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Label-Free Electrochemiluminescence Nano-aptasensor for the Ultrasensitive Detection of ApoA1 in Human Serum
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Label-Free Electrochemiluminescence Nano-aptasensor for the Ultrasensitive Detection of ApoA1 in Human Serum
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  • Chitra P. Kurup
    Chitra P. Kurup
    Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
  • Noor F. Mohd-Naim
    Noor F. Mohd-Naim
    Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
    PAPRSB Institute of Health Sciences, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
  • Natasha A. Keasberry
    Natasha A. Keasberry
    Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
  • Siti N. A. Zakaria
    Siti N. A. Zakaria
    Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
  • Vipul Bansal
    Vipul Bansal
    Ian Potter NanoBioSensing Facility, NanoBiotechnology Research Laboratory (NBRL), School of Science, RMIT University, GPO Box 2476, Melbourne, Victoria3000, Australia
    More by Vipul Bansal
  • Minhaz U. Ahmed*
    Minhaz U. Ahmed
    Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
    *Email: [email protected]; [email protected]
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ACS Omega

Cite this: ACS Omega 2022, 7, 43, 38709–38716
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https://doi.org/10.1021/acsomega.2c04300
Published October 20, 2022

Copyright © 2022 The Authors. Published by American Chemical Society. This publication is licensed under

CC-BY-NC-ND 4.0 .

Abstract

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A molybdenum sulfide/zirconium oxide/Nafion (MoS2/ZrO2/Naf) based electrochemiluminescence (ECL) aptasensor for the selective and ultrasensitive detection of ApoA1 is proposed, with Ru(bpy)32+ as the luminophore. The chitosan (CS) modification on the nanocomposite layer allowed glutaraldehyde (GLUT) cross-linking, resulting in the immobilization of ApoA1 aptamers. Scanning electron microscopy, tunneling electron microscopy, and energy dispersive X-ray spectroscopy were used to characterize the nanocomposite, while electrochemiluminescence (ECL), cyclic voltammetry, and electrochemical impedance spectroscopy were used to analyze the aptasensor assembly. The nanocomposite was used as an electrode modifier, which increased the intensity of the ECL signal. Due to the anionic environment produced on the sensor surface following the specific interaction of the ApoA1 biomarker with the sensor, more Ru(bpy)32+ were able to be electrostatically attached to the aptamer-ApoA1 complex, resulting in enhanced ECL signal. The ECL aptasensor demonstrated outstanding sensitivity for ApoA1 under optimal experimental conditions, with a detection limit of 53 fg/mL and a wide linear dynamic range of 0.1–1000 pg/mL. The potential practical applicability of this aptasensor was validated by analyzing ApoA1 in human serum samples, with recovery rates of 94–108% (n = 3). The proposed assay was found to be substantially better compared to the commercially available enzyme-linked immunosorbent assay method, as reflected from over 1500 times improvement in the detection limit for ApoA1.

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Copyright © 2022 The Authors. Published by American Chemical Society

