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Article

Covalent Immobilisation of a Nanoporous Platinum Film onto a Gold Screen-Printed Electrode for Highly Stable and Selective Non-Enzymatic Glucose Sensing

by
Wesley McCormick
1,2,
Pádraig McDonagh
2,
John Doran
1,3 and
Denis McCrudden
1,2,*
1
The Bryden Centre, Letterkenny Institute of Technology, F92 FC93 Letterkenny, Ireland
2
Department of Life and Physical Sciences, Letterkenny Institute of Technology, F92 FC93 Letterkenny, Ireland
3
Department of Engineering, Letterkenny Institute of Technology, F92 FC93 Letterkenny, Ireland
*
Author to whom correspondence should be addressed.
Catalysts 2021, 11(10), 1161; https://doi.org/10.3390/catal11101161
Submission received: 17 August 2021 / Revised: 22 September 2021 / Accepted: 24 September 2021 / Published: 26 September 2021
(This article belongs to the Special Issue Electrocatalysis: From Catalytic Reactions to Energy Storage and Sensing Applications)
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Abstract

:
Progress in the development of commercially available non-enzymatic glucose sensors continues to be problematic due to issues regarding selectivity, reproducibility and stability. Overcoming these issues is a research challenge of significant importance. This study reports a novel fabrication process using a double-layer self-assembly of (3 mercaptopropyl)trimethoxysilane (MPTS) on a gold substrate and co-deposition of a platinum–copper alloy. The subsequent electrochemical dealloying of the less noble copper resulted in a nanoporous platinum structure on the uppermost exposed thiol groups. Amperometric responses at 0.4 V vs. Ag/AgCl found the modification to be highly selective towards glucose in the presence of known interferants. The sensor propagated a rapid response time <5 s and exhibited a wide linear range from 1 mM to 18 mM. Additionally, extremely robust stability was attributed to enhanced attachment due to the strong chemisorption between the gold substrate and the exposed thiol of MPTS. Incorporation of metallic nanomaterials using the self-assembly approach was demonstrated to provide a more reproducible and controlled molecular architecture for sensor fabrication. The successful application of the sensor in real blood serum samples displayed a strong correlation with clinically obtained glucose levels.

1. Introduction

To date, enzymatic glucose sensors remain commercially unchallenged, mainly due to the high selectivity of the enzyme towards glucose. However, the inclusion of an enzyme in biosensor fabrication can cause the sensor to be affected by temperature, pH, humidity and toxic chemicals [1]. Ensuring the stability of the immobilised enzyme and mediator on electrode surfaces also requires considerable attention, often involving elaborate fabrication processes [2].
To overcome the problems associated with an enzymatic biosensor, the fabrication of non-enzymatic glucose sensors has recently been intensively investigated to improve their electrocatalytic activity towards the oxidation of glucose. The non-enzymatic sensing of glucose based on the direct electrochemistry of glucose (oxidation or reduction) is a rapid and cost-effective approach [3]. As the sensor is enzyme-free, all associated enzymatic stability issues and enzyme immobilisation processes are removed from the fabrication process.
However, despite decades of research into non-enzymatic systems, problems associated with this approach have prevented its practical application. These include poor selectivity and reproducibility, slow kinetics of glucose, fouling of the electrode by real sample constituents and the limited number of modifications that are applicable to physiological pH [4]. Non-enzymatic electrocatalysts usually involve the use of a transition metal centre. Many different metals have been investigated, including nickel, copper, cobalt, gold, zinc and platinum [5,6,7,8,9,10]. Of these, platinum has been shown to be the most promising material, although its use as a smooth surface provides low sensitivity and poor selectivity and is susceptible to fouling of the surface [11].
More recent studies have reported that the successful fabrication of a non-enzymatic glucose sensor requires a high real surface area (with high roughness factor) [12]. This results in the highly sensitive and selective electro-oxidation of glucose. This is due to the fact that the adsorption of glucose on the electrode surface is a prerequisite step, and the electro-oxidation of common interfering electroactive species such as ascorbic acid, uric acid and p-acetamedophenol is independent of the electrode’s roughness because it is diffusion-controlled [13].
Nanoparticles display attractive features in electrochemistry as a direct consequence of their nanodimensions. Their size and ultimately the electrochemical active area of the surface can be closely controlled using electrochemical deposition. Recently, nanoporous Pt has been reported to show high sensitivity and an excellent ability to be selective for glucose, while resisting interfering species. These advances were attributed to the increased roughness factor and porosity of the electrode surface, selectively enhancing the current of a sluggish reaction. This feature also resulted in an excellent antifouling property [14,15].
Many reports exist where nanomaterials are prepared, characterised and then applied in microliter quantities to the electrode surface. Such modifications have advanced the non-enzymatic detection of glucose [15,16,17,18,19,20]. However, modifying an electrode in this way can lead to issues with regard to stability and reproducibility. Self-assembled monolayers (SAMs), in contrast, have the ability to provide a more reproducible, simple and reliable procedure to immobilise molecules on various metal surfaces [21,22,23]. SAM formation is an easy method recently used for selected metal nanoparticle chemisorption onto surfaces such as gold, platinum or silver [6]. In chemisorption, much stronger and more stable covalent bonds are formed between the adsorbate and the electrode surface.
In an effort to produce a reliable, reproducible non-enzymatic sensor for glucose, this study describes the immobilisation of a two-stage self-assembled monolayer of (3-mercaptopropyl)trimethoxysilane (MPTS) onto a gold surface. A nanoporous platinum surface is then covalently attached to exposed thiol groups of the MPTS from copper platinum solutions using a voltammetric alloying/dealloying procedure. The surface area of the resulting nanoporous platinum surface is controlled by the number of voltammetric cycles. The sensor is then investigated with regard to its ability to accurately detect glucose in the presence of common interferents and with regard to stability and reproducibility.

