key: cord-0983674-3vzp1b0e
authors: Ozoemena, Okoroike C.; Ehirim, Tobechukwu J.; Khawula, Tobile; Makgopa, Katlego; Shai, Leshweni J.; Ozoemena, Kenneth I.
title: Bovine Serum Albumin-Dependent Charge-Transfer Kinetics Controls the Electrochemical Immunosensitive Detection: Vibrio cholerae as a Model Bioanalyte
date: 2021-06-09
journal: Electrocatalysis (N Y)
DOI: 10.1007/s12678-021-00673-8
sha: 0e3c5763936534a50c1d72ab8f31eaabff9f0f4c
doc_id: 983674
cord_uid: 3vzp1b0e

This work investigates how bovine serum albumin (BSA), a commonly used protein in the fabrication of electrochemical immunosensors, can impact on the sensitivity of detection when integrated with antibody (Ab) pre-encapsulated with (i) insulating polyacrylonitrile (PAN) fibre (i.e., GCE-PAN-Ab-BSA immunosensor) or (ii) conducting PAN-grafted iron (II) phthalocyanine (FePc) (i.e., GCE-PAN@FePc-Ab-BSA immunosensor), using Vibrio cholerae toxin as a case study bioanalyte. Both immunosensors show different charge-transfer kinetics that strongly impact on their immunosensitive detection. From the electrochemical data, GCE-PAN-Ab-BSA is more insulating with the presence of BSA, while the GCE-PAN@FePc-Ab-BSA is more conducting with BSA. The CV of the GCE-PAN-Ab-BSA is dominated by radial diffusion process, while that of the GCE-PAN@FePc-Ab-BSA is planar diffusion process. The behaviour of GCE-PAN@FePc-Ab-BSA has been associated with the facile coordination of BSA and FePc that permits co-operative charge-transport of the redox probe, while that of the GCE-PAN-Ab-BSA is related to the interaction-induced PAN-BSA insulating state that suppresses charge-transport. As a consequence of these different interaction processes, GCE-PAN-Ab-BSA immunosensor provides higher electroanalytical performance for the detection of Vibrio cholerae toxin (with sensitivity of 16.12 Ω/log [VCT, g/mL] and limit of detection (LoD) of 3.20 × 10(−13) g/mL compared to those of the GCE-PAN@FePc-Ab-BSA (4.16 Ω/log (VCT, g mL(−1)) and 2.00 × 10(−12) g/mL). The study confirms the need for a thorough understanding of the physico-chemistries of the electrode platforms for the construction of immunosensors. Although this work is on immunosensors for cholera infection, it may well apply to other immunosensors. [Image: see text]

Cholera is a disease that demonstrates the global socio-economic inequalities. It is mostly the disease more prevalent in povertystricken communities. It is a bacterial disease that is characterized by diarrhoea, dehydration, vomiting, and death, especially if it is not quickly detected and treated. The causative agent of cholera is called Vibrio cholerae, a bacterium that produces cholera toxin. The onset of the infection with V. cholerae follows the ingestion of contaminated drinking water or food by humans. It was shown in a study conducted between 2000 and 2008 that about 1.4 billion of people were at the risk of cholera infection, and children over the age of 5 years were found to show symptoms of cholera infection [1] . The reported cholera infection across the globe remains between 1.3 and 4.0 million [2] . Several techniques exist for the diagnosis of cholera infection, with the culture method as the gold standard [3] . Unfortunately, culture method is still associated with several disadvantages, including huge time-consumption, high cost, and the requirement of well-trained specialists to carry out the analysis. For example, culture method can take up to 8 days to get the results while, according to literature [4] , cholera kills within 12 to 24 h if not treated. There are many other methods such as enzyme-linked immunosorbent assay [5] , polymerase chain reaction (PCR) [6, 7] , and electrochemical methods [8] [9] [10] [11] [12] [13] [14] [15] . Of all the aforementioned techniques, electrochemistry gives excellent promise for fast detection, simplicity, sensitivity, selectivity, and ability to miniaturize the process for the development of hand-held point-of-care diagnostic devices. There is a need to continue to research on the development of electrochemical methods for improved detection of cholera infection.

