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Article

A Double-Deck Structure of Reduced Graphene Oxide Modified Porous Ti3C2Tx Electrode towards Ultrasensitive and Simultaneous Detection of Dopamine and Uric Acid

by
Yangguang Zhu
1,2,
Qichen Tian
3,
Xiufen Li
1,*,
Lidong Wu
4,
Aimin Yu
5,
Guosong Lai
6,
Li Fu
7,
Qiuping Wei
8,
Dan Dai
2,9,
Nan Jiang
2,9,
He Li
2,9,
Chen Ye
2,9,* and
Cheng-Te Lin
2,9,*
1
Laboratory of Environmental Biotechnology, School of Environmental and Civil Engineering, Jiangnan University, Wuxi 214122, China
2
Key Laboratory of Marine Materials and Related Technologies, Zhejiang Key Laboratory of Marine Materials and Protective Technologies, Ningbo Institute of Materials Technology and Engineering (NIMTE), Chinese Academy of Sciences, Ningbo 315201, China
3
College of Chemical Engineering, Zhejiang University of Technology, Hangzhou 310032, China
4
Key Laboratory of Control of Quality and Safety for Aquatic Products, Chinese Academy of Fishery Sciences, Beijing 100141, China
5
Department of Chemistry and Biotechnology, Faculty of Science, Engineering and Technology, Swinburne University of Technology, Hawthorn, VIC 3122, Australia
6
Department of Chemistry, Hubei Normal University, Huangshi 435002, China
7
College of Materials and Environmental Engineering, Hangzhou Dianzi University, Hangzhou 310018, China
8
School of Materials Science and Engineering, Central South University, Changsha 410083, China
9
Center of Materials Science and Optoelectronics Engineering, University of Chinese Academy of Sciences, Beijing 100049, China
*
Authors to whom correspondence should be addressed.
Biosensors 2021, 11(11), 462; https://0-doi-org.brum.beds.ac.uk/10.3390/bios11110462
Submission received: 11 October 2021 / Revised: 6 November 2021 / Accepted: 15 November 2021 / Published: 18 November 2021
(This article belongs to the Special Issue Biosensors for Monitoring of Biologically Relevant Molecules)
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Abstract

:
Considering the vital physiological functions of dopamine (DA) and uric acid (UA) and their coexistence in the biological matrix, the development of biosensing techniques for their simultaneous and sensitive detection is highly desirable for diagnostic and analytical applications. Therefore, Ti3C2Tx/rGO heterostructure with a double-deck layer was fabricated through electrochemical reduction. The rGO was modified on a porous Ti3C2Tx electrode as the biosensor for the detection of DA and UA simultaneously. Debye length was regulated by the alteration of rGO mass on the surface of the Ti3C2Tx electrode. Debye length decreased with respect to the rGO electrode modified with further rGO mass, indicating that fewer DA molecules were capable of surpassing the equilibrium double layer and reaching the surface of rGO to achieve the voltammetric response of DA. Thus, the proposed Ti3C2Tx/rGO sensor presented an excellent performance in detecting DA and UA with a wide linear range of 0.1–100 μM and 1–1000 μM and a low detection limit of 9.5 nM and 0.3 μM, respectively. Additionally, the proposed Ti3C2Tx/rGO electrode displayed good repeatability, selectivity, and proved to be available for real sample analysis.

