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Article

Flexible Graphene Paper Modified Using Pt&Pd Alloy Nanoparticles Decorated Nanoporous Gold Support for the Electrochemical Sensing of Small Molecular Biomarkers

by
Encheng Sun
1,2,
Zhenqi Gu
1,*,
Haoran Li
1,
Xiao Liu
1,
Yuan Li
1 and
Fei Xiao
3,*
1
Technology Inspection Center of Shengli Oilfield Branch, Sinopec (Shandong) Testing and Evaluation Research Co. Ltd., China Petrochemical Corporation, Dongying 257000, China
2
Sinopec (Shandong) Testing and Evaluation Research Co. Ltd., China Petrochemical Corporation, Dongying 257000, China
3
Key Laboratory of Material Chemistry for Energy Conversion and Storage, Ministry of Education, School of Chemistry and Chemical Engineering, Huazhong University of Science & Technology, Wuhan 430074, China
*
Authors to whom correspondence should be addressed.
Biosensors 2024, 14(4), 172; https://doi.org/10.3390/bios14040172
Submission received: 6 February 2024 / Revised: 27 March 2024 / Accepted: 29 March 2024 / Published: 3 April 2024
(This article belongs to the Special Issue Current Perspectives in Biocatalytic Biosensors)
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Abstract

:
The exploration into nanomaterial-based nonenzymatic biosensors with superb performance in terms of good sensitivity and anti-interference ability in disease marker monitoring has always attained undoubted priority in sensing systems. In this work, we report the design and synthesis of a highly active nanocatalyst, i.e., palladium and platinum nanoparticles (Pt&Pd-NPs) decorated ultrathin nanoporous gold (NPG) film, which is modified on a homemade graphene paper (GP) to develop a high-performance freestanding and flexible nanohybrid electrode. Owing to the structural characteristics the robust GP electrode substrate, and high electrochemically catalytic activities and durability of the permeable NPG support and ultrafine and high-density Pt&Pd-NPs on it, the resultant Pt&Pd-NPs–NPG/GP electrode exhibits excellent sensing performance of low detection limitation, high sensitivity and anti-interference capability, good reproducibility and long-term stability for the detection of small molecular biomarkers hydrogen peroxide (H2O2) and glucose (Glu), and has been applied to the monitoring of H2O2 in different types of live cells and Glu in body fluids such as urine and fingertip blood, which is of great significance for the clinical diagnosis and prognosis in point-of-care testing.

Graphical Abstract

1. Introduction

In the human body, several small molecules such as hydrogen peroxide (H2O2) and glucose, play an important role in metabolic process and can be recognized as biomarkers. For example, H2O2, the most common type of reactive oxygen species (ROS), is a byproduct of various oxidase reactions. In organisms, excessive hydrogen peroxide can damage DNA and other biological molecules, which in turn may induce a variety of diseases such as Alzheimer’s disease, myocardial infarction, Parkinson’s disease, cancer, etc. [1,2]. Therefore, the determination of H2O2 is of practical significance in biological and clinical fields. Meanwhile, the glucose level in blood is a significant biomarker of Diabetes mellitus. In 2019, a total of 463 million people worldwide were diagnosed as diabetic, representing 9.3% of the global adult population. This number is expected to increase to 578 million (10.2%) in 2030 and 700 million (10.9%) in 2045 [3,4]. Therefore, the development of a highly sensitive and selective method for detecting these small molecular biomarkers in real human samples is of great importance in biological and biomedical applications [5,6]. Among the various detection technologies, electrochemical sensors are devices that can detect and measure chemical substances by converting their interaction with electrodes into electrical signals, where chemical reactions between the target substance and the electrodes generate a measurable signal, typically voltage or current [7,8,9]. With the merits of high sensitivity, rapid response times, good long-term stability, ease of miniaturization and cost-effectiveness, electrochemical sensors are highly versatile and applicable in detecting various biomarkers for biomedical monitoring, healthcare, and so on [10,11,12,13].
To date, a variety of nanomaterials have been successfully used to construct electrochemical sensors [14,15,16,17]. Among them, bimetallic nanoparticles (NPs) offer distinct physicochemical properties including high catalytic selectivity, stability and ductility, good tensile strength, and corrosion resistance, which are superior to that of monometallic counterparts [18]. The exceptional catalytic activity of bimetallic systems stems from two primary factors, i.e., the “bifunctional effect” relates to geometric alterations in bimetallic systems versus monometallic ones, and the “ligand or electronic effect” signifies changes in the electronic characteristics of pure metals upon the addition of a second metal component [19]. For example, noble metals such as platinum (Pt) and palladium (Pd) usually exhibit significant catalytic activity for diverse chemical reactions, even at low temperatures [20,21]. While alloys combining Pt (or Pd) demonstrate heightened catalytic effects due to their strong synergistic behavior compared to their monometallic counterparts [22,23,24]. However, the pursuit of suitable supporting materials for achieving efficient electrochemical deposition of alloys remains a formidable challenge. Recently, there has been considerable attention directed toward nanoporous metallic materials that exhibit a distinct continuous network of ligaments with diameters at the nanoscale, showing several unique properties surpassing those of bulk materials [25]. Notably, these nanoporous materials possess a high strength-to-weight ratio, high surface area-to-volume ratio and high ductility during compression [26,27]. Particularly, nanoporous gold (NPG), driven by dealloying processes of gold–silver alloy, showcases an integral morphology with a self-supporting nanostructure [22,23]. It boasts excellent conductivity and a high specific surface area, mitigating issues related to Au-NPs aggregation. Consequently, NPG stands out as an outstanding support material for constructing functionalized layers [28,29,30]. One the other hand, the capability of flexible microelectrode technology can break through the limitations of applicability, miniaturization and spatial resolution, which has made it at the frontier of advancing electrochemical sensors such as implantable and wearable sensor devices for in vivo and in situ real-time detection of various biomarkers in the human body [31]. Given the robust mechanical properties and unique electrical performance of high-surface-area nanocarbon materials, electrocatalysts are commonly supported on these substrates [32]. Significantly, freestanding graphene paper (GP) electrodes demonstrate unique mechanical flexibility, high electrical conductivity, excellent stability, and can facilitate the easy oxidation–reduction of reactants as well [33,34]. Hence, depositing Pd-Pt bimetal on nanoporous gold (NPG) modified graphene paper is a promising strategy for minimizing costs as well as maximizing the electrochemical sensing activity.
Herein, we present a new design and facile synthesis of NPG supported alloy nanocatalysts by employing a straightforward single-step method to deposit minute Pt and Pd alloy nanoparticles (Pt&Pd-NPs) onto ultrathin NPG support (Pt&Pd-NPs–NPG), which is modified onto a GP microelectrode for electrochemical sensing of biomarkers including H2O2 and Glu in real human samples (Figure 1). The synergistic effects between the robust GP electrode substrate, the permeable NPG support, and the deposited ultrafine Pt&Pd-NPs on it give rise to the resultant nanohybrid microelectrode with a large surface area and abundant adsorption sites for target analytes, thus enhancing the electrochemical catalytic activity and the signal-to-noise ratio of miniaturized systems. With an optimal combination of high sensitivity, selectivity, reliability and good biocompatibility, the practical application of the proposed flexible microelectrode was further explored for electrochemical detection of H2O2 in live cells and Glu in human urine and blood samples, which provides important information for biomedical applications, healthcare monitoring, and so on.