Introduction

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Electrochemiluminescence (ECL) is a system involving electrochemical and chemiluminescence analysis, which has received increasing interest in recent years due to its outstanding sensitivity. (1) ECL detection is a robust method for understanding chemistry-related areas, such as medical diagnostics, environment, and food monitoring, which is attributed to the advantages afforded by both electrochemistry and chemiluminescence. (2) ECL is more resistant to autofluorescence background noise and scattered light interference than photoluminescence as there is no excitation light source. Additionally, the accurate and reproducible potential initiates and controls the ECL signals. As a result, in the sensing functionality, ECL sensors provide reliable sensing systems. ECL reagents utilized in the manufacture of biosensors include luminol and its derivatives, quantum dots, and Ru complex. (2) Due to their high photon production and stability, Ru(bpy)32+ as a label and tripropylamine (TPA) as a co-reactant are employed most frequently. (3)
Signal amplification strategies using nanomaterials as electrode materials, carriers, labels, or catalysts have been previously employed to improve the sensitivity of electrochemical sensors. (4−6) Due to their capability to enhance electronic conductivity between electrodes and biomolecules, various nanosized metal oxides are often used to construct biosensor interfaces. (7) Among them, the nanostructured transition metal oxide, zirconia (ZrO2), has sparked credible interest due to its thermal stability, chemical inertness, nontoxicity, wide band gap, and superior electrical and surface properties As a result, it has been reported to possess applications in a range of fields, including orthopedic implants, (8) tissue engineering, biosensing, and bioimaging. (9) However, bare ZrO2 nanoparticles (NPs) tend to aggregate and form large clusters during synthesis, which negatively impacts upon their application potential. To address the issue of ZrO2 NPs agglomeration, graphene-based nanomaterials have been used together with ZrO2, which has been shown to improve their electrochemical sensing properties. (10,11)
A large number of analogues of graphene, which are broadly classified in the family of two-dimensional (2D) materials, have recently emerged as attractive materials for various applications. (12−14) For instance, the 2D layered structure of MoS2, a transition metal dichalcogenide, is analogous to graphene but with a key distinction that MoS2 being a semiconductor offers opportunities for tuning the optoelectronic and luminescence properties, which is restrictive in highly conducting graphene. (15,16) An “S–Mo–S” sandwich structure is formed by a positively charged molybdenum plane and two negatively charged sulfur planes in an atomically thin MoS2 layer. The layers are interconnected by van der Waals interactions. (17) Due to their remarkable physical and electrical features, a large surface area, as well as their ease of manufacture, MoS2 nanosheets have received the significant attention in recent years. The integration of MoS2 with a wide range of materials, including carbon materials, (18) noble metals, (19) transition metals, (20) and polymers (21) has been demonstrated to form a viable multifunctional nanoplatform. Combining two or more different materials to create composite materials can improve the charge transfer capabilities of the composite. As an example of a MoS2-based heterocomposite, the copper nanowires/molybdenum disulfide/reduced graphene oxide (CuNWs/MoS2/rGO) ternary nanostructure was found to have synergistic effects that improved the electrochemical characteristics of the aptasensor for cardiac troponin I (cTnI) detection, resulting in good sensitivity and selectivity. (22) Similarly, the combination of ZnS-CdS NPs with MoS2 was observed to enhance ECL signals, which assisted in developing a sensitive aptasensor for the detection of carcinoembryonic antigen (CEA). (23) These examples illustrate the immense potential for MoS2 in the development of efficient ECL biosensing platforms.
Specific and sensitive detection of protein biomarkers is essential for basic research, disease modeling, and consumer-facing diagnostics applications. (24−26) One such important protein biomarker is human apolipoprotein A-I (ApoA1) that has been implicated as a sensitive predictor of coronary heart disease. (27) ApoA1 is a key protein component of high-density lipoprotein (HDL) that plays an important role in lipoprotein metabolism, reverse cholesterol transport, and atherosclerosis prevention. (28) ApoA1 levels were also found to be lower in the serum of patients with ovarian cancer (29) and atherosclerosis. (30) As a result, development of efficient detection methods for precise detection of ApoA1 is critical for early diagnosis and treatment of associated diseases. As part of the standard clinical screening, ELISA is normally used to assess the level of ApoA1 molecules in biofluids. (31) However, the assay is temperature-sensitive with long incubation periods and high operational costs. Other alternative methods described for ApoA1 detection include HPLC (32) and LCMS, (33) both of which suffer from a long analysis time and the requirement of skilled labor to operate the complex procedure. To this end, several alternative approaches to sensitively detect ApoA1 by employing antibody as a capture probe have been introduced. These include impedance-based electrochemical sensors, (34) surface plasmon resonance (SPR) sensors, (35) and ECL immunosensors. (36) However, some of the key challenges associated with the use of antibodies in sensing platforms are higher production cost and low ambient stability, the latter limiting the sensor shelf life and posing logistic challenges around transport and storage conditions. Aptamers, which are artificial single-stranded DNA or RNA oligonucleotides do not face the above challenges and are thus receiving remarkable interest in recent years to replace antibodies in point-of-care sensing platforms. (37) Aptamers can fold into secondary or three-dimensional complexes in response to specific biological interactions with the target molecules, resulting in favorable binding sites for the analyte and producing highly specific and ultrasensitive detection platforms. (38−40)
In this study, we report a simple and novel MoS2/ZrO2/Naf-based ECL aptasensor (Naf, Nafion) for highly selective and ultrasensitive detection of ApoA1 (Figure 1). The surface of the working electrode of the screen-printed carbon electrode (SPCE) was modified with MoS2/ZrO2/Naf nanocomposite, which was compactly fixed by adding CS. The MoS2/ZrO2/Naf nanocomposite offered large surface area and improved electrochemical activity for biosensing purposes. To construct the SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt-modified sensor, GLUT was used as a cross-linking agent for coupling the ApoA1 aptamers to the modified electrode surface. To generate the ECL signal, the aptasensor was incubated in a phosphate buffer saline solution (pH 7.4) containing KCl, 50 μM Ru(bpy)32+, and 5 mM TPrA. In the presence of the target protein biomarker ApoA1, an aptamer-ApoA1 complex was formed, which improved the ECL signals. The aptasensor provided an ultrasensitive detection of ApoA1 based on the changes in ECL intensity observed. The efficiency of the newly developed ECL aptasensor was demonstrated in the human serum for rapid and sensitive measurement of ApoA1.