1. Introduction

Dopamine (DA) is a catecholamine neurotransmitter in the central nervous system which contributes to various physiological functions, including memory, stimulus-response, motion control and vasodilation. [1,2]. The abnormality of DA is clinically related to several neurological disorders, such as senile dementia, Parkinson’s disease, and schizophrenia [3]. Uric acid (UA) is the major end product of purine metabolism, and an excess of UA levels may lead to serious chronic and metabolic diseases, such as gouty, hyperuricemia and kidney injury [4,5]. Considering the vital physiological functions of DA and UA and their coexistence in the biological matrix, the development of biosensing techniques for their simultaneous detection with high sensitivity is desirable for diagnostic and analytical applications [6,7].
Conventional analytical methods for the simultaneous detection of DA and UA, such as high-performance liquid chromatography (HPLC), chemiluminescene, and capillary electrophoresis, have been under development for decades [8,9,10]. As DA and UA are electrochemically active compounds, the electrochemical method has been adopted for the detection of these biomolecules with high sensitivity, simplicity and time efficiency [11,12,13]. However, the oxidation peak positions of these biomolecules are almost the same and difficult to distinguish effectively when using conventional electrodes such as glassy carbon electrodes (GCE) [14]. By using various nanomaterials modified on GCE chemically, the peak resolutions of these biomolecules have been much improved [15]. Therefore, this method has been widely adopted for the recognition of DA and UA simultaneously [16,17].
Among them, graphene has received extensive attention, due to its high surface-to-volume ratio, good electrical conductivity and high carrier mobility [18,19,20,21,22]. Kim et al. proposed a graphene-modified electrode for the selective detection of DA with a linear range of 4.0–100.0 μM and a detection limit of 2.6 μM [23]. Qi et al. constructed an electrochemical sensor based on pristine graphene to detect DA and UA, achieving a linear range of 5.0–710 μM and 6.0–1330 μM and a detection limit of 2.0 and 4.8 μM, respectively [24]. Gao et al. fabricated a graphene oxide (GO)-modified GCE with the covalent coupling method, indicating a good performance in sensing DA with a detection range of 1.0–15.0 μM and a detection limit of 0.27 μM [25]. However, since DA in human blood is usually low as 0.01–1 μM, the sensitivity of graphene-modified electrodes needs to be further improved [26]. Conventionally, using a graphene hybrid with metal (Au, Pt, Ag) nanoparticles (NPs) or carbon nanomaterial (as carbon nanotubes (CNTs)) is a common approach to increase the electrochemical activity of a modified electrode. Wang et al. synthesized novel Au NPs and reduced the graphene oxide (rGO) composite film by electrodepositing AuNPs onto the rGO surface, showing good performance in its ability to detect DA and UA with a linear range of 6.8–41.0 μM, 8.8–53.0 μM and a low detection limit of 1.4, 1.8 μM, respectively [27]. Sun et al. demonstrated a novel sensor based on graphene and Pt NPs nanocomposite by self-assembling Pt NPs onto the graphene surface, indicating its excellent performance in detecting DA and UA with a linear range of 0.03–8.13 μM, 0.05–11.9 μM and a low detection limit of 0.03, 0.05 μM, respectively [28]. Sun et al. developed a sensor based on CNTs and GO nanocomposite, exhibiting its performance in detecting DA and UA with a linear range of 5.0–500 μM, 3.0–60.0 μM and a low detection limit of 1.5, 1.0 μM, respectively [29].
Compared to the electrode modified by graphene, the detection performance of the electrode modified by graphene-based nanocomposite is improved, but it still needs to be further promoted. The interfacial binding strength of graphene-based nanocomposite and electrode may not be high either. To overcome this problem, a new and promising 2D nanomaterial with a 2D-layered structure, MXene, especially titanium carbide MXene (Ti3C2Tx), has been extensively applied as a material with a high number of electric electrodes for batteries, supercapacitors and electrochemical detection [30,31,32,33]. Due to its excellent metallicity, electrical conductivities, hydrophilic surfaces, and environmental-friendly characteristics, Ti3C2Tx has been employed for the electrochemical detection of biomolecules, H2O2, and heavy metal ions [34,35,36]. Murugan et al. proposed a Ti3C2Tx-modified electrode, which exhibited good performance in determining DA and UA and obtained a low detection limit of 0.06 and 0.08 μM, respectively [37]. These successful applications of Ti3C2Tx in the electrochemical detection prove that Ti3C2Tx is an ideal conductive matrix and improves electron transfer kinetic effectively. Particularly, the Ti-O-C covalent bonding is formed at the Ti3C2Tx/rGO heterointerface via nucleophilic substitution dehydration reaction, and charge transport through the heterointerface is increased [38]. Therefore, the interfacial binding strength of Ti3C2Tx/rGO heterointerface increases, resulting in an excellent electrochemical performance in detecting biomolecules. The Debye screening length, λD, is defined as the effective thickness of the equilibrium double layer (EDL) [39]. The detection limit of biosensors is determined by λD between the surface of sensitive nanomaterials and the electrolyte [40]. Thus, λD can be altered effectively to obtain the low detection limit of biosensors based on the Ti3C2Tx/rGO heterostructure.
In this work, we attempted to construct Ti3C2Tx/rGO heterostructure with double-deck layer through electrochemical reduction. The rGO was modified on porous Ti3C2Tx electrode as the biosensor for the detection of DA and UA simultaneously. The Debye length was regulated by the alteration of rGO on the surface of Ti3C2Tx electrode. As evidenced by the differential pulse voltammetry (DPV) test, this proposed Ti3C2Tx/rGO sensor exhibited an excellent performance in detecting DA and UA with a linear range of 0.1–100 μM and 1–1000 μM and a low detection limit of 0.0095 and 0.3 μM, respectively. Additionally, the proposed biosensor indicated good repeatability, selectivity, and potential for real sample analysis.

2. Materials and Methods

2.1. Chemicals

Potassium chloride (KCl), sodium chloride (NaCl), sodium sulphate (Na2SO4), dibasic sodium phosphate (Na2HPO4), potassium dihydrogen phosphate (KH2PO4), and Uric acid (UA) were purchased from Sinopharm Chemical Reagent Co., Ltd. (Shanghai, China). Dopamine (DA) was purchased from Shanghai Aladdin Biochemical Technology Co., Ltd. (Shanghai, China). All of the above chemical reagents were analytical reagents and were used without further purification. GO powder and rGO water dispersion were purchased from Nanjing JCNANO Technology Co., Ltd. (Nanjing, China). Ti3C2Tx water dispersion was purchased from Beike 2D materials Co., Ltd. (Suzhou, China). Deionized Milli-Q water (18.2 MΩ/cm) was used throughout the experiments.

2.2. Fabrication of Ti3C2Tx/rGO Electrodes

The Ti3C2Tx water dispersion and GO water dispersion were dispersed ultrasonically for 1 h in an ice bath. Before modification, GCE electrodes with a diameter of 3 mm were polished using a 0.05 μm alumina slurry and cleaned in deionized water and ethanol by ultrasonication. Following that, GCE was activated via repetitive potential range scanning from −1–1 V with a scan rate of 0.1 V/s in 0.5 M H2SO4. The Ti3C2Tx dispersion was uniformly dropped onto the surface of the GCE and dried, followed by GO dispersion in the same way (Ti3C2Tx/GO electrode). The Ti3C2Tx/rGO-modified GCE was obtained through the electrochemical reduction method of immersing Ti3C2Tx/GO into PBS with cyclic voltammetry (CV) sweeping in the potential range of 0.0–1.4 V at a scan rate of 0.1 V/s for 5 cycles, which was defined as the experimental group (Ti3C2Tx/rGO electrode). As shown in Figure S1 (see Supplementary Materials), a large reduction peak was observed at the potential peak position of −1.23 V in the first cycle, and vanished subsequently, which referred to the electrochemical reduction process of GO to rGO. As controls, Ti3C2Tx-modified GCE (Ti3C2Tx electrode) and rGO modified-GCEs (rGO electrode) were also prepared using the same method.