2. Experimental

2.1. Preparation of Freestanding GP

Graphene oxide (GO) nanosheets were synthesized using the modified Hummers method. The freestanding and flexible GO paper was prepared using the printing method according to our previous work [35]. In detail, the GO suspension with a high concentration of 5~10 mg mL−1 was dropped onto the substrate of a commercial cellulose paper and rolled back and forth to enable the GO suspension to uniformly cover the paper. After air-drying, a uniform GO layer coated paper was obtained. The freestanding and flexible graphene paper (GP) was prepared by directly immersing the GO coated paper into HI solution at room temperature for 2 h. During this procedure, the GO layer was peeled off from the cellulose paper to form a freestanding GO paper, which was chemically reduced into reduced GO paper at the same time. The as-obtained GP was repeatedly washed with copious ethanol and deionized water and dried at room temperature for 10 h.

2.2. Preparation of Freestanding NPG/GP

Typically, a piece of Au50Ag50 (weight ratio) alloy membrane (1 cm × 1 cm) was carefully placed on a glass slide and immersed in concentrated nitric acid until it was dealloyed for 30 min in concentrated nitric acid in the dark at 30 °C. After that, the as-obtained freestanding and ultrathin NPG membrane was transferred into the deionized water and rinsed by floating three times. The NPG/GP was prepared by transferring the NPG membrane to the homemade GP (1 cm × 1 cm), followed by dropping 10 μL Nafion solution onto the surface of NPG to make it more stable on the GP substrate.

2.3. Preparation of Pt&Pd-NPs–NPG/GP

For the preparation of Pt&Pd-NPs–NPG/GP, chloroplatinic acid hydrate (H2PtCl6), palladium chlorine acid (H2PdCl4) and formic acid (HCOOH) were mixed and dispersed in deionized water at room temperature. The total concentration of H2PtCl6 and H2PdCl4 was 3 × 10−4 M, with a different ratio of H2PtCl6 to H2PdCl4, and the concentration of HCOOH was 5 × 10−3 M. Then, NPG/GP was carefully transferred to the mixed solution. The Pd&Pt-NPs were synthesized and deposited onto NPG/GP using the redox reaction between H2PtCl6, H2PdCl4 and HOOCH at room temperature for 3 h, and washed using deionized water three times. The Pt&Pd–NPG/GP synthesized in precursor solution with the concentration ratios of H2PtCl6 to H2PdCl4 of 3:1, 1:1 and 1:3, were denoted as Pt3Pd1–NPG/GP, Pt1Pd1–NPG/GP and Pt1Pd3–NPG/GP. Meanwhile, Pt–NPG/GP and Pd–NPG/GP were synthesized using the same procedure.

2.4. Cell Culture

Different live cells including human cervical carcinoma cells (Hela cell), Schwann cells (RSC96) and human umbilical vein endothelial cells (HUVEC cell) were seeded at a density of 105 cells/well into 6-well plates and maintained in a culture medium consisting of Dulbecco’s modified Eagle medium (DMEM) at 37 °C and subcultured every 3 days. The cell number was calculated using a cell counter.

2.5. Treatment of Human Body Fluid Samples

The process of obtaining fingertip blood and urine samples for monitoring Glu concentration involves a series of procedural steps. Typically, fingertip blood samples were acquired by cleaning the fingertip area and using a disposable blood lancet or a similar microneedle device to gently puncture the skin surface for blood extraction. For urine samples, participants were required to provide freshly collected urine samples, usually obtained using a urine collection cup. Subsequently, the as-prepared electrochemical sensor was employed to monitor the Glu concentration in these samples (diluted 50-fold in PBS). The sensor induces changes in electrochemical signals in the presence of Glu, indicating variations in the Glu concentration within the samples.

3. Results and Discussion

3.1. Physical Characterization of the Nanohybrid Paper Electrode

Scanning electron microscopy (SEM) was employed to examine the morphology of the freestanding GP. Figure 2A,B reveal that the GP surface exhibits numerous wrinkles, believed to stem from the self-assembly of flexible graphene nanosheets. Notably, SEM images illustrate that the NPG layer deposited on GP comprises interconnected ligaments and numerous nanopore channels, characterized by ligament size ranges of 10~50 nm (Figure 2C). These observations closely corroborate earlier research findings [36]. In-depth analysis of the nanoarchitecture of the NPG membrane was conducted via transmission electron microscopy (TEM), as depicted in Figure 2E. It revealed an ultrathin feature and showcased a characteristic 3D nanoporous arrangement, and its edges were quite smooth, as shown in Figure S1 (Supplementary Materials). For the deposition of Pt&Pd-NPs, the as-obtained NPG support possesses high specific surface area and a controlled effect on the size of Pt&Pd-NPs due to their quantum confinement and edge effects. Figure 2D shows that upon Pt&Pd-NPs deposition, the surface of NPG displays increased roughness. The TEM images of different samples are investigated in detail. It can be observed from Figure S2 that there is an ultra-thin film that entirely covered the surface of NPG for the Pd–NPG sample. As shown in the high-resolution TEM (HR-TEM) image, the film is uniform with a thickness of 2~3 nm. Furthermore, the lattice spacing of 0.235 nm is characteristic of the Au crystalline structure on the NPG support. The interplanar spacing of the film was measured to be 0.222 nm, corresponding to lattice planes of Pd (111). No visible NPs can be seen for Pd–NPG, probably due to the fact that Pd tends to form a dense film rather than NPs on NPG support. Moreover, for Pt1Pd1–NPG/GP, several seriously agglomerated NPs with a coated film can be seen in Figure S3. With the increase in Pt content in Pt3Pd1-NPs, it can be observed that the NPG surface is completely covered by a layer of close-packed and well-distributed NPs, with a uniform size distribution of 3 to 5 nm (Figure 2F,G), which are anticipated to have potential for high electrocatalytic activity in electrochemical biosensing applications. The HR-TEM image of Figure 2H shows the excellent crystallinity of Pt3Pd1-NPs–NPG. The lattice spacing of 0.235 nm is assigned to the NPG support, and the interplanar spacing of Pt3Pd1-NPs lattice fingers is measured to be 0.196 nm and 0.222 nm, corresponding to well-mixed lattice planes of Pt (100) and Pd (111), respectively. Furthermore, the TEM image of Pt–NPG is similar to that of Pt3Pd1-NPs, which also reveal the formation of high-density and well-dispersed NPs on the NPG support (Figure S4).
To determine the chemical composition of Pt3Pd1-NPs–NPG samples, X-ray photoelectron spectroscopy (XPS) analysis was carried out. Figure 3 shows the high-resolution XPS spectra of different element regions. In the Pt 4f spectrum, distinct Pt 4f7/2 and Pt 4f5/2 peaks are observed, exhibiting a difference in binding energy of 3.33 eV. Deconvolution of these peaks reveals two component peaks in Pt 4f7/2 and three in Pt 4f5/2. Specifically, the presence of Pt2+ ions is indicated by the component peak at 72.9 eV in Pt 4f7/2, while the peak at 75.0 eV is attributed to Pt4+ ions. As for the Pd 3d spectrum, primary peaks are identified at 335.4 eV and 340.5 eV, corresponding to Pd 3d5/2 and Pd 3d3/2. Additionally, the Au 4f7/2 and Au 4f5/2 peaks are observed at binding energies of 84.1 eV and 87.7 eV, respectively, originating from the NPG support. Moreover, a comprehensive assessment of the elemental content reveals an atomic ratio of 20.3% Pt, 6.4% Pd, and 73.3% Au for the Pt3Pd1-NPs–NPG composition.