Figure 1

Figure 1. Fabrication steps of the ApoA1 aptasensor.

Experimental Section

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Materials and Methods

The materials used in this study have been presented in Supporting Information Section S1.

Preparation of MoS2/ZrO2 Nanocomposite

0.5 mg of MoS2 powder was dispersed in 1 mL of 0.2% Naf with vigorous stirring and sonication for 30 min until the solution reached a homogeneous stable condition. 0.5 mg of ZrO2 in 0.2% Naf was prepared in the same way. Thereafter, the dispersed MoS2 and ZrO2 were mixed in 1:2 ratio and stirred for 2 h to obtain a highly dispersive solution of MoS2/ZrO2/Naf nanocomposite.

Fabrication of ECL Aptasensor

The fabrication process of the ECL aptasensor is depicted in Figure 1. To construct the SPCE/MoS2/ZrO2/Naf/CS layer, 2 μL of the nanocomposite MoS2/ZrO2/Naf was placed on the working electrode of SPCE, then coated with 2 μL of 0.5 mg/mL CS solution, and dried at room temperature. This is followed by dropping 2 μL of GLUT solution (1%) as a cross-linking agent onto the SPCE/MoS2/ZrO2/Naf/CS and incubating at room temperature for 1 h. The electrodes were rinsed in 0.01 M PBS (pH 7.4) after the modification. Thereafter, 2 μL of ApoA1 aptamer (1 μM, NH2 terminated) was added to the modified SPCE and incubated for 1 h at room temperature. The modified electrodes were blocked using 2 μL of 0.1% BSA solution to avoid nonspecific binding after being gently washed with 0.01 M PBS. The constructed aptasensor was stored at 4 °C until future use. In order to detect target protein ApoA1, the aptasensor was incubated with 2 μL of ApoA1 solution at room temperature for 30 min.

Electrochemical and ECL Detection

The detection parameters and instruments used for the detection process are presented in Supporting Information Section S2.

Characterization of the Nanomaterials

Tunneling electron microscopy (TEM), scanning electron microscopy (SEM), energy dispersive X-ray spectroscopy (EDX), and electrochemiluminescence (ECL) analyses were performed to characterize the nanomaterials, which are explained in more detail in the Supporting Information Section S3.