2. Results and Discussion

2.1. Electrode Preparation

During the fabrication of the modified sensor, it was imperative that the gold surface was as clean as possible to promote the interaction of gold with the thiol-terminated molecules of the MPTS. Therefore, an electrochemical cleaning step was performed by subjecting the gold electrode to cyclic voltammetry (CV) in a 0.5 M sulphuric acid solution. The voltammetric response of the gold electrode in 0.5 M sulphuric acid displays typical characteristic peaks, shown in Figure 1. The peaks in the anodic scan correspond to different forms of oxide species on the gold surface, and the single reduction peak in the cathodic scan is due to the removal of the oxide layer when reversing the scan direction. The scan obtained was typical of a clean gold electrode in an acidic solution.

2.2. Au-MPTS-Pt Fabrication

The fabrication of the sensor involved immersing the prepared gold electrode in the MPTS solution. MPTS was chosen in this self-assembly approach as, structurally, it possesses two reactive functional groups—the thiol tail and the methoxy headgroup. The thiol tail allows covalent attachment to the gold surface, while the methoxy group can undergo hydrolysis and condensation reactions [24]. This immersion resulted in the attachment of a self-assembled monolayer of MPTS onto the surface by the formation of Au–S bonds. The electrode was then immersed in 0.01 M NaOH, causing the hydrolysis of the self-assembled monolayer through a polycondensation reaction, forming exposed silane units arranged in a 2-dimensional (2D) network. A second immersion of the electrode into the MPTS solution resulted in the formation of a second silane layer via Si-O-Si bonds, producing a surface containing many exposed thiol moieties. The fabrication process of the sensor is shown in Scheme 1. Chemisorption of a nanoporous platinum surface onto the MPTS 2D network was performed by the electrochemical co-deposition of a platinum–copper alloy and the subsequent electrochemical dealloying of the less noble copper using a previously described method [25]. A platinum–copper layer was deposited during the cathodic scan, while removal of the less noble alloying partner in the return scan yielded a porous platinum structure.