3.2. Electrochemical Characterization of the Nanohybrid Paper Electrode

The cyclic voltammetry (CV) was employed to perform the electrochemical characterization of different modified GP electrodes in a solution of 0.5 M H2SO4, covering a potential range of −0.2~1.4 V. The roughness factor (RF) was calculated using the formula outlined in reference [37]:
R F = A r A g
Herein, Ar denotes actual surface area and Ag represents geometric surface area of the nanostructured electrode. For NPG/GP, Pd–NPG/GP, Pt1Pd3-NPs–NPG/GP, Pt1Pd1-NPs–NPG/GP, Pt3Pd1-NPs–NPG/GP and Pt-NPs–NPG/GP, the Ar values were determined theoretically through the reduction peaks of Au oxide species, a method considered more practical compared to utilizing the hydrogen adsorption/desorption peaks of Pt&Pd due to the involvement of quite higher charges [37,38]. The calculation equation is as follows:
A r = ∫ I d U a · v
The constants a stand at 435 and 400 μQ cm−2 for Pt&Pd-NPs–NPG/GP and NPG/GP, respectively. I and U values are derived from the CV data, with v representing the scan rate during testing. As depicted in Figure S5, the reduction peak potentials for Pt&Pd-NPs–NPG/GP and NPG/GP are aligned closely with the reported values [39,40]. The Ag value of GP is measured to be 0.7 cm2, while the Ar value for NPG/GP reaches 3.7 cm2. Remarkably, the integration of 3D NPG onto GP has notably augmented the electroactive surface area of GP. Additionally, the subsequent incorporation of densely packed NPs onto NPG has maximized the electroactive surface area of the resulting nanohybrid GO electrode to its fullest potential. The Ar value for Pd–NPG/GP, Pt1Pd3-NPs–NPG/GP, Pt1Pd1-NPs–NPG/GP, Pt3Pd1-NPs–NPG/GP and Pt-NPs–NPG/GP is measured to be 25.5, 32.6, 34.7, 29.8 and 44.2 cm2, respectively. Moreover, the calculated RF for Pt3Pd1-NPs–NPG/GP stands at the maximal value of 59.98, which is significantly higher than that of NPG (5.25). This discrepancy suggests that the Pt&Pd-NPs–NPG/GP electrocatalyst exhibits enhanced electrocatalytic activity, particularly in selectively accelerating kinetical reactions. Therefore, Pt3Pd1-NPs–NPG/GP (i.e., Pt&Pd-NPs–NPG/GP) was chosen as the optimal electrocatalyst in the further experiments.
The electrochemical properties of different GP-based electrodes are assessed using electrochemical impedance spectroscopy (EIS). Nyquist plots for GP, NPG/GP and Pt&Pd-NPs–NPG/GP are depicted in Figure S6. The Rct values for GP, NPG/GP and Pt&Pd-NPs–NPG/GP are 109 Ω, 93 Ω and 89 Ω, respectively. Evidently, all freestanding GP-based electrodes exhibit remarkably low resistance and swift charge transfer capabilities. These characteristics underscore their potential utility as flexible microelectrodes in diverse electrochemical sensing systems.

3.3. Electrochemical Sensing Performances of Pt&Pd-NPs–NPG/GP towards H2O2

Since H2O2 is a crucial small molecular biomarker in cancer studies [41,42], and precise quantitative determination of H2O2 in biological and environmental samples holds paramount importance [43,44], in this study we conducted an in-depth investigation into the electrochemical catalytic activity of Pt&Pd-NPs–NPG/GP towards H2O2, with Pt-NPs–NPG/GP and Pd–NPG/GP as the control samples. Figure 4A exhibits the characteristic cyclic voltammetry (CV) curves obtained from different modified GP electrodes when immersed in a testing solution of PBS (0.1 M, pH 7.4) with 20 mM H2O2 under optimal detection conditions. The absence of redox peaks of H2O2 on GP indicates the low electrocatalytic activity of pristine graphene materials towards H2O2. However, upon NPG modification, a distinct reduced peak around ~0 V emerges in the CV curve of NPG/GP, indicating efficient electrocatalytic reduction of H2O2 by robust NPG/GP. Furthermore, the CV curve of Pt&Pd-NPs–NPG/GP exhibits a distinct reduced peak of H2O2, and reduced peak current density significantly increases. Comparatively, the reduced peak of H2O2 on Pt-NPs–NPG/GP is quite abroad, and the peak current density is much lower than that on Pt&Pd-NPs–NPG/GP. Meanwhile, the peak current density of H2O2 on Pd-NPs–NPG/GP is lowest. These results highlight the markedly enhanced electrocatalytic activity of Pt&Pd-NPs–NPG/GP. In this work, the Pt&Pd-NPs–NPG synthesized from the precursor solution with Pt:Pd ratio of 3:1 exhibits high-density and uniform ultra-fine NP structure, rather than the formation of dense film or seriously agglomerated NPs of the control samples. The high-density ultra-fine alloy NPs with well-mixed Pt and Pd atoms can furnish an extensive surface area, abundant active sites, and the synergistic effect between Pt and Pd, which could facilitate the redox reaction of H2O2 on the electrode.
The amperometric technique was employed to assess the electrochemical sensing capabilities of Pt&Pd-NPs–NPG/GP towards H2O2, maintaining a fixed potential of −0.1 V. Figure 4B illustrates the current–time (i-t) curves of Pt&Pd-NPs–NPG/GP upon continuous addition of H2O2 into stirred 0.1 M PBS. The sensing system exhibits rapid response kinetics to H2O2, reaching its maximum steady-state current densities in 2~3 s, demonstrating the rapid absorption, activation and electrochemical reduction of H2O2 on the electrode. The relationship between current densities and H2O2 concentration (Figure 4C) reveals a proportional response within a broad concentration range of 0.1 μM to 26.37 mM, demonstrating high sensitivity of 2.37 mA mM−1 cm−2 and a low detection limit of 0.1 μM at a signal-to-noise ratio of 3. The performances for the detection of H2O2 using different nanomaterial-based electrochemical sensors are shown in Table S1. The results show that the electrochemical sensing performances of Pt&Pd-NPs–NPG/GP are comparable and superior to that of others and even our previous work [45,46,47,48,49,50,51,52,53], indicating that the proposed work possesses significant potential in various areas of biological and biomedical application.
To evaluate the anti-interference ability, the proposed Pt&Pd-NPs–NPG/GP electrode was tested for the detection of H2O2 in the presence of possibly interfering ions commonly found in physiological samples. As depicted in Figure 4D, the amperometric responses of the Pt&Pd-NPs–NPG/GP electrode upon sequential additions of 1.0 mM H2O2 and different ions that commonly existed in human samples were analyzed. Notably, discernible current responses were found exclusively towards H2O2, and negligible corresponding signals were detected for the other tests. The reproducibility and stability of Pt&Pd-NPs–NPG/GP electrode were further evaluated. Ten identically fabricated electrodes show a relative standard deviation (RSD) of 4.25% in response to 1.0 mM H2O2. Twenty consecutive measurements using the same electrode result in an RSD of 2.63%, affirming its robust stability for repeated H2O2 detection. Moreover, the long-term stability investigations reveal that the Pt&Pd-NPs–NPG/GP electrode retains 99.2% and 95.5% of its initial sensitivity after 3 and 30 days, respectively, indicating its high stability.