2.3. Characterizations

Field emission scanning electron microscope (FE-SEM QUANTA 250 FEG, FEI, Hillsboro, OR, USA) and energy dispersive spectroscopy (EDS)-mapping were applied to observe the morphology of the nanomaterials, including CNTs and AgNWs, separately, and the composite material. The surface compositions and chemical states were carried out by Raman spectroscopy (Renishaw in Via Reflex, Renishaw plc, Wotton-under-Edge, London, UK) with a laser wavelength of 532 nm and X-ray photoelectron spectroscopy (XPS, Axis Ultra DLD, Kratos Analytical, Manchester, UK), respectively. All electrochemical experiments were conducted with a CHI660e electrochemical workstation (Shanghai Chenhua Co., Ltd., Shanghai, China).

2.4. Electrochemical Tests

The electrolyte was a phosphate buffer solution (PBS) which contained 137 mM NaCl, 102.7 mM KCl, 8.1 mM Na2HPO4, and 1.8 mM KH2PO4 (pH ≈ 7.4). The bare GCE, Ti3C2Tx, rGO, and Ti3C2Tx/rGO were applied as working electrodes, which were separately immersed into PBS containing different DA concentrations, from 9.5 nM to 100 μM, and different UA concentrations, from 0.3 μM to 1000 μM, respectively, to compare their electrochemical performances. A saturated calomel electrode (SCE, Pt Hg(l)|Hg2Cl2 (s)|KCl (saturated)) and a Pt electrode were applied as a reference electrode and counter electrode, respectively. CV, DPV, and electrochemical impedance spectroscopy (EIS) tests were conducted to analyze the electrochemical behavior of different concentrations of DA and UA on the GCE modified with various materials. CV curves (five cycles) were recorded from 0 to 0.5 V with scan rate of 0.1 V/s, while DPV tests were conducted from −0.2 to 0.5 V with an increment step of 4 mV, amplitude of 50 mV, and pulse period of 0.5 s. EIS was performed in 0.1 to 100 KHz on various modified electrodes with 10 mV amplitude of the AC voltage.

3. Results and Discussion

3.1. Characterization of Ti3C2Tx/rGO Nanocomposite

The schematic diagram of the simultaneous electrochemical detection procedures of DA and UA on Ti3C2Tx/rGO electrode is displayed in Figure 1a. The uniform Ti3C2Tx and GO water dispersion were prepared through ultrasonication. GO dispersion was dropped and dried on the Ti3C2Tx electrode to form a Ti3C2Tx/GO electrode with a double-deck structure, and an electrochemical reduction process was applied using CV sweeping to obtain a Ti3C2Tx/rGO electrode for DA and UA detection. Based on previous studies (Figure 1b) [41], a pair of reversible peaks (Ox1, Re1) can be interpreted as the two-electron oxidation of DA to o-dopaminoquinone. Meanwhile, a pair of reversible peaks (Ox2, Re2) originated from the transformation of UA to dehydrourate. Specifically, oxidation peaks Ox1, Ox2 at 0.185 V and 0.316 V were chosen as the characteristic peaks for quantitative analysis of the electrochemical behavior of DA and UA, respectively.
According to the morphologies of Ti3C2Tx shown in Figure 2a, Ti3C2Tx was well distributed on the surface of GCE, and a porous electrode with good electrical conductivity was formed. Figure 2b is an enlarged view of Figure 2a, and the corresponding EDS mapping of C, Ti, F, and O are shown. The results indicate the two-dimensional layered sheet-like structures of Ti3C2Tx with good flatness. Figure 2c displays the morphologies of Ti3C2Tx/rGO, exhibiting the rough surface of rGO with random wrinkles and the layered structures of Ti3C2Tx. Figure 2d is an enlarged view of Figure 2c, and the corresponding EDS mapping of C, Ti, F, and O are shown. The morphology revealed the recovery of rGO film to the surface of Ti3C2Tx.
The Raman spectra of rGO, Ti3C2Tx and Ti3C2Tx/rGO are shown in Figure 2e. Three main peaks of rGO, namely the D band (~1350 cm−1), G band (~1580 cm−1), and 2D band (~2700 cm−1), correspond to random vibration of amorphous carbon (sp3 hybrid carbon) and in-plane vibration of graphitic carbon (sp2 hybrid carbon) [42]. The peak positions of Ti3C2Tx at 199 and 719 cm−1 are assigned to the out-of-plane vibrations of Ti and C atoms. The modes at 287, 369, and 624 cm−1 are the Eg group vibrations, including in-plane modes of Ti and C, and surface functional group atoms [43]. The peak positions of Ti3C2Tx/rGO are located at 205, 287, 369, 624, 723, 1350, 1580, and 2700 cm−1, verifying the existence of both Ti3C2Tx and rGO in the composite. From the full XPS survey spectra of Ti3C2Tx/rGO, F 1s, Ti 2s, O 1s and Ti 2p, C 1s appear at the binding energy of 684.8, 536.6, 496.9, 462.8 and 287.7 eV, respectively, as shown in Figure 2f, confirming the presence of four elements in the composite [44]. As depicted in Figure 2g, the Ti 2p narrow spectra of Ti3C2Tx/rGO are divided into two parts: Ti 2p3/2 and Ti 2p1/2. Ti 2p3/2 spectra can be segmented into four components, which are located at 454.9 eV (Ti-C), 455.4 eV (Ti(II)), 456.3 eV (Ti(III)), and 458.8 eV (TiO2). The Ti 2p1/2 spectra can be fitted into three components, which are located at 461.1 eV (Ti-C), 462.1 eV (Ti(II)), and 462.6 eV (Ti(III)). Next, C 1s’ XPS curve can be fitted into five components (Figure 2h), which correspond to 284.8 eV (C-C), 281.6 eV (C-Ti), 282.4 eV (C-Ti-O), 287.5 eV (C=O), and 288.6 eV (O-C=O) [45]. Notably, the peak of C=O and O-C=O are ascribed to the introduction of rGO and the closed interaction between Ti3C2Tx and rGO [46]. The O 1s spectrum of Ti3C2Tx/rGO is well fitted into two components (Figure 2i), which are centered at 531.8 eV (C-Ti-OH) and 529.6 eV (Ti-O-Ti). Therein, the oxygen-containing functional termination groups of Ti3C2Tx/rGO were confirmed by the presence of C-Ti-OH bond [47]. The XPS consequence verifies the formation of Ti3C2Tx/rGO heterostructure and is consistent with the previous results.