2.3. Characterisation of Au-MPTS-Pt

The increase in the surface area of Pt chemisorbed on the MPTS/Au electrode was monitored by electrochemical cycling between −0.25 and 1.4 V in 0.5 M H2SO4. Voltammograms displayed a platinum oxide reduction peak at 0.42 V vs. Ag/AgCl reference electrode similar to that reported previously [26] (Figure 2).
In this study, the oxygen absorption method was used to determine the real surface area of the platinum-modified electrodes. The area under the platinum oxide peak in the CV scan was determined using the automatic peak search option on the potentiostat. The real surface area (cm2) of the modified electrode was determined by dividing the area un-der the oxide reduction peak (μC) by a correction factor of 420 μC cm−2 for a platinum electrode [27]. The surface roughness factor (rf) was then calculated by dividing the real surface area (cm2) by the geometric area (cm2). The electrode subjected to 100 cycles produced a rf of 235, while the electrode cycled 300 times created a rf of 612.
These rf values indicate a significant increase in the electrochemical surface area of immobilised platinum nanoparticles after 300 cycles when compared to that recorded after 100 cycles. Each cycle increased the surface area of the formed nanoporous platinum, resulting in an increased area being available for gold oxide formation in the forward scan and consequently an increase in the reduction peak area in the return scan. Recent studies have demonstrated that nanoporous platinum surfaces deliver many advantages, including a stable, self-supporting, nanometre-sized structure coupled with increased catalytic activity and selectivity for glucose due to the high surface area of the porous surface [15,25,26,28].
Scanning electron microscopy analysis was performed to determine the surface morphology characteristics of the electrode. Figure 3 depicts the FE-SEM images of the surface of the electrode before modification (A) and at different magnifications of the modification (B, C and D). The SEM image of the unmodified gold substrate displays a flat morphology with some ridges and pits (Figure 3A). The SEM image of the nanoporous platinum modified electrode (Figure 3B) shows well-dispersed, spherical platinum clusters with an approximate size of 2 µm. Detailed images at higher magnification of the modified electrode are shown in Figure 3C,D. The platinum clusters contained nanopores of approximately 10 to 20 nm in size, which can be clearly observed in Figure 3D.
The chemical composition of the nanoporous platinum layer was determined by energy-dispersive X-ray spectroscopy (EDX) (Figure 4). Figure 4A shows the spectrum obtained from the electrode that was subjected to 100 deposition cycles, while Figure 4B shows the results from the electrode that had undergone 300 deposition cycles. Both EDX spectra of the nanoporous platinum layer confirm the presence of platinum as the element of the highest percentage weight. Increased deposition cycles in Figure 4B produced an increase in Pt signal (45.0 to 71.9%), which, consequently, led to a reduction in the Si signal (4.9 to 0.8%) from the MPTS. This confirms that with increasing deposition cycles, the platinum percentage weight increased and the available MPTS attachment sites decreased as they were continuously being occupied by platinum. The Au signal was due to the gold substrate on which the platinum was deposited. Other elements appearing in the EDX spectrum were Cu, coming from the residual copper after the dealloying process, and O and C, which were present due to the use of MPTS as the organic linker in the fabrication of the electrode.
The nanoporous Pt surface was analysed by XPS. Figure 5B shows the high-resolution spectra for Pt 4f. The doublet structure revealed dual components with assigned binding energies at 76.7 eV, 4f7/2 and 79.9 eV, 4f5/2. These increased energies can be associated with charging on the platinum surface and increased final state effects due to the nanoparticle size [29]. Previous studies have also shown that Pt-S bond formation can cause a shift in Pt 4f spectra [30]. This would correspond with the covalent nature of the interaction between platinum and the silane linker.

2.4. Electrochemical Detection of Glucose

Cyclic voltammetry was used to evaluate the response of the sensor towards glucose oxidation (voltammograms not shown). The potential at which glucose was oxidised was determined from the addition of glucose concentrations (2, 4 and 6 mM) into 0.1 M PBS. A glucose oxidation peak occurred between 0.35 and 0.45 V, which agrees with previous studies by this group when using a platinum surface [14]. The area of the peak increased linearly with glucose concentration. The performance of the modified platinum electrode was compared with different glucose sensors, as shown in Table 1.

2.5. Interference Study

A major challenge associated with non-enzymatic glucose sensors is eliminating the effects of other physiological interferences commonly found in blood. These interferents can often be oxidised at the same working potential as glucose, which can result in an overestimation of the analyte. The selectivity of Au-MPTS-Pt was investigated by measuring the amperometric response of glucose at potentials of 0.35, 0.40 and 0.45 V in the presence of the common interferents (Figure 6). In physiological conditions, interfering compounds exist at lower concentrations when compared to glucose levels.
Therefore, the amperometric response of the Au-MPTS-Pt to successive additions of 1 mM glucose, 0.1 mM p-acetamidophenol (AP), 0.1 mM ascorbic acid (AA), 0.1 mM uric acid (UA) and 1 mM glucose (Glu), respectively, in a stirred 0.1 M phosphate buffer (pH 7.4) was investigated. Figure 5 shows the change that occurs in the amperometric response at different potentials. There is a minimal response to interfering species at 0.4 V, with no significant effect on the recovery of glucose, which suggests the anti-interference capability and high selectivity of the Au-MPTS-Pt electrode at this potential.