3.4. Real-Time Electrochemical Detection of H2O2 Secretion by Live Cells

To explore the practical application of the Pt&Pd-NPs–NPG/GP-based biosensor, it was employed to monitor H2O2 released from living cells, where RSC96 cells, HUVEC cells and Hela cells were selected for real-time monitoring of H2O2 after stimulation. Microscopic images captured under both bright-field and dark-field conditions demonstrate that following more than 2 h of incubation with the Pt&Pd-NPs–NPG/GP electrode, these cells exhibited sustained viability, and retained their original morphology (Figure 5A–C), highlighting the satisfactory biocompatibility of the Pt&Pd-NPs–NPG/GP electrode.
Then, H2O2 secretion from living cells at 80% confluency by the administration of N-formyl-methionyl-leucyl-phenylalanine (fMLP), a synthetic peptide known to elicit the secretion of reactive oxygen intermediates [54], was examined. Figure 5D–F shows the amperometric current of the Pt&Pd-NPs–NPG/GP electrode in close proximity to live cells (105 cells/well) within the PBS solution. A remarkable drop in current density was distinct in living cells after the addition of 10 µL of fMLP with concentration of 0.1 mM, subsequently increasing slightly until a plateau was reached. In contrast, there was negligible response upon injection of fMLP without cells (Figure 5G). This suggests the increased responses originated from the H2O2 secretion from stimulated live cells. Further examination of the current responses from these three cell types yielded intriguing insights. Following equivalent fMLP additions, the amperometric current densities increased by 29 µA cm−2 for Hela cells, 11 µA cm−2 for HUVEC cells and 51 µA cm−2 for RSC96 cells (Figure 5H,I). In addition, the amperometric current response for Hela cells reached the plateau the fastest, followed by RSC96 cells and HUVEC cells (Figure 5I). These findings illustrate the high sensitivity of the proposed method in qualitatively determining H2O2 released from diverse live cells, which holds great promise for further exploration in clinical diagnosis.

3.5. Electrochemical Sensing Performances of Pt&Pd-NPs–NPG/GP towards Glucose

Diabetes mellitus presents a global public health challenge attributed to metabolic imbalances involving insulin deficiency and hyperglycemia. Deviations in glucose (Glu) concentration beyond the normal range of 4.4~6.6 mM are indicative of this disorder [55]. Therefore, the development of high-performance Glu sensors holds significant importance for diagnosing diabetes mellitus. The electrocatalytic capabilities of Pt&Pd-NPs–NPG/GP have been leveraged for nonenzymatic Glu biosensing, aiming to circumvent the limitations associated with enzymatic Glu sensors, notably insufficient long-term stability and unsatisfactory reproducibility arising from enzyme nature and immobilization activity [56]. CV curves of Pt&Pd-NPs–NPG/GP with different Glu concentrations in testing solution were examined (Figure 6A). Remarkably, distinct anodic peaks related to Glu oxidation and its intermediates are prominently discerned during the positive scan. Conversely, during the cathodic scan at elevated potential ranges, Glu oxidation is hindered by the presence of surface oxides. The reduction of Pt oxide has augmented the active sites accessible for Glu oxidation, leading to a substantial increase in oxidation peak current densities. These findings are consistent with an established mechanism of Glu oxidation on Pt-based electrodes [57]. The redox currents notably escalate with increasing Glu concentration for Pt&Pd-NPs–NPG/GP. In contrast, the CV curves of NPG/GP and GP display nearly absent redox peaks in testing solution containing 10 mM Glu, highlighting the improved electrocatalytic activity attributed to Pt&Pd-NPs on the electrode. Furthermore, the CV curves of 10 mM Glu on Pt-NPs–NPG/GP and Pd–NPG/GP demonstrate the same oxidation peaks of Glu and reduction peaks of Pt/Pd oxide, however, the peak current densities are much lower than that of Pt&Pd-NPs–NPG/GP (Figure S7). This is also due to the significant high surface to volume ratio, abundant active sites and the synergistic effect of alloy NPs, which facilitate the oxidation reaction of Glu on the electrode.
Figure 6B exhibits the i-t curve of the Pt&Pd-NPs–NPG/GP electrode upon successive injections of Glu into a PBS solution, while maintaining an applied potential of −0.3 V. The amperometric current response rapidly reaches 95% of its steady-state value within 2~3 s upon each Glu addition. Additionally, a notable linear relationship within the Glu concentration range of 0.1~20.0 mM is achieved, with a high sensitivity of 39.05 μA mM−1 cm−2 and a detection limit as low as 50 μM (S/N = 3), which are comparable and superior to that of other recently published works including our group’s [58,59,60,61,62,63,64,65,66] (Table S2). Investigations into the potential interference from electroactive compounds commonly found in biological systems, such as dopamine (DA), uric acid (UA), ascorbic acid (AA), cholesterol (Cho) and lactic acid (LA), reveal no interference with the amperometric signals of Glu (Figure S8). The current density changes upon the addition of equal concentrations of these compounds alongside 1.0 mM Glu remain below 5%. This excellent anti-interference performance can be attributed to the low reduction potential of −0.3 V vs. SCE, which inhibits the redox reactions of interfering substances on Pt&Pd-NPs–NPG/GP. Such characteristics render it suitable for sensitive and selective Glu detection in various human body fluid samples.

3.6. Electrochemical Detection of Glu in Different Human Body Fluid Samples

Body fluid examination serves as a pivotal tool for diagnosing ailments and monitoring overall health. This type of assessment typically encompasses analyzing blood, urine, cerebrospinal fluid, synovial fluid and other bodily fluids. Through scrutinizing these liquids, clinicians acquire a wealth of information regarding a patient’s health status. For instance, blood tests offer insights into blood cell counts, inflammatory markers, nutritional levels, and indications of various potential diseases. Urine analysis aids in diagnosing renal issues, diabetes and other metabolic concerns. The examination of cerebrospinal fluid assists in detecting neurological disorders, while synovial fluid evaluation aids in diagnosing conditions like arthritis. To illustrate the applicability of the proposed sensor, it has been utilized for Glu detection in other complex biological samples, i.e., fingertip blood and urine. The results are presented in Table 1, which is highly consistent with those obtained using the clinical measurement method. The recoveries of spiked samples fall within the range of 90–109.0%, indicating the high reliability and efficacy of the proposed nonenzymatic electrochemical biosensor based on the Pt&Pd-NPs–NPG/GP electrode. This demonstrates its potential for effectively monitoring various analytes simultaneously in trace amounts within real biological samples.

4. Conclusions

In summary, we developed a novel approach for synthesizing alloy nanocatalysts supported by NPG. Our method involved a facile single-step procedure for depositing minute Pd&Pt-NPs onto an ultrathin NPG support, which was then modified onto a freestanding and flexible GP microelectrode. The resulting nanohybrid microelectrode, leveraging the synergistic effects between different components, demonstrates outstanding electrocatalytic activity and favorable biocompatibility, and has been integrated into electrochemical sensors for sensitive and reliable detection of H2O2 in living cells and Glu in human body fluids. We envision that our proposed strategy in the design of highly active noble metal nanocatalysts and flexible graphene paper electrodes opens a new horizon in the development of high-performance and advanced electrochemical sensing systems, which holds great promise for a wide spectrum of applications in biomedical domains, healthcare monitoring and related fields.