Generally, electrochemical immunosensors involve the modification of an electrode surface or platform with a specific antibody (or antigen) to allow for the interaction of the corresponding antigen (or antibody). The main attraction of immunosensors is their high specificity of interaction as only specific antibody interacts with its specific antigen in a lock-and-key manner. The electrode platform used in the fabrication of the immunosensors is a key determining factor for the sensitivity of detection. Thus, several researchers have reported several electrode platforms for the immobilization of cholera immunosensors. These electrode platforms include graphene [8] , liposomes and poly(3,4ethylenedioxythiophene)-coated carbon nanotubes [9] , dendrimers integrated with gold nanoparticles [10] , zinc oxide [11] , polyacrylonitrile (PAN) nanofibres [12] , copper (II) complex with polypyrrole-nitrilotriacetic acid on carbon nanotubes [13] , carbon nanofibres (CNF) [14] , and onionlike carbon modified with PAN (OLC-PAN) [15] . In electrochemistry, to be redox-active, a material must be able to lose or gain electrons (i.e., conducting), while a redox-inactive (or redox-silent) material is insulating. Unlike inorganic materials, most polymeric materials are bio-compatible with antibodies and antigens; hence, their use as electrode platforms for immunosensors. Most studies on immunosensors, in particular those using polymeric electrode platforms (redox-active or redox-inactive), focus on determining the basic analytical parameters (such as detection limits and linear concentration range) with no interest or effort on understanding the scientific reasons for the differences in the analytical data. This is the key motivation for this work.

Bovine serum albumin (BSA) is an important protein which is popularly used to block non-specific sites in the immunosensing platforms [9] [10] [11] [12] [13] [14] [15] [16] [17] . In electrochemical immunosensors, the sensing mechanism is generally dominated by capacitance (i.e., non-Faradaic detection) due to the redox-inactivity of the electrode platform upon which the antibody or antigen is immobilized. Generally, the introduction of the BSA onto the electrode platforms (redox-active or redox-silent) enhances the insulating behaviour of the immuosensors. The question is "why is this so"? The answer is that BSA is unable to interact with the species that make up the electrode platform. So, the next question would be "What if the electrode platform contains a specie that can interact with BSA, leading to electrocatalysis or enhanced charge-transfer kinetics, to what extent can this affect the immunosensing detection"? To our knowledge, there is no study that has attempted to investigate nor answered this very important question. The answer to the question will allow researchers to make rational decision on the type of electrode platform that should be employed in constructing an immunosensor, in terms of the ability of the electrode material to enhance electrocatalysis (i.e., Faradaic response, or enhanced charge-transfer kinetics) or reduce it (i.e., insulating, or poor electron transfer kinetics).

In this work, for the first time, we investigate the use of polyacrylonitrile (PAN) fibre (which is non-conducting) and iron(II)phthalocyanine-polyacrylonitrile (PAN@FePc) fibre (which is conducting due to the presence of the FePc species) as electrode platforms for the immobilization of cholera antibody for the detection of Vibrio cholerae toxin (antigen). The work reveals, amongst other findings, that (i) both PAN and PAN@FePc exhibit different physico-chemical properties (in terms of morphology, surface areas, and pore volumes), which have direct impact on their voltammetry and limits of detection of Vibrio cholerae toxin, and (ii) that BSA interacts with redox-active FePc in PAN, leading to enhanced chargetransfer processes that are inimical to the sensitive detection of Vibrio cholerae toxin.

All the reagents used were obtained from Sigma-Aldrich South Africa, and include the following: polyacrylonitrile, iron(II)phthalocyanine (FePc), glycine, 1-ethyl-3-(3dimethylaminopropyl) carbodiimide hydrochloride (EDC), N-hydroxysulfosuccinimide (Sulfo-NHS), cholera toxin B subunit antigen (Ag) (from Vibrio cholerae Cat. No. C9903, 95% SDS-PAGE, lyophilized powder), anti-cholera toxin antibody (Ab) (from rabbit, whole antiserum, Cat. No. C3062), bovine serum albumin (heat shock fraction, pH 7, ≥ 98% purity), and thiosulphate citrate bile salt (TCBS). All the reagents for the experiments were prepared using ultrapure water (18.2 M Ω cm resistivity). Phosphate buffer, containing small amounts of sodium azide (as a preservative) and EDTA (for disentangling cells) (PBS/AE, pH 7.4), was prepared as described in the literature [18] . The redox probe (0.1 M K 4 Fe(CN) 6 /K 3 Fe(CN) 6 (1:1 mixture) was prepared using the PBS/AE, pH 7.4.

Electrospun polyacrylonitrile (PAN) fibre and iron (ll) phthalocyanine (FePc)/polyacrylonitrile fibre (PAN@FePc) hybrid were obtained by electrospinning procedure [19, 20] . The procedure is summarized in Fig. 1 .