2.6. Amperometric Measurement of Glucose

The performance of the nanoporous Au-MPTS-Pt towards the detection of glucose was then studied by recording the amperometric response at 0.4 V in stirred phosphate buffer (Figure 7). Upon successive additions of 1 mM glucose at regular intervals, significant and fast current responses were observed using the modified electrode, with a steady-state current being achieved within 5 s.
The calibration curve (inset) displays two distinct regions of linearity, similar to the response reported in a number of previous studies [39,40,41,42,43]. The first region provided a linear range from 1 to 7 mM glucose with a regression coefficient of 0.9995 and a sensitivity value of 191.67 µA mM−1 cm−2. The second region displayed a linear range from 7 to 18 mM glucose with a regression coefficient of 0.9995 and sensitivity of 135.98 µA mM−1 cm−2.

2.7. Analysis of Real Samples

Validation studies for the practical application of the Au-MPTS-Pt sensor in real blood serum samples were performed. The sensor was employed to determine the glucose concentration in three clinically validated serum samples obtained from the local university hospital. The samples did not undergo further pre-treatment before the analysis. For each sample, the current response at 0.4 V was recorded for 0.5 mL of serum added to 9.5 mL of 0.1 M PBS (pH 7.4). The glucose content of the serum samples was then calculated from the calibration plot. Results shown in Table 2 display a high degree of accuracy relative to the clinically validated samples.

2.8. Reusability, Stability and Reproducibility

The reusability of a single sensor was evaluated by measuring the amperometric response to 10 samples each containing 1 mM glucose in 0.1 M PBS (Figure 8A). The investigation showed that the sensor exhibits high reusability, with 97% of the sensor’s initial response being recorded after ten uses.
The stability of a sensor stored at room temperature was evaluated by measuring the amperometric response to 1 mM glucose and 0.1 mM interferants every week for ten weeks. The results in Figure 8B show the sensor’s response to glucose and interferents during week 1 and week 10. The responses are displayed as a percentage of the sensor’s initial value, with 93.4% of the sensor’s initial response being recorded after ten weeks.
The reproducibility was evaluated by measuring the amperometric response to 1 mM glucose in 0.1 M PBS using six independently fabricated sensors. The current response of each sensor is presented in Figure 8C and shows a relative standard deviation (RSD) of 1.45%.

3. Materials and Methods

3.1. Materials

All reagents were of analytical grade and used as purchased without further purification. Hexachloroplatinic acid hydrate (H2PtCl6), copper (II) sulphate (CuSO4), methanol (MeOH), (3-mercaptopropyl)trimethoxysilane (MPTS), hydrochloric acid (HCl), sodium hydroxide (NaOH), potassium phosphate monobasic (KH2PO4), potassium phosphate dibasic (K2HPO4), L-ascorbic acid (AA), uric acid (UA), acetamidophenol (AP) and glucose were obtained from Sigma Aldrich (Ireland). Sulphuric acid (H2SO4) and D-glucose were purchased from Fisher Scientific (Loughborough, UK). Ultra-purified water (resistivity ≤18 MΩ cm) supplied by a Milli-Q system (Millipore, Darmstadt, Germany) was used in the preparation of all solutions.
All electrochemical measurements were performed using a CHI660 potentiostat (Shanghai CH Instrument Company, Shanghai, China) and a personal computer for data storage and processing. The electrode assembly consisted of a screen-printed gold working electrode (3 mm Ø), a silver/silver chloride reference (3 M KCl) and a platinum counter electrode.