Results and Discussion

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Characterization of Nanomaterials

The morphologies and structure of the prepared nanomaterials MoS2, ZrO2, and the combination of MoS2/ZrO2/Naf were characterized by TEM and the nanocomplex MoS2/ZrO2/Naf was further characterized by SEM. The TEM image of MoS2 showed the presence of folded flakes (Figure 2A), indicating that it has a 2D structure that can offer a large surface area, (41) while the ZrO2 NPs were quasi-spherical with ca. 10–30 in size (Figure 2B). (42) The TEM image of MoS2/ZrO2/Naf (Figure 2C) shows successful dissemination of ZrO2 onto the surface of MoS2, confirming the successful formation of the nanocomposite. The SEM images of MoS2/ZrO2/Naf nanocomposite at different magnification and corresponding EDX spectrum shown in Figure S1A–C in the Supporting Information support the TEM observations. The signature peaks of molybdenum (Mo), zirconium (Zr), oxygen (O), and sulfur (S) observed in the corresponding EDX spectrum of MoS2/ZrO2/Naf (Figure S1C).

Figure 2

Figure 2. TEM images of (A) MoS2, (B) ZrO2, and (C) MoS2/ZrO2/Naf.

To demonstrate the effectiveness of the novel nanocomposite, the ECL signals of MoS2/Naf, ZrO2/Naf, and the nanocomplex MoS2/ZrO2/Naf were recorded in a 50 μM Ru(bpy)32+ and 5 mM TPrA mixture. Among various common ECL luminophores, such as Ru(bpy)32+, quantum dots, luminol, and luminol derivatives, we have used Ru(bpy)32+ due to its ability to generate a consistent and stable ECL signal in solution with its co-reactant TPrA. The ECL intensity of bare SPCE was observed to be as low as 5000 au (Figure S2A, curve a, Supporting Information). When compared to the bare SPCE, the MoS2/Naf- and ZrO2/Naf-coated SPCEs (Figure S2A, curves b and c, Supporting Information) generated improved ECL signals with 6–7 times higher intensity. However, the nanocomplex MoS2/ZrO2/Naf produced an even stronger ECL signal with over 12 times improved intensity (Figure S2A, curve d, Supporting Information), indicating that the electronic characteristics of the hybrid are improved, which perhaps results in improved charge transfer characteristics between the nanocomposite and Ru(bpy)32+-TPrA complex. Considering that the relative amounts of MoS2 and ZrO2 in the nanocomposite can affect the overall charge transfer ability, the MoS2 to ZrO2 ratio in MoS2/ZrO2/Naf was also optimized by considering the highest ECL intensity observed. As demonstrated in Figure S2B in the Supporting Information, the 1:2 ratio of MoS2 to ZrO2 produced the highest ECL intensity, and thus this composition was used for the subsequent experiments.
The successful assembly of the aptasensor as illustrated in Figure 1 was characterized by CV in 0.01 M PBS (pH 7.4) containing 5.0 mM [Fe(CN)6]3–/4– and 0.1 M KCl, as shown in Figure 3A. First, the CV of a bare electrode (curve a) was recorded and it was observed that [Fe(CN)6]3–/4– had a definite reversible redox activity. When Naf was introduced to the bare electrode (curve b), a reduction in CV current was detected, suggesting that negatively charged Naf substantially decreased the electron transfer rate between the electrode and [Fe(CN)6]3–/4–. Upon modification of the electrode with MoS2/ZrO2/Naf (curve c), a pair of well-defined oxidation and reduction peaks were recorded, potentially attributable to the excellent electrical conductivity of the MoS2/ZrO2 nanocomplex. The addition of CS and GLUT substantially reduced the CV signal (curve d) due to the insulating effect of GLUT on the electrode’s electroactive surface, which hampered electron transport. (43) After the immobilization of aptamer onto the GLUT-functionalized electrode surface, a slight increase in the CV peak current was observed potentially due to enhanced charge transfer mediated by ionic conductance (curve e). As the sugar phosphate backbone of DNA (aptamer) is negatively charged, it is usually surrounded by positive “counter ions”. This may result in the formation of an aptamer/water/counterion complex, which attracts more negatively charged [Fe(CN)6]3–/4–, hence the detection of an increased CV signal. (43,44) A reduction in the CV signal was subsequently observed with the addition of BSA (curve f). The charge repulsion between the negatively charged protein (the pI of ApoA1 is 5.8 (45)) and the redox probe resulted in a further decrease in CV signal after the incubation of the aptasensor with ApoA1 protein (curve g). A validation of the current response was performed using a cationic redox species, RuHex ([Ru(NH3)6]3+) (Figure 3B), and the results were compared to that of the anionic [Fe(CN)6]3–/4–- redox species. When the electrode surface was modified with MoS2/ZrO2/Naf (Figure 3B, curve b), the peak current of RuHex increased, indicating that the nanocomposite provided an enhanced electroactive surface area and hence facilitated the electron transport. The Randles–Sevcik equation was used to determine the electroactive surface area (A) of the bare and nanocomposite-modified SPCE. (46)
Ip=2.65×105n3/2AD1/2V1/2C
(1)
where n is the number of electrons exchanged, C is the concentration of the electroactive species (mol/cm3), and D is the diffusion coefficient of the electroactive species (8.43 × 10–6 cm2/s). (47,1) When compared to the unmodified SPCE, the MoS2/ZrO2/Naf-modified SPCE was found to have a 150% higher electroactive surface area. Due to the increase in surface area, the nanocomposite was then employed to modify the working electrode.