First, the precursor materials (PAN or a mixture of PAN and FePc, 1:1 mixture) were dissolved in DMF at the ratio of 1 mg PAN or PAN@FePc to 2 ml DMF and properly ultrasonicated to form a solution. The solution was then injected through the syringe into the electrospinning machine at 10 kV power supply and at room temperature at a flow rate of 0.6 mL/h. A distance of about 15 cm was maintained between the aluminum collector plate and the syringe point. The collected products (PAN fibre and PAN@FePc fibres) were collected, soaked in distilled de-ionized water for about 12 h to wash off the DMF, then oven-dried (60 °C for 2 h) to give the final products.

During the fabrication of the immunosensor, the conventional method of covalent linking of the antibody on the electrode platform was strictly adhered to as previously reported [14, 15] . This is summarized as follows: the bare electrode (GCE) was cleaned, then the nanomaterial (e.g., PAN) dissolved in 10-μL DMF solution and drop dried on the bare GCE, which was slowly dried at 40 °C to form GCE-PAN. The GCE-PAN was immersed in a solution of 2 M NaOH for 2 h at 40 °C, to expose the -COOH group for subsequent covalent bonding with EDC/sulfo-NHS mixture. Then, the carboxylated carbonaceous fragments were washed off on the electrode surface to enhance the coordination of the -NH 2 group of the Vibrio cholerae antibody (5 μL from 1-mL commercial solution) to form GCE-PAN-Ab. BSA was introduced to block non-specific sites of the porous electrode, resulting the final modified electrode abbreviated as GCE-PAN-Ab-BSA. The same process was also followed in the modification of PAN@ FePc, and the final immunosensor produced was abbreviated as GCE-PAN@FePc-Ab-BSA. The final modified immunosensor was stored at 4 °C until use. The procedure for electrochemical immunosensor fabrication is summarized in Fig. 2 below.

An Autolab Potentiostat PGSTAT 100 (Eco Chemie, Utrecht, The Netherlands) driven the General-Purpose Electrochemical System (GPES® version 4.9) was used for all the electrochemical experiments, including the cyclic voltammetry (CV) and electrochemical impedance spectroscopy (EIS). Glassy carbon electrode (GCE, diameter = 3.0 mm, BAS®) with or without the modifying materials, PAN and PAN@FePc, served as the working electrode, Pt rod, and Ag/AgCl (3 M KCl) served as the counter and reference electrodes, respectively. Before using the electrolyte for any experiment, it was first de-aerated with pure nitrogen (Afrox, South Africa), which is conducted at room temperature. Every EIS experiment was carried out with the GPES® Frequency Response Analyzer (FRA) software between 100 kHz and 0.01 Hz with the amplitude (rms value) of the ac signal of 10 mV, in the electrolyte solution containing the redox probe (0.1 M K 4 Fe(CN) 6 /K 3 Fe(CN) 6 (1:1 mol ratio) dissolved in 0.14 M PBS/AE (pH 7.4)). The EIS was performed at the equilibrium potential (E 1/2 ) of the redox probe (ca. 0.13 V vs Ag|AgCl, 3 M KCl). Figure 3 compares the SEM images of PAN fibres (A) and PAN@FePc fibres (B). Both materials exhibit one-dimensional morphology, with the PAN fibres showing fine and smooth structure of about ≤ 0.5 μm in diameter and several microns in length. The PAN@FePc fibres, on the other hand, gave rough fibres with an average diameter of ≥ 2.5 μm, which is more than five times greater than that of the average PAN fibre. Brunauer-Emmett-Teller (BET) analysis was conducted to further establish the physical properties of the PAN and PAN@FePc fibres. From the BET data, the FeP-PAN fibres exhibit surface area (37.56 cm 2 g −1 ) and pore volume (0.20 cm 3 g −1 ) which are more than twice those of the PAN fibres (i.e., 17.87 cm 2 g −1 and 0.08 cm 3 g −1 ).

The Faradaic current that flows at an electrode surface is interpreted on two inexorably intertwined processes: (i) the mass transport (i.e., the diffusion rate of the analyte from the bulk electrolyte to the electrode) and (ii) charge-transfer kinetics (i.e., electronic or ionic transport across the electrode-electrolyte interface) [21] . Figure 4 compares the cyclic voltammograms (CVs; Fig. 4A , B) of the PAN and PAN@FePc before and after the introduction of BSA to obtain the final immunosensors. Table 1 summarizes the CV parameters of the electrodes, with and without the BSA.

The ratio of the anodic-to-cathodic peak current (I pa /I pc ) provides some insight into the kinetics of the electrodes; the best reversibility gives the ratio as unity. With the exception . The increase in current response (mass transport) and electrode kinetics following the introduction of the antibody (observed in both redox-active and redox-inactive electrode platforms) is somewhat surprising considering that antibody is known to be bulky and not as conducting. However, similar observations have been made by Solanki and co-workers [11, 12] who attributed the behaviour to either the presence of the redox mediator in the electrode platform [12] or the porous nature of the electrode surface [11] . We believe that similar processes are taking place in this work but, in addition, mass transport/diffusion modes (as described before [21] ) and will be discussed below, are playing key electrochemical roles.