Supplementary Materials

The following supporting information can be downloaded at https://www.mdpi.com/article/10.3390/bios14040172/s1, Figure S1: TEM images of NPG; Figure S2: TEM images of Pd film on NPG support; Figure S3: TEM images of Pt1Pd3 on NPG support; Figure S4: TEM image of Pt-NPs on NPG support; Figure S5: CV curves of Pt-NPs-NPG/GP, Pt3Pd1-NPs-NPG/GP, Pt1Pd1-NPs-NPG/GP, Pt1Pd3-NPs-NPG/GP and NPG/GP electrodes in 0.5 M H2SO4 solution. Scan rate: 50 mV s−1; Figure S6: EIS Nyquist plots of Pt&Pd-NPs-NPG/GP (a), NPG/GP (b) and GP (c) at open circuit potential with an ac perturbation of 5 mV in the frequency range of 1000 kHz to 0.01 Hz. Inset: equivalent circuit diagram proposed for analysis of the EIS data; Figure S7: CV curves of Pd-NPG/GP, Pt-NPs-NPG/GP and Pt&Pd-NPs-NPG/GP in 0.1 M PBS (pH 7.4) in the presence of 50 mM Glu; Figure S8: Amperometric responses to the consecutive addition of 1 mM Glu and 1 mM interfering species in a stirred PBS solution (0.1 M, pH 7.4); Table S1: Comparison of the performances for the detection of H2O2 by different nanomaterials-based electrochemical sensors; Table S2: Comparison of the performances for the detection of Glu by different nanomaterials-based electrochemical sensors [49,50,51,52,53,54,55,56,57,58,59,60,61,62,63,64,65,66].

Author Contributions

E.S.: Methodology, Investigation, Writing—original draft, Project administration. Z.G.: Methodology, Validation, Formal analysis, Writing—review & editing. H.L.: Investigation, Data curation, Formal analysis. X.L.: Conceptualization, Resources. Y.L.: Resources, Methodology. F.X.: Conceptualization, Supervision, Project administration, Funding acquisition. All authors have read and agreed to the published version of the manuscript.

Funding

This research was funded by the National Key Research and Development Program of China (Grant No. 2022YFC2408100), Natural Science Foundation of Hubei Province, China (Grant No. 2022CFA031), National Natural Science Foundation of China (Grant No. 21874051 and 51772110).

Institutional Review Board Statement

The study was conducted in accordance with the Declaration of Helsinki, and approved by the Ethics Committee of Tongji Medical College, Huazhong University of Science and Technology (protocol code [2013] IEC (A152) and date of approval is 2 March 2023).

Informed Consent Statement

Informed consent was obtained from subjects involved.

Data Availability Statement

The data presented in this study are available on request from the corresponding author.

Conflicts of Interest

Author Encheng Sun, Zhenqi Gu, Haoran Li, Xiao Liu and Yuan Li were employed by Technology Inspection Center of Shengli Oilfield Branch, China Petrochemical Corporation. Author Encheng Sun was also employed by Sinopec (Shandong) Testing and Evaluation Research Co. Ltd, China Petrochemical Corporation. The remaining authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest’ in the proof.