3.2. Electrochemical Collaboration Behavior of Ti3C2Tx/rGO towards DA

To investigate the electrochemcial response of Ti3C2Tx/rGO towards DA and UA, CV scanning was performed on the Ti3C2Tx/rGO electrode in PBS with 10 μM DA and 10 μM UA. As shown in Figure 3a, compared with the CV curve from blank PBS, there is an oxidation peak and a reduction peak in the CV curve of DA (Re1, Ox1), and UA (Re2, Ox2) [41]. Among them, Ox1 and Ox2 were specified as the characteristic peaks for qualitative and quantitative analysis of the electrochemical behavior of DA and UA, respectively. As shown in Figure 3b,c, DPV curves of electrochemical behaviors at a potential interval of 0.0–0.5 V were conducted in the presence of 10 μM DA on bare GCE, Ti3C2Tx, rGO, and Ti3C2Tx/rGO electrodes. The current intensity of the Ti3C2Tx electrode exhibited higher than GCE, indicating that the porous Ti3C2Tx electrode with good electrical conductivity promoted the electron transfer of DA oxidation. Compared to the Ti3C2Tx electrode, the current intensity of the rGO electrode improved by nearly double, demonstrating the much better electrochemical performance of rGO than Ti3C2Tx towards DA. Furthermore, the Ox1 current intensity of Ti3C2Tx/rGO electrode was much higher than the sum of rGO and Ti3C2Tx, owing to the synergistic effect of the huge specific surface area of rGO and the porous Ti3C2Tx electrode with good electrical conductivity. To assess the electrochemcial feasibility of various modified electrodes in 10 mM [Fe(CN)6]3−/4−, EIS was performed on bare GCE, Ti3C2Tx, and Ti3C2Tx/rGO electrodes with 10 mV amplitude of the AC voltage, as shown in Figure 3d. The semicircle diameter at higher frequencies in the Nyquist diagram indicates the interfacial electron transfer resistance (Rct), which controls the electron transfer of [Fe(CN)6]3−/4− on the electrode surface [48]. The Rct values of GCE, Ti3C2Tx, and Ti3C2Tx/rGO electrodes were 1036.0, 628.8, and 369.6 Ω, respectively. The result reveals that the Ti3C2Tx/rGO electrode greatly facilitates the electron transfer of the DA electrochemical reaction, which agrees with the former results. Rs, Rp, Qcoat, and Qsub represent the solution resistance, pore resistance, coating constant phase, and double-layer constant phase, respectively, and the corresponding values are listed in Table S1.
To further investigate the synergistic effect of the Ti3C2Tx/rGO nanocomposite, GO and Nafion were taken as the coating layer hybrid with Ti3C2Tx and rGO as the coating layer hybridize with the Au electrode instead of the Ti3C2Tx electrode, in comparison with the Ti3C2Tx/rGO nanocomposite modified electrode. As shown in Figure 3e,f, the current intensity on the Ti3C2Tx/Nafion electrode was lower than that of the Ti3C2Tx electrode. This indicates that Nafion as an electric material is not suitable for hybridizing with Ti3C2Tx to DA electrochemical reaction. The current intensity of the Ti3C2Tx/rGO electrode was higher than of the Ti3C2Tx/GO electrode, indicating that less oxygen-containing groups of rGO with better electrical conductivity exhibited greater facilitation of electron transfer reaction of DA. Interestingly, the current intensity of Au electrode/rGO electrode was lower than that of the Ti3C2Tx/rGO electrode, demonstrating the advantage of the porous Ti3C2Tx electrode to the smooth Au electrode towards DA electrochemical reaction, as displayed in Figure S2. To further reveal the superior electrochemical performance of rGO to Ti3C2Tx, a comparison experiment of DA adsorption performance was conducted between Ti3C2Tx and rGO water dispersions, as shown in Figure 3g. Ti3C2Tx and rGO water dispersions containing 100 μM DA were prepared with sonification. After filtration by 0.22 μM membrane, the filtrates of Ti3C2Tx and rGO dispersions both became much more transparent, and the colors of both film membranes were much darker. The result demonstrates that nanomaterials such as Ti3C2Tx and rGO adsorption DA were mostly trapped on the membrane. Then, the DPV curves of electrochemical behaviors at a potential interval of 0.0–0.35 V were conducted on the Ti3C2Tx/rGO electrode in electrolytes using original DA solutions, filtrates of the Ti3C2Tx, and rGO dispersions containing 300 μM DA, respectively, as shown in Figure 3h. The adsorption consequence revealed that the DA adsorption performance of rGO was greater than that of Ti3C2Tx. This may be due to the electrostatic interaction between positively charged DA (pKa = 8.87) and negatively charged rGO with oxygen-containing groups at pH 7.0, as well as the π–π interaction between the phenyl structure of DA and two-dimensional planar hexagonal carbon–carbon structure of graphene, rather than the electrostatic interaction between DA and negative Ti3C2Tx only [49].