The CV data show that the presence of BSA strongly suppressed the current response at the GCE-PAN-Ab-BSA but enhanced that of the GCE-PAN@FePc-Ab-BSA. This result suggests that BSA easily interacts or co-operate with FePc to catalyze the redox activity of the probe, thus fast chargetransfer kinetics. On the contrary, with the PAN alone, the interaction with the BSA leads to a more insulating state that strongly suppresses charge-transfer kinetics. Surprisingly, this finding has rarely been reported in any BSA-incorporated electrochemical immunosensors. For example, Gupta et al. [11] observed higher electron transfer rate constants (highrate constant) with ITO-ZnO-Ab-BSA immunosensor than the corresponding electrodes without BSA (i.e., ITO-ZnO or ITO-ZnO-Ab) and attributed the finding only to the porous nature of the electrode surface. Similar to our case, PAN@ FePc is more porous than the PAN (see BET data in Table 1 ), but we believe that the redox kinetics of BSA in the presence of FePc is beyond the porous nature of the PAN@FePc electrode. From literature reports, the following are apparent: First, the adsorption of BSA with non-metal and polymeric materials is generally accompanied with increased chargetransfer resistance (R CT ) [22, 23] ; thus, the poor R CT observed with the GCE-PAN-Ab-BSA immunosensor electrode is not surprising. Second, transition metallophthalocyanines (MPc = where M = Fe, Co, Cu, Ni, etc.) are known for their electrocatalytic/redox activities due to their central metal ions [24] [25] [26] [27] [28] [29] ; thus, the redox activity of the FePc in this work is not surprising. Third, the interaction of FePc with BSA in this work is highly possible for the following reasons: (i) BSA interacts and binds with a large variety of mononuclear and polynuclear metal ion complexes with aromatic ligands [30, 31] ; (ii) BSA has a binding/adsorption affinity with Fe-based materials; for example, it interacts with steel and such adsorption has been reported to be accompanied by a fast charge-transfer [31] ; (iii) BSA interacts with magnetic iron oxide nanoparticles, and such interaction is very spontaneous, i.e., negative change in the Gibb's free energy (− ΔG) [32] ); and (iv) the binding energy of BSA with transition metal ions is slightly smaller/less stable with some transition metal ions (such as Fe 2+ , Ni 2+ , Co 2+ ) than others (such as Cu 2+ and Zn 2+ ) [33] . Fourth, the co-operative catalysis of BSA-FePc in this work is possible because (i) BSA has been reported to be a good catalyst only when it is conjugated with a co-catalyst such as an MPc complex (e.g., BSA-conjugated CuPc complex catalysed Diels-Alder reaction [34] ), or iodine (e.g., co-operative cascade catalysis by BSA-iodine complex [35] ). Thus, it can be concluded that the faster electron-transfer kinetics (electrocatalysis) observed for the GCE-PAN@FePc-Ab-BSA is related, not just to its high surface area and pore volume of the PAN@ FePc compared to the PAN fibres, as confirmed by the BET data, but due to the co-operative interaction of FePc and BSA. Next, we investigated the voltammetric behaviour of the two BSA-conjugated immunosensors (GCE-PAN-Ab-BSA and GCE-PAN@FePc-Ab-BSA) in the redox probe at various scan rates. As seen in Fig. 5 , the GCE-PAN-Ab-BSA showed sigmoid-like voltammograms at every scan rate (Fig. 5A) , which is characteristic of radial or convergent diffusion process in microelectrodes [36] [37] [38] (Fig. 5C) . On the other hand, the GCE-PAN@FePc-Ab-BSA showed welldefined voltammetric response at every scan rate (Fig. 5B) , characteristic of linear diffusion observed in macroelectrodes [21, 39, 40] (Fig. 5D) .