References

  1. Lennicke, C.; Cocheme, H.M. Redox metabolism: ROS as specific molecular regulators of cell signaling and function. Mol. Cell 2021, 81, 3691–3707. [Google Scholar] [CrossRef]
  2. Sies, H.; Belousov, V.V.; Chandel, N.S.; Davies, M.J.; Jones, D.P.; Mann, G.E.; Murphy, M.P.; Yamamoto, M.; Winterbourn, C. Defining roles of specific reactive oxygen species (ROS) in cell biology and physiology. Nat. Rev. Mol. Cell Biol. 2022, 23, 499–515. [Google Scholar] [CrossRef]
  3. Xiao, J.; Liu, Y.; Su, L.; Zhao, D.; Zhao, L.; Zhang, X. Microfluidic chip-based wearable colorimetric sensor for simple and facile detection of sweat glucose. Anal. Chem. 2019, 91, 14803–14807. [Google Scholar] [CrossRef]
  4. Lipani, L.; Dupont, B.G.R.; Doungmene, F.; Marken, F.; Tyrrell, R.M.; Guy, R.H.; Ilie, A. Non-invasive, transdermal, path-selective and specific glucose monitoring via a graphene-based platform. Nat. Nanotechnol. 2018, 13, 504–511. [Google Scholar] [CrossRef]
  5. Wu, J.; Liu, H.; Chen, W.; Ma, B.; Ju, H. Device integration of electrochemical biosensors. Nat. Biomed. Eng. 2023, 1, 346–360. [Google Scholar] [CrossRef]
  6. Li, D.; Xiong, Q.; Liu, W.; Liang, L.; Duan, H. Nanozymatic magnetic nanomixers for enzyme immobilization and multiplexed detection of metabolic disease biomarkers. Biosens. Bioelectron. 2023, 219, 114795. [Google Scholar] [CrossRef]
  7. Saha, T.; Del Caño, R.; Mahato, K.; De la Paz, E.; Chen, C.; Ding, S.; Yin, L.; Wang, J. Wearable electrochemical glucose sensors in diabetes management: A comprehensive review. Chem. Rev. 2023, 123, 7854–7889. [Google Scholar] [CrossRef]
  8. Li, S.; Zhang, H.; Zhu, M.; Kuang, Z.; Li, X.; Xu, F.; Miao, S.; Zhang, Z.; Lou, X.; Li, H.; et al. Electrochemical biosensors for whole blood analysis: Recent progress, challenges, and future perspectives. Chem. Rev. 2023, 123, 7953–8039. [Google Scholar] [CrossRef]
  9. Liu, Y.L.; Huang, W.H. Stretchable electrochemical sensors for cell and tissue detection. Angew. Chem. Int. Ed. 2020, 60, 2757–2767. [Google Scholar] [CrossRef]
  10. Zhang, R.Z.; Chen, W. Recent advances in graphene-based nanomaterials for fabricating electrochemical hydrogen peroxide sensors. Biosens. Bioelectron. 2017, 89, 249–268. [Google Scholar] [CrossRef]
  11. Sempionatto, J.R.; Lasalde-Ramírez, J.A.; Mahato, K.; Wang, J.; Gao, W. Wearable chemical sensors for biomarker discovery in the omics era. Nat. Rev. Chem. 2022, 6, 899–915. [Google Scholar] [CrossRef]
  12. Teymourian, H.; Barfidokht, A.; Wang, J. Electrochemical glucose sensors in diabetes management: An updated review (2010–2020). Chem. Soc. Rev. 2020, 49, 7671–7709. [Google Scholar] [CrossRef]
  13. Wongkaew, N.; Simsek, M.; Griesche, C.; Baeumner, A.J. Functional nanomaterials and nanostructures enhancing electrochemical biosensors and lab-on-chip perperformances: Recent progress, applications, and future perspective. Chem. Rev. 2019, 119, 120–194. [Google Scholar] [CrossRef]
  14. Amali, R.K.A.; Lim, H.N.; Ibrahim, I.; Huang, N.M.; Zainal, Z.; Ahmad, S.A.A. Significance of nanomaterials in electrochemical sensors for nitrate detection: A review. Trends Environ. Anal. Chem. 2021, 31, e00135. [Google Scholar] [CrossRef]
  15. Gupta, R.; Raza, N.; Bhardwaj, S.K.; Vikrant, K.; Kim, K.-H.; Bhardwaj, N. Advances in nanomaterial-based electrochemical biosensors for the detection of microbial toxins, pathogenic bacteria in food matrices. J. Hazard. Mater. 2021, 401, 123379. [Google Scholar] [CrossRef] [PubMed]
  16. Qian, L.; Durairaj, S.; Prins, S.; Chen, A. Nanomaterial-based electrochemical sensors and biosensors for the detection of pharmaceutical compounds. Biosens. Bioelectron. 2021, 175, 112836. [Google Scholar] [CrossRef]
  17. Dong, T.; Matos Pires, N.M.; Yang, Z.; Jiang, Z. Advances in electrochemical biosensors based on nanomaterials for protein biomarker detection in saliva. Adv. Sci. 2022, 10, 2205429. [Google Scholar] [CrossRef]
  18. Baig, N.; Sajid, M.; Saleh, T.A. Recent trends in nanomaterial-modified electrodes for electroanalytical applications. TrAC Trends Anal. Chem. 2019, 111, 47–61. [Google Scholar] [CrossRef]
  19. Sun, Y.; Xue, Z.; Liu, Q.; Jia, Y.; Li, Y.; Liu, K.; Lin, Y.; Liu, M.; Li, G.; Su, C.Y. Modulating electronic structure of metal-organic frameworks by introducing atomically dispersed Ru for efficient hydrogen evolution. Nat. Commun. 2021, 12, 1369. [Google Scholar] [CrossRef]
  20. Yi, J.; Xianyu, Y. Gold nanomaterials-implemented wearable sensors for healthcare applications. Adv. Funct. Mater. 2022, 32, 2113012. [Google Scholar] [CrossRef]
  21. Xu, Y.; Zhang, B. Recent advances in porous Pt-based nanostructures: Synthesis and electrochemical applications. Chem. Soc. Rev. 2014, 43, 2439–2450. [Google Scholar] [CrossRef] [PubMed]
  22. Sun, Y.; Zheng, H.; Wang, C.; Yang, M.; Zhou, A.; Duan, H. Ultrasonic-electrodeposition of PtPd alloy nanoparticles on ionic liquid-functionalized graphene paper: Towards a flexible and versatile nanohybrid electrode. Nanoscale 2016, 8, 1523–1534. [Google Scholar] [CrossRef] [PubMed]
  23. Liu, W.; Hiekel, K.; Hübner, R.; Sun, H.J.; Ferancova, A.; Sillanpää, M. Pt and Au bimetallic and monometallic nanostructured amperometric sensors for direct detection of hydrogen peroxide: Influences of bimetallic effect and silica support. Sens. Actuators B Chem. 2018, 255, 1325–1334. [Google Scholar] [CrossRef]
  24. Wang, T.; Wu, Y.; She, J.; Xu, Y.; Zhang, Y.; Zhao, A.; Manoj, D.; Xi, J.; Sun, Y.; Ren, J.; et al. 3D nitrogen-doped carbon nanofoam arrays embedded with PdCu alloy nanoparticles: Assembling on flexible microelectrode for electrochemical detection in cancer cells. Anal. Chim. Acta 2021, 1158, 338420. [Google Scholar] [CrossRef] [PubMed]
  25. Wang, Y.; Huang, W.; Si, C.; Zhang, J.; Yan, X.; Jin, C.; Ding, Y.; Zhang, Z. Self-supporting nanoporous gold-palladium overlayer bifunctional catalysts toward oxygen reduction and evolution reactions. Nano Res. 2016, 9, 3781–3794. [Google Scholar] [CrossRef]
  26. Li, X.; Zhu, L.; Kasuga, T.; Nogi, M.; Koga, H. All-nanochitin-derived, super-compressible, elastic, and robust carbon honeycombs and their pressure-sensing properties over an ultrawide temperature range. ACS Appl. Mater. Interfaces 2023, 15, 41732–41742. [Google Scholar] [CrossRef] [PubMed]
  27. Li, X.; Zhu, L.; Kasuga, T.; Nogi, M.; Koga, H. Frequency-tunable and absorption/transmission-switchable microwave absorber based on a chitin-nanofiber-derived elastic carbon aerogel. Chem. Eng. J. 2023, 469, 144010. [Google Scholar] [CrossRef]
  28. Luc, W.; Jiao, F. Nanoporous metals as electrocatalysts: State-of-the-art, opportunities, and challenges. ACS Catal. 2017, 7, 5856–5861. [Google Scholar] [CrossRef]
  29. Jiang, J.Z.; Ren, L.Q.; Huang, Y.P.; Li, X.D.; Wu, S.H.; Sun, J.J. 3D nanoporous gold-supported Pt nanoparticles as highly accelerating catalytic Au-Pt micromotors. Adv. Mater. Interfaces 2018, 5, 1701689. [Google Scholar] [CrossRef]
  30. Chen, Q. Bicontinuous nanoporous metals with self-organized functionalities. Chem. Mater. 2022, 34, 10237–10248. [Google Scholar] [CrossRef]
  31. Flores-Hernandez, D.R.; Santamaria-Garcia, V.J.; Melchor-Martinez, E.M.; Sosa-Hernandez, J.E.S.; Parra-Saldivar, R.; Bonilla-Rios, J. Paper and other fibrous materials—A complete platform for biosensing applications. Biosensors 2021, 11, 128. [Google Scholar] [CrossRef] [PubMed]