3.3. Ti3C2Tx/rGO Electrode Performance Optimization of DA Detection

To further improve the electrochemical performance of the proposed sensor, experimental parameters including the preparation of modified electrodes, electrolyte pH were optimized. To affirm the influence of the preparation of layer-by-layer structured Ti3C2Tx/rGO electrode on the DPV response in PBS with 100 nM DA, various rGO masses including 0.03, 0.075, 0.15, 0.3, 0.75, and 1.5 μg were formed on the same Ti3C2Tx electrode cast on 6.0 μg. As shown in Figure 4a, the background current of the DA detection peak in 0.124 V greatly increased with the rising mass of rGO, and the DA oxidation peak was obviously observed only when rGO mass adjusted to 0.075 μg in the fabrication of the Ti3C2Tx/rGO electrode. The results reveal that the rising mass of rGO was not suitable for the nM concentration level of effective DA detection, and rGO mass was chosen as 0.075 μg. Similarly, to confirm the suitable mass of Ti3C2Tx in the fabrication of Ti3C2Tx/rGO electrode, various Ti3C2Tx masses of 0.6, 1.5, 3, 6, 12, and 30 μg were firstly cast on GCE, and 0.075 μg GO was then dropped on and dried to perform the CV method of electrochemical reduction. The DPV response in PBS with 10 μM DA was then performed, as shown in Figure 4b,c. The Ti3C2Tx mass was selected as 3 μg, and the corresponding optimal mass ratio of Ti3C2Tx to rGO was 40:1.
To better determine if the mechanism of a lower rGO mass is suitable for trace level DA detection, CV and DPV curves at a potential interval of 0.0–0.5 V were performed in PBS on an rGO electrode cast with masses of 0.15 μg, 0.6 μg, and 3.0 μg respectively, as shown in Figure 4d,e. The capacitance can be calculated by CV methods with the following formula: C = ∫ V 0 V 0 + Δ V i   d V S · Δ V , wherein, S refers to scan rate; ΔV refers to potential scan range; and i refers to current. The area Ac of the CV curves determines the value of capacitance, when S and ΔV remain consistent. Obviously, the results reveal that the total capacitance formed on the rGO electrode and the background current both increased with the rising rGO mass. The structure of the EDL at the junction of a metal with an electrolyte solution conceives the layer to have two elements, known as “Helmholtz layer, and diffuse layer” [50]. The two elements interpret the existence of a capacitance Cd of electrical double layer to be close to the solid/electrolyte interface, the Helmholtz capacitance CH, and diffuse layer capacitance CD, wherein Cd−1 = CH−1 + CD−1 [51]. The thickness of the diffuse layer gives the distance from the solution up to the point where the electrostatic effect of the surface is felt by the ions [40]. According to the schematic diagram in Figure 4f,g, when the rGO mass modified on GCE increased, the total capacitance Cd increased, and the diffuse layer capacitance CD increased. Thus, λD decreased with respect to the rGO electrode modified with greater rGO mass, indicating that fewer DA biomolecules were capable of passing through EDL and reaching the surface of GO to achieve the voltammetric response of DA. The increasing mass of GO decreased λD, suggesting that the detection limit of DA was raised to a higher level, and the result is consistent with Figure 4a.
The effect of pH on the electrochemical response of the Ti3C2Tx/rGO electrode was conducted in the range from 3.0 to 11.0, as shown in Figure 4h. The oxidation peak potentials of DA shifted negatively with the increased electrolyte pH, ascribing to an improvement in the reversibility of the investigated faradic process that involves the deprotonation of DA, followed by the protonation of the amine group in DA to form a cation [52,53]. The value of the peak current reached the maximum at pH 7.0 and was selected as the optimal pH value. The electrochemical behavior of various electrodes was performed by CV in 10 mM [Fe(CN)6]3−/4− containing 0.1 M KCl electrolyte solution at scan rates ranging from 20 to 260 mV s−1 (Figure 4i). The observed peak currents (Ipa and Ipc) both increased linearly, with the square root of scan rates as shown in Figure 4j, indicating that the Ti3C2Tx/rGO electrodes were controlled by diffusion [54].