3.2. Fabrication of the Modified Electrode

The disposable gold electrode was electrochemically cleaned by cycling 50 times be-tween −0.2 and 1.5 V vs. Ag/AgCl in 0.5 H2SO4 at a scan rate of 0.1 V s−1 until a reproducible scan typical for a gold surface was achieved. The MPTS solution was prepared by placing 100 μL MPTS, 300 μL MeOH, 300 μL ultrapure water and 100 μL hydrochloric acid in a conical flask. The solution was then sonicated in a sonic bath for 30 min to allow gelation to occur.
Spontaneously assembled monolayers were formed by immersing the gold electrode in the MPTS solution for 3 h. The electrode was thoroughly rinsed with ultrapure water and immersed in aqueous 0.01 M NaOH for 2 h, causing the silane units of the MPTS to become polymerised into a 2D network. A second silane layer was formed by immersing the electrode back in the MPTS solution for 12 h. The MPTS-modified electrode was rinsed several times with ultrapure water.
A 20 mM H2PtCl6 and 20 mM CuSO4 solution was made by adding 0.0414 g of H2PtCl6 and 0.025 g of CuSO4 to a 5 mL volumetric flask and adding 0.5 M H2SO4. Platinum nanoparticles were electrodeposited onto the MPTS layer by cyclic voltammetry according to a procedure by Kloke and co-workers [28]. The attachment of platinum nanoparticles to the MPTS layer was achieved by multiple repetitions of the electrochemical co-deposition of a platinum–copper alloy and subsequent electrochemical dealloying of copper. This procedure involved subjecting the working electrode to up to 300 CV scans in the platinum–copper solution. The potential range was from 1.4 to −0.6 V vs. Ag/AgCl at a scan rate of 50 mV s−1. The electrode was rinsed with ultrapure water, dried with nitrogen and stored at room temperature. The modified electrode was denoted as Au-MPTS-Pt.

3.3. Structural and Morphological Analysis

The morphological and structural observations were obtained by scanning electron microscopy (SEM) using a Hitachi Regulus 8230. The elemental composition was confirmed by energy-dispersive x-ray spectroscopy (EDX) analysis using an Oxford Instruments Ultim Max 170 and X-ray photoelectron spectroscopy (XPS) using a Kratos Axis Ultra DLD.

3.4. Electrochemical Surface Roughness Determination

Electrochemical characterisation of the Au-MPTS-Pt was performed using cyclic voltammetry by subjecting the electrode to 10 scans in 0.5 M H2SO4 in the potential range from −0.25 to 1.4 V vs. Ag/AgCl at a scan rate of 0.05 V s−1. The charge (μC) associated with the area under the platinum oxide reduction peak in the final scan was divided by a con-version factor of 420 μC cm−2, giving the real electrochemical area of the electrode (cm2). The real electrochemical area was divided by the geometric area (cm2) to produce a sur-face roughness factor.

3.5. Cyclic Voltammetric Detection of Glucose

The electrocatalytic activity of the sensor towards glucose oxidation was investigated by cyclic voltammetry. The applied potential ranged from −0.6 to 0.8 V at a scan rate of 100 mV s−1. A blank scan and varying glucose concentrations (2, 4 and 6 mM) were recorded by cycling the electrode in 20 mL of 0.1 M PBS.

3.6. Amperometric Detection of Glucose and Interferences

For amperometric detection, the electrode was immersed in a rapidly stirred solution of 0.1 M PBS (20 mL) to provide convective transport and the potential was held at different values from 0.35 to 0.45 V. The linear range was determined by additions of 1 mM glucose at regular intervals. The selectivity of the electrode was determined by an initial addition of 1 mM glucose followed by additions of 0.1 mM interfering species and a final addition of 1 mM glucose. Additions were delivered in increments of 100 s.
Glucose concentrations in serum samples obtained from a local hospital laboratory were determined using the modified electrode by the addition of 0.5 mL of serum to 9.5 mL of 0.1 M PBS. Values found were compared to those recorded in the medical laboratory.

4. Conclusions

Non-enzymatic glucose sensors were successfully fabricated using nanoporous platinum attached to gold screen-printed substrates using a MPTS 2D monolayer. The platinum nanoporous layer was electrochemically deposited by cyclic voltammetry. The modified electrode exhibited good stability and selectivity towards glucose in the presence of interfering compounds commonly found in human blood serum. The sensor also dis-played a wide linear range, fast response time, good reproducibility and excellent reusability. The sensor also provided accurate glucose measurements in human blood serum samples obtained from the local hospital. Nanoporous platinum provided a highly selective glucose sensing platform, while the MPTS self-assembly approach of modification resulted in increased stability and reproducibility. The above attributes of the fabricated sensor may provide a new approach to practical glucose determination in real samples.