  32. Lin, T.; Xu, Y.; Zhao, A.; He, W.; Xiao, F. Flexible electrochemical sensors integrated with nanomaterials for in situ determination of small molecules in biological samples: A review. Anal. Chim. Acta 2022, 1207, 339461. [Google Scholar] [CrossRef] [PubMed]
  33. Kongkaew, S.; Meng, L.; Limbut, W.; Liu, G.; Kanatharana, P.; Thavarungkul, P.; Mak, W.C. Craft-and-stick xurographic manufacturing of integrated microfluidic electrochemical sensing platform. Biosensors 2023, 13, 446. [Google Scholar] [CrossRef] [PubMed]
  34. Poletti, F.; Scidà, A.; Zanfrognini, B.; Kovtun, A.; Parkula, V.; Favaretto, L.; Melucci, M.; Palermo, V.; Treossi, E.; Zanardi, C. Graphene-paper-based electrodes on plastic and textile supports as new platforms for amperometric biosensing. Adv. Funct. Mater. 2021, 32, 2107941. [Google Scholar] [CrossRef]
  35. Xiao, F.; Yang, S.; Zhang, Z.; Liu, H.; Xiao, J.; Wan, L.; Luo, J.; Wang, S.; Liu, Y. Scalable synthesis of freestanding sandwich-structured graphene/polyaniline/ graphene nanocomposite paper for flexible all-solid-state supercapacitor. Sci. Rep. 2015, 9, 9359. [Google Scholar] [CrossRef] [PubMed]
  36. Koenig, M.; Simon, F.; Formanek, P.; Müller, M.; Gupta, S.; Stamm, M.; Uhlmann, P. Catalytically active nanocomposites based on palladium and platinum nanoparticles in poly(2-vinylpyridine) brushes. Macromol. Chem. Phys. 2013, 214, 2301–2311. [Google Scholar] [CrossRef]
  37. Park, I.S.; Lee, K.S.; Jung, D.S.; Park, H.Y.; Sung, Y.E. Electrocatalytic activity of carbon-supported Pt–Au nanoparticles for methanol electro-oxidation. Electrochim. Acta 2007, 52, 5599–5605. [Google Scholar] [CrossRef]
  38. Friedrich, K.A.; Henglein, F.; Stimming, U.; Unkauf, W. Investigation of Pt particles on gold substrates by IR spectroscopy particle structure and catalytic activity. Colloid. Surface A Physicochem. Eng. Asp. 1998, 134, 193–206. [Google Scholar] [CrossRef]
  39. Jaramillo, T.F.; Baeck, S.H.; Cuenya, B.R.; McFarland, E.W. Catalytic activity of supported Au nanoparticles deposited from block copolymer micelles. J. Am. Chem. Soc. 2003, 125, 7148–7149. [Google Scholar] [CrossRef] [PubMed]
  40. Oesch, U.; Janata, J. Electrochemical study of gold electrodes with anodic oxide films-I. Formation and reduction behavior of anodic oxides on gold. Electrochim. Acta 1983, 28, 1237–1246. [Google Scholar] [CrossRef]
  41. Dietz, K.-J.; Vogelsang, L. H2O2 sensing in immunity. Nat. Plants 2022, 8, 1140–1141. [Google Scholar] [CrossRef]
  42. Lin, L.-S.; Huang, T.; Song, J.; Ou, X.-Y.; Wang, Z.; Deng, H.; Tian, R.; Liu, Y.; Wang, J.-F.; Liu, Y.; et al. Synthesis of copper peroxide nanodots for H2O2 self-supplying chemodynamic therapy. J. Am. Chem. Soc. 2019, 141, 9937–9945. [Google Scholar] [CrossRef] [PubMed]
  43. Ma, T.; Ye, J.; Tang, Y.; Yuan, H.; Wen, D. Superhydrophilicity regulation of carbon nanotubes boosting electrochemical biosensing for real-time monitoring of H2O2 released from living cells. Anal. Chem. 2023, 95, 17851–17859. [Google Scholar] [CrossRef] [PubMed]
  44. Huang, W.; Xu, Y.; Wang, Z.; Liao, K.; Zhang, Y.; Sun, Y. Dual nanozyme based on ultrathin 2D conductive MOF nanosheets intergraded with gold nanoparticles for electrochemical biosensing of H2O2 in cancer cells. Talanta 2022, 249, 123612. [Google Scholar] [CrossRef] [PubMed]
  45. Chen, X.; Dong, J.; Chi, K.; Wang, L.; Xiao, F.; Wang, S.; Zhao, Y.; Liu, Y. Electrically conductive metal–organic framework thin film-based on-chip micro-biosensor: A platform to unravel surface morphology-dependent biosensing. Adv. Funct. Mater. 2021, 31, 2102855. [Google Scholar] [CrossRef]
  46. Daemi, S.; Ghasemi, S.; Akbar Ashkarran, A. Electrospun CuO-ZnO nanohybrid: Tuning the nanostructure for improved amperometric detection of hydrogen peroxide as a non-enzymatic sensor. J. Colloid Interface Sci. 2019, 550, 180–189. [Google Scholar] [CrossRef] [PubMed]
  47. Sun, Y.; Dong, X.; He, H.; Zhang, Y.; Chi, K.; Xu, Y.; Asif, M.; Yang, X.; He, W.; Liao, K.; et al. 2D carbon network arranged into high-order 3D nanotube arrays on a flexible microelectrode: Integration into electrochemical microbiosensor devices for cancer detection. NPG Asia Mater. 2023, 15, 6. [Google Scholar] [CrossRef]
  48. Li, J.; Shen, C.; Luo, J.; Pan, T.; Deng, J.; Cao, Z. Metal-organic framework-derived brain platygyra coral-like porous carbon architectures for real-time monitoring of hydrogen peroxide in biological matrices. Chem. Eng. J. 2023, 471, 144805. [Google Scholar] [CrossRef]
  49. Han, N.; Hua, S.Y.; Zhang, L.Y.; Yi, S.S.; Zhang, Z.T.; Wang, Y.; Zhou, Y.; Chen, D.L.; Gao, Y.F. CuCo-Cu@CoCH stamen-like nanoarray prepared by co-reduction for electrochemical detection of hydrogen peroxide. Appl. Surf. Sci. 2022, 576, 151879. [Google Scholar] [CrossRef]
  50. Patella, B.; Buscetta, M.; Di Vincenzo, S.; Ferraro, M.; Aiello, G.; Sunseri, C.; Pace, E.; Inguanta, R.; Cipollina, C. Electrochemical sensor based on rGO/Au nanoparticles for monitoring H2O2 released by human macrophages. Sens. Actuators B Chem. 2021, 327, 128901. [Google Scholar] [CrossRef]
  51. Wang, Q.; Zhang, X.; Chai, X.; Wang, T.; Cao, T.; Li, Y.; Zhang, L.; Fan, F.; Fu, Y.; Qi, W. An electrochemical sensor for H2O2 based on Au nanoparticles embedded in UiO-66 metal–organic framework films. ACS Appl. Nano Mater. 2021, 4, 6103–6110. [Google Scholar]
  52. He, G.; Gao, F.; Li, W.; Li, P.; Zhang, X.; Yin, H.; Yang, B.; Liu, Y.; Zhang, S. Electrochemical sensing of H2O2 released from living cells based on AuPd alloy-modified PDA nanotubes, Anal. Methods 2019, 11, 1651–1656. [Google Scholar]
  53. Xiao, F.; Song, J.; Gao, H.; Zan, X.; Xu, R.; Duan, H. Coating graphene paper with 2D-assembly of electrocatalytic nanoparticles: A modular approach toward high-performance flexible electrodes. ACS Nano 2012, 6, 100–110. [Google Scholar] [CrossRef] [PubMed]
  54. Rojas, D.; Hernández-Rodríguez, J.F.; Della Pelle, F.; Del Carlo, M.; Compagnone, D.; Escarpa, A. Oxidative stress on-chip: Prussian blue-based electrode array for in situ detection of H2O2 from cell populations. Biosens. Bioelectron. 2020, 170, 112669. [Google Scholar] [CrossRef] [PubMed]
  55. DeJournett, J.; Nekludov, M.; DeJournett, L.; Wallin, M. Performance of a closed-loop glucose control system, comprising a continuous glucose monitoring system and an AI-based controller in swine during severe hypo- and hyperglycemic provocations. J. Clin. Monit. Comput. 2021, 35, 317–325. [Google Scholar] [CrossRef] [PubMed]
  56. Zhu, X.; Ju, Y.; Chen, J.; Liu, D.; Liu, H. Nonenzymatic wearable sensor for electrochemical analysis of perspiration glucose. ACS Sens. 2018, 3, 1135–1141. [Google Scholar] [CrossRef] [PubMed]
  57. Habrioux, A.; Sibert, E.; Servat, K.; Vogel, W.; Kokoh, K.B.; Alonso, V.N. Activity of platinum–gold alloys for glucose electrooxidation in biofuel cells. J. Phys. Chem. B. 2007, 111, 10329–10333. [Google Scholar] [CrossRef] [PubMed]
  58. Yue, X.; Feng, J.; Li, H.; Xiao, Z.; Qiu, Y.; Yu, X.; Xiang, J. Novel synthesis of carbon nanofiber aerogels from coconut matrix for the electrochemical detection of glucose. Diam. Relat. Mater. 2021, 111, 108180. [Google Scholar] [CrossRef]
  59. Long, M.; Tan, L.; Liu, H.; He, Z.; Tang, A. Novel helical TiO2 nanotube arrays modified by Cu2O for enzyme-free glucose oxidation. Biosens. Bioelectron. 2014, 59, 243–250. [Google Scholar] [CrossRef]