3.4. Electrochemical Determination of DA and UA with Different Concentrations

The quantitative electrochemical detection of DA and UA on the Ti3C2Tx/rGO electrode was conducted via DPV measurements, as shown in Figure 5a,b. An increase in peak current value was recorded with the increasing concentration of DA in a range from 9.5 nM to 100 μM, and the increasing concentration of UA in a range from 300 nM to 1000 μM, respectively. Correspondingly, the inset graphic of Figure 5a,b depicts the enlarged view in the potential range from 0.0–0.3 V and 0.1–0.4 V to clearly show the variations of DPV curves ranging from 0.0–100 nM DA and 0.0–1.0 μM DA, respectively. As presented in Figure 5c, the calibration curve of DA and UA was obtained from the average of peak current data. According to the calibration curve, the linear range of DA detection was in a range from 0.1 to 100 μM, and UA detection was in a range from 1 to 1000 μM, respectively. The linear regression equation of DA was Ipc (μA) = 0.413 lg DA (μM) − 5.780 (R2 = 0.993), and the linear regression equation of UA was Ipc (μA) = 0.529 lg UA (μM) − 0.209 (R2 = 0.994). The limit of detection (LOD) of DA and UA on the Ti3C2Tx/rGO electrode was determined as 9.5 nM and 300 nM, respectively.
Specifically, the quantitative electrochemical detection of DA and UA were conducted by DPV measurements on six individual electrodes. Compared with graphene- based modified electrodes prepared using various methods for simultaneous detection of DA and UA, as shown in Figure 5d, our Ti3C2Tx/rGO electrode achieved a relatively low simultaneous detection LOD of DA and UA and a four-order-magnitude linear range with convenience and efficiency. The corresponding literatures are listed in Table 1.

3.5. Repeatability, Reproducibility, Interference, and Real Sample Analysis

In order to study the repeatability of the Ti3C2Tx/rGO electrode for DA detection (10 μM), the Ox1 peak currents in DPV curves were repeatedly measured 11 times on the same electrode at a potential interval of 0.0–0.5 V. As shown in Figure 5e, the reduction peak potentials of DPV curves were consistent at 0.129 V, and these curves overlapped well. The relative standard deviation (RSD) of peak currents was 3.57%. The reproducibility of the Ti3C2Tx/rGO electrode was performed in the presence of 10 μM DA by using six individual electrodes in DPV curves, as shown in Figure 5f, and the RSD was 3.92%. The results indicate that the Ti3C2Tx/rGO electrode has good repeatability and reproducibility. The anti-interference of the Ti3C2Tx/rGO electrode was investigated via DPV curves in PBS containing various concentrations of DA ranging from 0.1 μM to 10 μM in the presence of 30 μM UA as interfering substances, as shown in Figure 5g. Similarly, the anti-interference was performed in PBS containing UA ranging from 1 μM to 100 μM in the presence of 10 μM DA, as presented in Figure 5h. When compared to the calibration curve of DA and UA detection individually in Figure 5a,b, the anti-interference results indicate that DA and UA did not induce obvious interference in the DPV determination of each other. The anti-interference of Ti3C2Tx/rGO electrode in the presence of other potential interfering substances as 100 µM glucose, 100 µM ascorbic acid (AA), 100 µM H2O2, and 10 µM isoniazid in PBS containing 3 μM DA and 3 μM UA was investigated via DPV curves, as shown in Figure S3. The results indicate that our constructed sensor will not be affected by these molecules during testing.
To evaluate the practical application performance of Ti3C2Tx/rGO electrodes for simultaneous detection of DA and UA, human serum was selected as real samples for analysis using the standard addition technique. The serum samples were centrifuged at 6000 rpm for 5 min, and the supernatants were collected and diluted 100 times with PBS. Then KCl was added to 0.1 M of the serum samples, and the pH was adjusted to 7.0 to perform appropriate electrochemical detection of DA and UA [56]. Serum samples were then spiked with 0.1, 0.3 μM DA, and 1, 3 μM UA, respectively, and the DPV curves of Ti3C2Tx/rGO electrode were extracted, as shown in Figure 5i. The results demonstrate the accuracy and reliability of the fabricated sensor, indicating that the proposed Ti3C2Tx/rGO electrode exhibited good potential for simultaneously detecting DA and UA practically.
Thus, our fabricated Ti3C2Tx/rGO electrode with a double-deck layer was applied as the biosensor for the simultaneous detection of DA and UA successfully. The detection sensitivity of the Ti3C2Tx/rGO electrode was greatly improved with the adjustment to Debye length. Our proposed Ti3C2Tx/rGO electrode displayed good repeatability, selectivity, and proved suitable for real sample analysis.

4. Conclusions

In summary, a Ti3C2Tx/rGO heterostructure with a double-deck layer was fabricated through electrochemical reduction. The rGO was modified on the porous Ti3C2Tx electrode as the biosensor for the simultaneous detection of DA and UA. The Debye length λD is regulated by the alteration of rGO on the surface of the Ti3C2Tx electrode. λD decreased with respect to the rGO electrode modified with a greater rGO mass, indicating that fewer DA biomolecules were capable of passing through EDL and reaching the surface of GO to achieve the voltammetric response of DA. Thus, the proposed Ti3C2Tx/rGO sensor had an excellent performance in the detection of DA and UA, with a wide linear range from 0.1–100 μM to 1–1000 μM and a low detection limit from 0.0095 to 0.3 μM, respectively. Additionally, the proposed Ti3C2Tx/rGO electrode displayed good repeatability, selectivity, and proved suitable for real sample analysis.