Figure 3

Figure 3. Layer-by-layer characterization of ApoA1 aptasensor. (A) Cyclic voltammograms of (a) bare SPCE, (b) SPCE/Naf, (c) SPCE/MoS2/ZrO2/Naf, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt, (f) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA, and (g) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM [Fe(CN)6]3–/4– and 0.1 M KCl. (B) Cyclic voltammograms of (a) bare SPCE, (b) SPCE/MoS2/ZrO2/Naf, (c) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA, and (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM Ru[(NH3)]63+ and 0.1 M NaCl. (C) EIS of (a) bare SPCE, (b) SPCE/MoS2/ZrO2/Naf, (c) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BS, and (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM [Fe(CN)6]3–/4– and 0.1 M KCl.

Upon aptamer immobilization, as well as after ApoA1 incubation, as expected, the opposite phenomenon was seen.With the aptamer immobilization, the CV signal in cationic RuHex solution decreased, instead of the increase we observed with anionic [Fe(CN)6]3–/4– solution. Similarly, incubation of the ApoA1 protein with the aptasensor resulted in an increased CV signal in cationic RuHex solution, instead of the decreased CV signal recorded in anionic [Fe(CN)6]3–/4– solution. From these results, the ECL aptasensor based on MoS2/ZrO2/Naf was deduced to be successfully fabricated for ApoA1 detection.
EIS was employed to examine the interface alterations upon various modifications of the aptasensor electrodes using 5 mM [Fe(CN)6]4–/3– in 0.1 M KCl. (48−50) The charge transfer resistance (Rct) at the electrode surface is equivalent to the diameter of the semicircle. The EIS response after each layer-by-layer modification is displayed as a Nyquist plot in Figure 3C. Due to the repulsive behavior of negative charges from [Fe(CN)6]3–/4–- and Naf, the MoS2/ZrO2/Naf-modified electrode (curve b) had a higher Rct value than the bare SPCE (curve a). (51) After modification of the electrode with the CS/GLUT layer, there was a consecutive increase in Rct (curve c). Upon aptamer immobilization and blocking by BSA, Rct increased even further (curve d). By impeding the electron transfer rate, the binding of ApoA1 to the modified electrode increased the Rct value more notably (curve e). These expected changes in Rct at different stages of sensor development demonstrate the successful fabrication of the aptasensor.