  60. Wang, L.; Fu, J.; Song, Y. A facile strategy to prepare Cu2O/Cu electrode as a sensitive enzyme-free glucose sensor. Int. J. Electrochem. Sci. 2012, 7, 12587–12600. [Google Scholar] [CrossRef]
  61. Belkhalfa, H.; Teodorescu, F.; Quéniat, G.; Co nier, Y.; Dokhan, N.; Sam, S.; Abderrahmani, A.; Boukherroub, R.; Szunerits, S. Insulin impregnated reduced graphene oxide/Ni(OH)2 thin films for electrochemical insulin release and glucose sensing. Sens. Actuat. B-Chem. 2016, 237, 693–701. [Google Scholar] [CrossRef]
  62. Kim, Y.J.; Chinnadayyala, S.R.; Le, H.T.N.; Cho, S. Sensitive electrochemical non-Enzymatic detection of glucose based on wireless data transmission. Sensors 2022, 22, 2787. [Google Scholar] [CrossRef] [PubMed]
  63. Chung, R.J.; Wang, A.N.; Liao, Q.L.; Chuang, K.-Y. Non-enzymatic glucose sensor composed of carbon-coated nano-zinc oxide. Nanomaterials 2017, 7, 36. [Google Scholar] [CrossRef] [PubMed]
  64. Ye, J.S.; Liu, Z.T.; Lai, C.C.; Lo, C.T.; Lee, C.L. Diameter effect of electrospun carbon fiber support for the catalysis of Pt nanoparticles in glucose oxidation. Chem. Eng. J. 2016, 283, 304–312. [Google Scholar] [CrossRef]
  65. Chen, K.J.; Lee, C.F.; Rick, J.; Wang, S.-H.; Liu, C.C.; Hwang, B.J. Fabrication and application of amperometric glucose biosensor based on a novel PtPd bimetallic nanoparticle decorated multi-walled carbon nanotube catalyst. Biosens. Bioelectron. 2012, 33, 75–81. [Google Scholar] [CrossRef]
  66. Xiao, F.; Li, Y.; Gao, H.; Ge, S.; Duan, H. Growth of coral-like PtAu-MnO2 binary nanocomposites on free-standing graphene paper for flexible nonenzymatic glucose sensors. Biosens. Bioelectron. 2013, 41, 417–423. [Google Scholar] [CrossRef]
Biosensors 14 00172 g001
Figure 1. Schematic of the fabrication process of flexible Pt&Pd-NPs–NPG/GP electrodes for electrochemical biosensors towards H2O2 and Glu.
Figure 1. Schematic of the fabrication process of flexible Pt&Pd-NPs–NPG/GP electrodes for electrochemical biosensors towards H2O2 and Glu.
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Figure 2. SEM images of (A,B) GP, (C) NPG/GP and (D) Pt3Pd1-NPs–NPG/GP with different magnifications. TEM images of (E) NPG and (F,G) Pt3Pd1-NPs–NPG with different magnifications. (H) HRTEM image of Pt3Pd1–NPG illustrates the lattice spacings of each element.
Figure 2. SEM images of (A,B) GP, (C) NPG/GP and (D) Pt3Pd1-NPs–NPG/GP with different magnifications. TEM images of (E) NPG and (F,G) Pt3Pd1-NPs–NPG with different magnifications. (H) HRTEM image of Pt3Pd1–NPG illustrates the lattice spacings of each element.
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Figure 3. XPS spectra of (A) Pt 4f, (B) Pd 3d and (C) Au 4f of Pt3Pd1-NPs–NPG/GP.
Figure 3. XPS spectra of (A) Pt 4f, (B) Pd 3d and (C) Au 4f of Pt3Pd1-NPs–NPG/GP.
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Figure 4. (A) CV curves of NPG/GP, Pt-NPs–NPG/GP, Pd-NPs–NPG/GP and Pt&Pd-NPs–NPG/GP in a testing solution of 20 mM H2O2. Scan rate: 50 mV s−1. (B) Amperometric responses of Pt&Pd-NPs–NPG/GP to sequential injection of different concentrations of H2O2 in a stirred PBS solution. Applied potential: −0.1 V. (C) Calibration curves of the linear relationship between the current densities and H2O2 concentrations. (D) Amperometric responses to the sequential injection of equal H2O2 and interference ions.
Figure 4. (A) CV curves of NPG/GP, Pt-NPs–NPG/GP, Pd-NPs–NPG/GP and Pt&Pd-NPs–NPG/GP in a testing solution of 20 mM H2O2. Scan rate: 50 mV s−1. (B) Amperometric responses of Pt&Pd-NPs–NPG/GP to sequential injection of different concentrations of H2O2 in a stirred PBS solution. Applied potential: −0.1 V. (C) Calibration curves of the linear relationship between the current densities and H2O2 concentrations. (D) Amperometric responses to the sequential injection of equal H2O2 and interference ions.
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Figure 5. (A–C) Dark-field and bright-field (inset) images of different cells. (D–F) Amperometric current responses of the Pt&Pd-NPs–NPG/GP electrode located near different cells under stimulation and (G) without cells in PBS solution. Histogram of (H) the increased amperometric current densities and (I) time to reach the plateau for three types of living cells.
Figure 5. (A–C) Dark-field and bright-field (inset) images of different cells. (D–F) Amperometric current responses of the Pt&Pd-NPs–NPG/GP electrode located near different cells under stimulation and (G) without cells in PBS solution. Histogram of (H) the increased amperometric current densities and (I) time to reach the plateau for three types of living cells.
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Figure 6. (A) CV curves of Pt&Pd-NPs–NPG/GP electrodes for various concentrations of Glu in PBS solution with a scan rate of 50 mV s−1. Inset: CV curves of Pt&Pd-NPs–NPG/GP and bare NPG/GP electrodes in a solution of 10 mM Glu. (B) i-t curve of Pt&Pd-NPs–NPG/GP electrodes for successive additions of different concentrations of Glu.
Figure 6. (A) CV curves of Pt&Pd-NPs–NPG/GP electrodes for various concentrations of Glu in PBS solution with a scan rate of 50 mV s−1. Inset: CV curves of Pt&Pd-NPs–NPG/GP and bare NPG/GP electrodes in a solution of 10 mM Glu. (B) i-t curve of Pt&Pd-NPs–NPG/GP electrodes for successive additions of different concentrations of Glu.
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Table 1. Results of the Pt&Pd-NPs–NPG/GP-based electrochemical sensing system for the detection of Glu in different human urine and fingertip blood samples.
Table 1. Results of the Pt&Pd-NPs–NPG/GP-based electrochemical sensing system for the detection of Glu in different human urine and fingertip blood samples.
Clinical
Measurement Method (mM)		The Proposed Method
Spiked (mM)Found (mM)Recovery (%)
Urine I000/
0.20.1890
0.50.54108
Urine II000/
11.09109
21.9597.5
Urine III000/
55.17103.4
109.5695.6
Fingertip blood I4.6204.5398.1
15.67100.9
510.35107.6
Fingertip blood II8.3508.95107.2
19.64103.1
514.52108.8
Fingertip blood II10.5609.8693.37
111.97103.5
516.5106
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Sun, E.; Gu, Z.; Li, H.; Liu, X.; Li, Y.; Xiao, F. Flexible Graphene Paper Modified Using Pt&Pd Alloy Nanoparticles Decorated Nanoporous Gold Support for the Electrochemical Sensing of Small Molecular Biomarkers. Biosensors 2024, 14, 172. https://doi.org/10.3390/bios14040172

AMA Style

Sun E, Gu Z, Li H, Liu X, Li Y, Xiao F. Flexible Graphene Paper Modified Using Pt&Pd Alloy Nanoparticles Decorated Nanoporous Gold Support for the Electrochemical Sensing of Small Molecular Biomarkers. Biosensors. 2024; 14(4):172. https://doi.org/10.3390/bios14040172

Chicago/Turabian Style

Sun, Encheng, Zhenqi Gu, Haoran Li, Xiao Liu, Yuan Li, and Fei Xiao. 2024. "Flexible Graphene Paper Modified Using Pt&Pd Alloy Nanoparticles Decorated Nanoporous Gold Support for the Electrochemical Sensing of Small Molecular Biomarkers" Biosensors 14, no. 4: 172. https://doi.org/10.3390/bios14040172

APA Style

Sun, E., Gu, Z., Li, H., Liu, X., Li, Y., & Xiao, F. (2024). Flexible Graphene Paper Modified Using Pt&Pd Alloy Nanoparticles Decorated Nanoporous Gold Support for the Electrochemical Sensing of Small Molecular Biomarkers. Biosensors, 14(4), 172. https://doi.org/10.3390/bios14040172

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