Supplementary Materials

The following are available online at https://0-www-mdpi-com.brum.beds.ac.uk/article/10.3390/bios11110462/s1. Figure S1: CV curves of Ti3C2Tx/rGO electrode on electrochemical reduction of GO to rGO. Figure S2: Performance comparison of DPV curves on Ti3C2Tx/rGO and Au/rGO electrode with 10 μM DA in PBS and the corresponding current values. Figure S3: The anti-interference of our electrode in the presence of 100 µM glucose, 100 µM ascorbic acid, 100 µM H2O2 and 10 µM isoniazid with PBS containing 3 µM DA and 3 µM UA. Table S1: The fitting parameters of EIS for GCE, Ti3C2Tx and Ti3C2Tx/rGO electrode.

Author Contributions

Conceptualization, methodology, data curation and writing—original draft, Y.Z.; methodology, data curation, Q.T.; methodology, writing—review and editing, X.L.; conceptualization, methodology, supervision, L.W.; methodology, writing—review and editing, A.Y.; software, writing—review and editing, G.L.; supervision, writing—review and editing, L.F.; supervision, writing—review and editing, Q.W.; methodology, data curation, D.D.; supervision, funding acquisition, N.J.; conceptualization, methodology, supervision, H.L.; data curation, writing—original draft, writing—review and editing, C.Y.; conceptualization, writing—review and editing, funding acquisition, C.-T.L. All authors have read and agreed to the published version of the manuscript.

Funding

The authors are grateful for the financial support from the National Natural Science Foundation of China (U1709205), the National Key R&D Program of China (2017YFE0128600), the Project of the Chinese Academy of Sciences (XDC07030100, XDA22020602, KFZD-SW-409, ZDKYYQ20200001, and ZDRW-CN-2019-3), the CAS Youth Innovation Promotion Association (2020301), the Science and Technology Major Project of Ningbo (2018B10046), the Natural Science Foundation of Ningbo (2017A610010), the Foundation of State Key Laboratory of Solid Lubrication (LSL-1912), the National Key Laboratory of Science and Technology on Advanced Composites in Special Environments (6142905192806), and the K.C. Wong Education Foundation (GJTD-2019-13) for financial support.

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

Data sharing not applicable.

Conflicts of Interest

The authors declare no conflict of interest.