ECL Characterization

Each stage of modification of the SPCE electrode was characterized by the ECL method (Figure 4A) to assess the feasibility and viability of the aptasensor. In 50 μM Ru(bpy)32+ and 5 mM TPrA, the ECL intensity of bare SPCE was observed to be as low as 5000 au (curve a). The ECL intensity for the MoS2/ZrO2/Naf nanocomposite-modified electrode (curve b) increased significantly (∼12×), suggesting that numerous Ru(bpy)32+ molecules were successfully loaded within the heterostructural network of the MoS2/ZrO2/Naf nanocomposite, enabling the enhancement in ECL. With the addition of CS and GLUT layers, however, the ECL signals of the modified electrode rapidly diminished (SPCE/MoS2/ZrO2/Naf/CS/GLUT, curve c). Further reduction in ECL signal (curve d) was observed after modifying the SPCE/MoS2/ZrO2/Naf/CS/GLUT electrode with NH2-Apt and blocking with 0.1% BSA (curve d). This can be attributed to the hindrance brought about by the aptamer immobilization and modification with BSA. (52,53) This additionally confirmed that the SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA ECL aptasensor was successfully fabricated, which had an ECL signal of 8460 au. This ECL value acts as a reference for a bare aptasensor surface before it is exposed to the target analyte. Once this aptasensor was exposed to a 0.1 ppb (100 pg/mL) concentration of ApoA1, the ECL response was enhanced by over 3.8 times (curve e). (54) The presence of more negatively charged molecules attributed to ApoA1 (pI 5.8) (45)) on the surface of the working electrode resulted in an increased number of Ru(bpy)32+ molecules being attracted to the ApoA1 protein-aptamer complex formed. In turn, more electrogenerated Ru(bpy)33+ was reduced to become [Ru(bpy)32+]* by the deprotonated TPrA radical (TPrA) formed with [Ru(bpy)32+]*, which later decayed into an emission and led to the increase in ECL intensity. The ECL reaction mechanism could be described as follows:
Ru(bpy)32+eRu(bpy)33+
TPrAeTPrA+.
TPrA+.TPrA.+H+
Ru(bpy)33++TPrA.(Ru(bpy)32+)*
(Ru(bpy)32+)*Ru(bpy)32++hν

Figure 4

Figure 4. (A) ECL layer-by-layer characterization of ApoA1 aptasensor: (a) bare SPCE, (b) SPCE/MoS2/ZrO2/Naf, (c) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA, and (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1. Chronocoulometry of (B) (a) aptasensor in the absence of ApoA1 and (b) aptasensor in the presence of ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM [Fe(CN)6]3-/4- and 0.1 M KCl and (C) (a) aptasensor in the absence of ApoA1 and (b) aptasensor in the presence of ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM Ru[(NH3)]63+ and 0.1 M NaCl. The insets show the bar graph representations of the CC data.

By employing [Fe(CN)6]3–/4– and [Ru(NH3)6]3+ as redox probes, a chronocoulometric (CC) study was also performed to demonstrate the nature of the surface charge of the ApoA1 aptasensor in the absence and presence of ApoA1. The CC curve in Figure 4B depicts the influence of [Fe(CN)6]3–/4– on the electrostatic charge of an aptasensor without ApoA1 (curve a) and in the presence of ApoA1 (curve b) with the inset showing a bar diagram of the same result. Due to the repulsive electrostatic interactions, the anionic redox probe [Fe(CN)6]3–/4– was repelled in the presence of ApoA1 and therefore had a lower electrostatic charge than the ApoA1 aptasensor in the absence of ApoA1. When ApoA1 was present, however, a higher electrostatic charge was recorded at the surface of the ApoA1 aptasensor (curve b), compared to a lower electrostatic charge observed in the absence of ApoA1, as displayed in Figure 4C, curve a, with the use of [Ru(NH3)6]3+ as a cationic redox probe. This suggested that the surface of the aptasensor in the presence of ApoA1 was more negatively charged than the surface of the aptasensor in the absence of ApoA1.

