method for paracetamol determination [25][26][27][28][29][30][31][32].