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Figure 1. (a) Schematic diagram of electrochemical detection of DA and UA based on Ti3C2Tx/rGO electrode. (b) The proposed reaction scheme of redox reaction of DA and UA during electrochemical detection, respectively.
Figure 1. (a) Schematic diagram of electrochemical detection of DA and UA based on Ti3C2Tx/rGO electrode. (b) The proposed reaction scheme of redox reaction of DA and UA during electrochemical detection, respectively.
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Figure 2. SEM images of Ti3C2Tx electrode (a) and Ti3C2Tx/rGO electrode (c). (b,d) Regional enlarged view of (a,c) and the EDS mapping of element distribution of C, Ti, F, O, respectively. (e) Raman spectra of Ti3C2Tx, rGO, and Ti3C2Tx/rGO nanocomposite. (f) XPS survey spectra of Ti3C2Tx/rGO, and Ti 2p spectra (g), C 1s spectra (h), O 1s spectra (i) spectra, respectively.
Figure 2. SEM images of Ti3C2Tx electrode (a) and Ti3C2Tx/rGO electrode (c). (b,d) Regional enlarged view of (a,c) and the EDS mapping of element distribution of C, Ti, F, O, respectively. (e) Raman spectra of Ti3C2Tx, rGO, and Ti3C2Tx/rGO nanocomposite. (f) XPS survey spectra of Ti3C2Tx/rGO, and Ti 2p spectra (g), C 1s spectra (h), O 1s spectra (i) spectra, respectively.
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Figure 3. (a) CV of Ti3C2Tx/rGO electrode with and without 10 μM DA and 30 μM UA in PBS. (b) DPV curves of various modified electrodes with 10 μM DA in PBS. (c) The corresponding current value of (b). (d) Impedance plots of various modified electrodes with 10 mM [Fe(CN)6]3−/4−. (e) Performance comparison of DPV curves on various materials modified Ti3C2Tx electrode with 10 μM DA in PBS. (f) The corresponding current value of (e). (g) Schematic diagram of DA adsorption in Ti3C2Tx and rGO dispersion. (h) DPV curves of DA adsorption performance.
Figure 3. (a) CV of Ti3C2Tx/rGO electrode with and without 10 μM DA and 30 μM UA in PBS. (b) DPV curves of various modified electrodes with 10 μM DA in PBS. (c) The corresponding current value of (b). (d) Impedance plots of various modified electrodes with 10 mM [Fe(CN)6]3−/4−. (e) Performance comparison of DPV curves on various materials modified Ti3C2Tx electrode with 10 μM DA in PBS. (f) The corresponding current value of (e). (g) Schematic diagram of DA adsorption in Ti3C2Tx and rGO dispersion. (h) DPV curves of DA adsorption performance.
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Figure 4. (a) DPV curves of Ti3C2Tx/rGO electrode with various masses of rGO to the same of Ti3C2Tx with 100 nM DA in PBS; the inset graphic depicts an enlarged view in the potential range between 0.0–0.3 V. (b) DPV of Ti3C2Tx/rGO electrode with various masses of Ti3C2Tx to the same of rGO with 10 μM DA in PBS. (c) the corresponding current value of (b). (d,e) CV and DPV of rGO electrode in PBS with various amounts of rGO, respectively. (f,g) Schematic diagram of EDL model to interpret DA detection mechanism via Debye length regulation. (h) DPV of 10 μM DA on Ti3C2Tx/rGO electrode with pH. (i) Ti3C2Tx/rGO electrode in 10 mM [Fe(CN)6]3−/4− and 0.1 M KCl electrolyte solution at scan rates (v) from 20 to 260 mV s−1. (j) Linear plots of Ipa/Ipc vs. v.
Figure 4. (a) DPV curves of Ti3C2Tx/rGO electrode with various masses of rGO to the same of Ti3C2Tx with 100 nM DA in PBS; the inset graphic depicts an enlarged view in the potential range between 0.0–0.3 V. (b) DPV of Ti3C2Tx/rGO electrode with various masses of Ti3C2Tx to the same of rGO with 10 μM DA in PBS. (c) the corresponding current value of (b). (d,e) CV and DPV of rGO electrode in PBS with various amounts of rGO, respectively. (f,g) Schematic diagram of EDL model to interpret DA detection mechanism via Debye length regulation. (h) DPV of 10 μM DA on Ti3C2Tx/rGO electrode with pH. (i) Ti3C2Tx/rGO electrode in 10 mM [Fe(CN)6]3−/4− and 0.1 M KCl electrolyte solution at scan rates (v) from 20 to 260 mV s−1. (j) Linear plots of Ipa/Ipc vs. v.
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Figure 5. (a,b) DPV curves of Ti3C2Tx/rGO electrode with various concentrations of DA and UA; the inset graphic depicts an enlarged view in the potential range between 0.0–0.3 V and 0.1–0.4 V, respectively. (c) The corresponding peak current versus DA and UA concentration. (d) The performance comparisons. (e,f) The repeatability and reproducibility of Ti3C2Tx/rGO electrode. (g,h) Good anti-interference of our electrodes. (i) Serum sample analysis.
Figure 5. (a,b) DPV curves of Ti3C2Tx/rGO electrode with various concentrations of DA and UA; the inset graphic depicts an enlarged view in the potential range between 0.0–0.3 V and 0.1–0.4 V, respectively. (c) The corresponding peak current versus DA and UA concentration. (d) The performance comparisons. (e,f) The repeatability and reproducibility of Ti3C2Tx/rGO electrode. (g,h) Good anti-interference of our electrodes. (i) Serum sample analysis.
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Table
Table 1. Performance comparison of graphene-based materials modified electrodes for simultaneous detection of DA and UA.
Table 1. Performance comparison of graphene-based materials modified electrodes for simultaneous detection of DA and UA.
Modified ElectrodesMeasurementsLinear Range (μM)LOD (μM)Ref.
DAUADAUA
rGODPV0.5–600.5–600.50.5[49]
GrapheneAmperometric5.0–7106.0–13302.04.8[24]
GrapheneDPV0.5–20000.8–25000.120.2[14]
Graphene aerogelDPV0.65–750.4–500.220.12[17]
CNTs/GODPV5.0–5003.0–601.51.0[29]
Chitosan/GrapheneDPV1.0–242.0–451.02.0[55]
Au/rGODPV6.8–418.8–531.41.8[27]
Au/Pt/GO/rGODPV0.07–49,8000.13–82,8000.020.04[56]
Pt NPs/GrapheneDPV0.03–8.130.05–11.90.030.05[28]
Ag/rGODPV10–7010–1301.01.0[57]
Pd/Pt/rGODPV4–2004–4000.040.1[6]
Mn3O4/rGOSWV a1–6001–6001.420.76[58]
Hemin/GODPV0.5–400.5–500.170.17[59]
TiN/rGODPV5–17530–2150.160.35[60]
N-doped rGODPV1–601–300.10.2[61]
Ti3C2Tx/rGODPV0.1–1001–10000.00950.3This work
a SWV: Square wave voltammetry.
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Zhu, Y.; Tian, Q.; Li, X.; Wu, L.; Yu, A.; Lai, G.; Fu, L.; Wei, Q.; Dai, D.; Jiang, N.; et al. A Double-Deck Structure of Reduced Graphene Oxide Modified Porous Ti3C2Tx Electrode towards Ultrasensitive and Simultaneous Detection of Dopamine and Uric Acid. Biosensors 2021, 11, 462. https://0-doi-org.brum.beds.ac.uk/10.3390/bios11110462

AMA Style

Zhu Y, Tian Q, Li X, Wu L, Yu A, Lai G, Fu L, Wei Q, Dai D, Jiang N, et al. A Double-Deck Structure of Reduced Graphene Oxide Modified Porous Ti3C2Tx Electrode towards Ultrasensitive and Simultaneous Detection of Dopamine and Uric Acid. Biosensors. 2021; 11(11):462. https://0-doi-org.brum.beds.ac.uk/10.3390/bios11110462

Chicago/Turabian Style

Zhu, Yangguang, Qichen Tian, Xiufen Li, Lidong Wu, Aimin Yu, Guosong Lai, Li Fu, Qiuping Wei, Dan Dai, Nan Jiang, and et al. 2021. "A Double-Deck Structure of Reduced Graphene Oxide Modified Porous Ti3C2Tx Electrode towards Ultrasensitive and Simultaneous Detection of Dopamine and Uric Acid" Biosensors 11, no. 11: 462. https://0-doi-org.brum.beds.ac.uk/10.3390/bios11110462

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