Analytical Performance of the Aptasensor

The analytical performance of the proposed aptasensor was investigated under the optimized conditions as mentioned in Supporting Information Section S4 (Figure S3). The ECL signal was recorded in the presence of ApoA1 protein, after the formation of the ApoA1-aptamer complex. Because the isoelectric point of ApoA1 is 5.8, it possessed a negative charge at the working pH of 7.4 that could attract more Ru(bpy)32+ to the surface of the aptasensor. As a result, the rate of electrogenerated Ru(bpy)33+ that was reduced to [Ru(bpy)32+]* by TPrA increased upon an increase in ApoA1 concentration, which in turn led to an increase in ECL signal. Figure 5A displays the responses of the constructed ECL aptasensor to different concentrations of ApoA1. A remarkable linear relationship between ECL intensity and logarithmic concentration of ApoA1 (log C, pg/mL) from 0.1 to 1000 pg/mL (0.0001 to 1 ppb) was observed as shown in Figure 5B. The linear regression equation was obtained as y = 7347 log C + 18522 with a correlation coefficient of R2 = 0.98. The theoretical limit of detection (LOD) was calculated to be 0.053 pg/mL using 3σ/m, where m is the slope of the straight line for triplicate measurements and σ is the standard deviation of the blank. The proposed MoS2/ZrO2/Naf-based ECL aptasensor has a wide linear range and great sensitivity when compared to other types of biosensors for ApoA1 detection previously described in the literature (Supporting Information, Table S1). The linear range and detection limits of ApoA1 are also more effective when compared to EC or ECL sensors that did not incorporate aptamer in their sensor design as the introduction of aptamer appeared to increase the selectivity of the biosensor. The wide linear range and low detection limit of our aptasensor are also notable when compared to similar ECL aptasensors based on metal oxide nanoparticles. As a reference, we also used a commercial ApoA1 ELISA immunoassay kit to validate the results obtained from our aptasensor (Figure 5C). The LOD for the ELISA was 0.08 ng/mL (80 pg/mL), while that of the proposed aptasensor was 0.053 pg/mL, which places the sensitivity of the ECL aptasensor for ApoA1 about 1500 times higher than that of the ELISA.

Figure 5

Figure 5. Analytical performance of the aptasensor. (A) ECL response of the proposed aptasensor in detecting ApoA1 from concentrations: (a) 0.1 pg/mL, (b) 1 pg/mL, (c) 10 pg/mL, (d) 50 pg/mL, (e) 100 pg/mL, (f) 5 pg/mL, (g) 750 pg/mL, and (h) 1000 pg/mL in PBS (0.01 M, pH 7.4) containing 5 mM TPrA. (B) Calibration curve of ApoA1 aptasensor at concentrations ranging from 0.1 pg/mL to 1000 pg/mL. (C) Calibration curve of fabricated aptasensor (ECL) and ELISA (absorbance) for ApoA1 detection.

Selectivity, Reproducibility, and Stability of the Aptasensor

The selectivity of the proposed ECL aptasensor was evaluated by analyzing proteins that may interfere with the detection step, such as haptoglobin (HP), leptin, vascular endothelial factor (VEGF), C-reactive protein (CRP), creatine kinase-MB (CKMB), and lipocalin-2 (LCN-2). The ECL intensity displayed by ApoA1 incubation was substantially higher than that of interfering proteins, and no significant difference was recorded between ApoA1 and the mixture of six interfering proteins, as shown in Figure S4A (Supporting Information). The result showed that the ECL aptasensor has a high selectivity for detecting ApoA1. To assess the reproducibility of the proposed aptasensor, the responses of four separate aptasensors fabricated under the same conditions incubated with 100 pg/mL ApoA1 were recorded. The ECL responses of these sensors are comparable and deemed to be acceptable, with the relative standard deviation determined to be 1.1% (Figure S4B, Supporting Information). The long-term stability of the aptasensor was monitored by measuring the ECL intensity once a week, and the aptasensors were stored in the refrigerator at 4 °C while not in use. After 14 days, the aptasensor was able to retain the ECL signal at 90% of its original response, indicating potential long-term stability of the aptasensor (Figure S4C, Supporting Information).