Unlike the voltammograms observed in the PAN-based immunosensor, the peak current in PAN@FePc-based voltammograms showed direct proportionality with the square root of the scan rate, clearly confirming the planar diffusion process. The voltammetric responses at the PANbased immunosensor (micro-electrodes) are quite different from those observed at the PAN@FePc-based immunosensor (macro-electrodes) because at different scan rates, the Electrochemical immunosensing of Vibrio cholerae toxin (VCT) was conducted using EIS. Figure 6 shows typical Nyquist plots obtained at different concentrations of the VCT. The electroanalysis was conducted by casting 2 μL of the VCT on the immunosensor surface and allowed to incubate for 20 min (see Fig. 1 ). As summarized in Fig. 1 , upon incubation of the VCT onto the immunosensor, the extent to which immobilized antibody interacts with the VCT is established by the inhibition or resistance to the one-electron redox kinetics of the probe (Fe(CN) 6 Table 2 summarizes the analytical parameters of merit, including the linear concentration range (LCR), sensitivity, limit of detection (LoD), and limit of quantification (LoQ), [14, 40] . Both immunosensors gave satisfactory LoD with the GCE-PAN-Ab-BSA giving the least LoD of 3.2 × 10 −13 g / mL compared to that of the GCE-PAN@ FePc-Ab-BSA of 2.0 × 10 −12 g/mL. As compared in Table 2 , only few reports gave lower LoD of ~ 10 −15 g/mL [10] and ~ 10 −17 g/mL [15] , while the LoDs obtained in this work are comparable or even better than some reports [9, [11] [12] [13] [14] .

From the result, the insulating electrochemical immunosensor (i.e., GCE-PAN-Ab-BSA) provides the best immunosensing towards Vibrio cholerae compared to the conducting electrochemical immunosensor (i.e., GCE-PAN@FePc-Ab-BSA). The high performance of the PAN-based immunosensor is related to its redox-inactive nature (assisted by the efficient blocking of the non-specific sites by the BSA), while the PAN@FePc-based immunosensor is related to its redox-activity (assisted by the facile co-operative interaction of BSA with FePc).

Considering the high performance of the GCE-PAN-Ab-BSA immunosensor, selectivity, repeatability, and stability studies were conducted with this immunosensor. The interferents (UA, CA, and AA) were used at high concentrations (~ 0.5 mg/mL) compared to the VCT (17.9 ng/mL) (Fig. 7) . Figure 7 shows that there is little or no difference in the SWV response in the presence and absence of the interfering species. To determine the repeatability of use, the conventional method of analysis was adopted. First, the immunosensor was deployed to detect VCT (i.e., 8.90 × 10 −7 g/ mL). Then, the immunosensor was cleaned to wash off the VCT that was bound onto the surface by dipping it into a glycine HCl buffer solution (pH 2.8) for 5 min, and then deployed again to detect the VCT by repeating the processing of incubation and electrochemical testing in the redox probe solution. The whole process of immunosensor surfaceregeneration, re-incubation, and electrochemical testing was repeated five times to determine if there is any change in the electrochemical response from the initial immunosensor surface. The result shows about 13% loss in signal response from the original signal, meaning that the immunosensor shows satisfactory stability and can be used repeatedly without significant deterioration in signal response.

This work is an attempt to understand how BSA, a commonly used biomolecules in constructing immunosensors, can impact on the electrochemical detection when integrated with insulating PAN and conducting PAN@FePc electrode platforms, using Vibrio cholerae toxin as a model bioanalyte. Some unique findings should be emphasized. First, both PAN and PAN@FePc show different physico-chemical properties (in terms of morphology and BET surface areas and pore volumes). Second, the voltammetry of the BSA-conjugated PAN-based immunosensor was dominated by radial diffusion process (micro-electrode arrays), while that of the BSAconjugated PAN@FePc counterpart was dominated by planar diffusion process (macro-electrode). Third, both CV and EIS data prove that GCE-PAN-Ab-BSA is insulating (non-Faradaic), while the GCE-PAN@FePc-Ab-BSA is conducting/catalytic (aided by the facile co-ordination of BSA with FePc). Fourth, the suppression of redox kinetics of the redox probe, which forms the underlying detection process for the antibody-antigen, was better observed with the GCE-PAN-Ab-BSA immunosensor than the conducting GCE-PAN@FePc-Ab-BSA immunosensor. The experimental findings prove that the insulating GCE-PAN-Ab-BSA immunosensor possesses the best characteristics for the detection of Vibrio cholerae toxin (in terms of sensitivity, LoD and LoQ). In general, one may conclude that the BSA-conjugation with the electrode platform can lead to different redox-chemistries, Faradaic or non-Faradaic. The immunosensitive detection is dependent on several factors including, but not limited to, surface area, pore volume, and nanoparticulate nature and redox activities.

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Acknowledgements OC Okoroike is grateful for the 2020 TUT Doctoral Scholarship Award and the Wits for permission to visit its School of Chemistry to conduct some of the experiments during the COVID-19 lockdown.Funding This work was supported by Tshwane University of Technology (TUT), University of the Witwatersrand (Wits), and the National Research Foundation.