Author Contributions

Conceptualization, W.M. and D.M.; methodology, W.M., P.M. and D.M.; validation, W.M., P.M. and D.M.; investigation, W.M. and P.M.; writing—original draft preparation, W.M., P.M. and D.M.; writing—review and editing, W.M., P.M. and D.M.; visualization, W.M.; supervision, D.M., J.D.; project administration, D.M., J.D. All authors have read and agreed to the published version of the manuscript.

Funding

This research received no external funding.

Acknowledgments

The authors acknowledge support from Martin Warren and his technical team, University of Kent, UK, for providing surface characterisation analysis.

Conflicts of Interest

The authors declare no conflict of interest.

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Figure 1. Cyclic voltammogram of the gold electrode in 0.1 M H2SO4 between 0.0 and 1.5 V vs. Ag/AgCl in 0.5 M H2SO4 at a scan rate of 0.1 V s−1.
Figure 1. Cyclic voltammogram of the gold electrode in 0.1 M H2SO4 between 0.0 and 1.5 V vs. Ag/AgCl in 0.5 M H2SO4 at a scan rate of 0.1 V s−1.
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Catalysts 11 01161 sch001 550
Scheme 1. Schematic diagram showing steps involved in the fabrication of the Au-MPTS-Pt.
Scheme 1. Schematic diagram showing steps involved in the fabrication of the Au-MPTS-Pt.
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Figure 2. Cyclic voltammograms of the Au-MPTS-Pt after 100 and 300 platinum deposition cycles. CVs were performed in 0.5 M H2SO4 at a scan rate of 50 mV s−1.
Figure 2. Cyclic voltammograms of the Au-MPTS-Pt after 100 and 300 platinum deposition cycles. CVs were performed in 0.5 M H2SO4 at a scan rate of 50 mV s−1.
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Figure 3. SEM images of the morphology of the electrode surface before (A) and after 300 cycles (B–D): gold surface prior to modification (A), nanoporous platinum surface at ×5k (B), ×20k (C) and ×60.1k magnification (D).
Figure 3. SEM images of the morphology of the electrode surface before (A) and after 300 cycles (B–D): gold surface prior to modification (A), nanoporous platinum surface at ×5k (B), ×20k (C) and ×60.1k magnification (D).
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Figure 4. EDX spectra of the modified electrode surface. Electrode composition after 100 cycles (A). Electrode composition after 300 cycles (B).
Figure 4. EDX spectra of the modified electrode surface. Electrode composition after 100 cycles (A). Electrode composition after 300 cycles (B).
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Figure 5. XPS spectra of the electrode surface after 300 cycles. Survey scan (A); high-resolution scan for platinum 4f (B).
Figure 5. XPS spectra of the electrode surface after 300 cycles. Survey scan (A); high-resolution scan for platinum 4f (B).
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Figure 6. Amperometric responses of the Au-MPTS-Pt to successive additions of 1 mM glucose, 0.1 mM AP, 0.1 mM AA, 0.1 mM UA and 1 mM glucose, respectively, in 0.1 M PBS (pH 7.4) at applied potentials of 0.35 V (blue), 0.40 V (green) and 0.45 V (red).
Figure 6. Amperometric responses of the Au-MPTS-Pt to successive additions of 1 mM glucose, 0.1 mM AP, 0.1 mM AA, 0.1 mM UA and 1 mM glucose, respectively, in 0.1 M PBS (pH 7.4) at applied potentials of 0.35 V (blue), 0.40 V (green) and 0.45 V (red).
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Figure 7. Amperometric response of the Au-MPTS-Pt towards successive additions of 1 mM glucose into a stirring solution of 0.1 M phosphate buffer (pH 7.4) at a constant potential of 0.4 V. Inset: Calibration curve of the Au-MPTS-Pt amperometric response of the glucose concentrations against the corresponding current generated. Sensitivity: 1 to 7 mM and 7 to 18 mM are 191.67 and 135.98 µA mM−1 cm−2, respectively.
Figure 7. Amperometric response of the Au-MPTS-Pt towards successive additions of 1 mM glucose into a stirring solution of 0.1 M phosphate buffer (pH 7.4) at a constant potential of 0.4 V. Inset: Calibration curve of the Au-MPTS-Pt amperometric response of the glucose concentrations against the corresponding current generated. Sensitivity: 1 to 7 mM and 7 to 18 mM are 191.67 and 135.98 µA mM−1 cm−2, respectively.
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Figure 8. Reusability: Amperometric responses of a Au-MPTS-Pt sensor to ten 1 mM glucose samples in 0.1 M PBS at the applied potential of 0.4 V (A). Stability: Amperometric responses of the Au-MPTS-Pt to additions of 1 mM glucose and 0.1 M interferences in 0.1 M PBS at week 1 and week 10 (B). Reproducibility: Amperometric responses of six independently fabricated Au-MPTS-Pt sensors to additions of 1 mM glucose in 0.1 M PBS (C).
Figure 8. Reusability: Amperometric responses of a Au-MPTS-Pt sensor to ten 1 mM glucose samples in 0.1 M PBS at the applied potential of 0.4 V (A). Stability: Amperometric responses of the Au-MPTS-Pt to additions of 1 mM glucose and 0.1 M interferences in 0.1 M PBS at week 1 and week 10 (B). Reproducibility: Amperometric responses of six independently fabricated Au-MPTS-Pt sensors to additions of 1 mM glucose in 0.1 M PBS (C).
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Table
Table 1. Comparison of the performance of different platinum-based glucose sensors.
Table 1. Comparison of the performance of different platinum-based glucose sensors.
Electrode ModificationPotential (V)Linear Range (mM)Sensitivity (µA mM−1 cm−2)Detection Limit (µM)Year and Ref.
PtNPs/CNCs−0.30 [a]0.05–10.0-202017 [31]
Hierarchical Pt micro-/nanostructures+0.45 [a]Up to 3.0473852018 [32]
PtAu/C−0.33 [b]0.01–10-32020 [33]
ZnO-Pt-g-C3N4+0.20 [a]0.25–1103.340.12020 [34]
Pt-CuO/GPE+0.60 [a]Up to 2520350.12020 [35]
PtNi alloy-graphene+0.30 [a]0.5–15.024.03162020 [36]
Pt-Au-graphene/GCE−0.10 [b]1.0–25.026.334.02014 [37]
Pt-CuO/rGO+0.60 [a]0.0005–1235770.012014 [38]
Pt nanoporous+0.40 [a]1.0–10.05.678002017 [26]
Au-MPTS-Pt+0.40 [a]1.0–7.07.0–18.0191.67135.9837This work
[a] vs. Ag/AgCl. [b] vs. SCE.
Table
Table 2. Determination of glucose in human blood serum samples.
Table 2. Determination of glucose in human blood serum samples.
SampleHospital Laboratory (mM)Au/MPTS/Pt (mM)Recovery (%)
15.085.09100.2
27.167.1199.3
33.753.5594.7
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McCormick, W.; McDonagh, P.; Doran, J.; McCrudden, D. Covalent Immobilisation of a Nanoporous Platinum Film onto a Gold Screen-Printed Electrode for Highly Stable and Selective Non-Enzymatic Glucose Sensing. Catalysts 2021, 11, 1161. https://doi.org/10.3390/catal11101161

AMA Style

McCormick W, McDonagh P, Doran J, McCrudden D. Covalent Immobilisation of a Nanoporous Platinum Film onto a Gold Screen-Printed Electrode for Highly Stable and Selective Non-Enzymatic Glucose Sensing. Catalysts. 2021; 11(10):1161. https://doi.org/10.3390/catal11101161

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McCormick, Wesley, Pádraig McDonagh, John Doran, and Denis McCrudden. 2021. "Covalent Immobilisation of a Nanoporous Platinum Film onto a Gold Screen-Printed Electrode for Highly Stable and Selective Non-Enzymatic Glucose Sensing" Catalysts 11, no. 10: 1161. https://doi.org/10.3390/catal11101161

APA Style

McCormick, W., McDonagh, P., Doran, J., & McCrudden, D. (2021). Covalent Immobilisation of a Nanoporous Platinum Film onto a Gold Screen-Printed Electrode for Highly Stable and Selective Non-Enzymatic Glucose Sensing. Catalysts, 11(10), 1161. https://doi.org/10.3390/catal11101161

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