Real Sample Analysis of ApoA1

The potential application of the aptasensor in a real-world situation was tested by detecting ApoA1 in a human serum sample. The serum was diluted (1:100) in PBS, with various concentrations (0.1, 1, 10, 100, and 1000 pg/mL) of standard ApoA1 solution spiked into the human serum sample using the standard addition method. The recoveries of ApoA1 ranged from 94% to 108%, and the RSDs ranged from 3.4% to 6.3% (Table 1).
Table 1. Detection of Different Concentrations of ApoA1 in Human Serum Using Proposed Aptasensor
 spiked concn (pg/mL)determined concn (pg/mL)recovery (%)RSD (%)
human serum sample0.10.1081086.3
 10.94945.5
 1010.51055.1
 1001081083.4
 10001057105.74.9
The accuracy of the proposed ECL aptasensor was evaluated by comparing the results with a commercially available ELISA test. From Table 2, the amount of spiked ApoA1 in serum samples acquired by the proposed ECL method appeared to be in good agreement with that detected by the ELISA method, with a recorded RSD of less than 5%.
Table 2. Detection of Different Concentrations of ApoA1 in Human Serum Using ECL Aptasensor and ELISA
spiked concn (pg/mL)ECL aptasensor (pg/mL)ELISA (pg/mL)RSD (%)
1001081064.7
1000105710502.6

Conclusion

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In summary, an ECL aptasensor based on MoS2/ZrO2/Naf nanocomposite was developed for the detection of ApoA1. Due to the excellent physical and chemical properties of the nanocomposite, the surface area and the electrochemical activity was improved. The nanocomposite exhibited strong ECL intensity when incubated with Ru(bpy)32+ in the presence of TPrA. Chitosan on the modified electrode’s surface assisted in the attachment of the cross-linking agent glutaraldehyde. In turn, more amine terminated ApoA1 aptamers were able to be covalently immobilized, thereby improving the detection sensitivity significantly. The ECL platform exhibited a linear response to ApoA1 for concentrations ranging from 0.1 to 1000 pg/mL, with an LOD of 0.053 pg/mL. It also displayed high specificity for target ApoA1 protein in the presence of various interfering proteins due to the specific recognition and capture ability of the aptamer toward ApoA1. The developed ECL aptasensor presented with good stability and reproducibility, as well as the ability to detect ApoA1 in human serum samples.

Supporting Information

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The Supporting Information is available free of charge at https://pubs.acs.org/doi/10.1021/acsomega.2c04300.

  • Additional information including (Section S1) materials and methods, (Section S2) electrochemical ECL detection, (Section S3) nanomaterials characterization, (Section S4) experimental conditions optimization, (Section S5) comparison of analytical performances of APOA1 detection methods, and (Section S6) selectivity, reproducibility, and stability of the aptasensor (PDF)

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Author Information

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  • Corresponding Author
  • Authors
    • Chitra P. Kurup - Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
    • Noor F. Mohd-Naim - Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei DarussalamPAPRSB Institute of Health Sciences, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei DarussalamOrcidhttps://orcid.org/0000-0002-9496-6249
    • Natasha A. Keasberry - Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
    • Siti N. A. Zakaria - Biosensors and Nanobiotechnology Laboratory, Integrated Science Building, Faculty of Science, Universiti Brunei Darussalam, Jalan Tungku Link, GadongBE 1410, Brunei Darussalam
    • Vipul Bansal - Ian Potter NanoBioSensing Facility, NanoBiotechnology Research Laboratory (NBRL), School of Science, RMIT University, GPO Box 2476, Melbourne, Victoria3000, AustraliaOrcidhttps://orcid.org/0000-0002-3354-4317
  • Funding

    This work was partly supported by the Universiti Brunei Darussalam’s Grants UBD/RSCH/1.4/FICBF(b)/2020/025 and UBD/RSCH/1.4/FICBF(b)/2021/032 and Brunei Research Council Grant-10.

  • Notes
    The authors declare no competing financial interest.

Acknowledgments

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C.P.K. thanks the Ministry of Education of Brunei and Universiti Brunei Darussalam for her Ph.D. fellowship. V.B. acknowledges the Ian Potter Foundation for establishing the Sir Ian Potter NanoBioSensing Facility at RMIT University.

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  • Abstract

    Figure 1

    Figure 1. Fabrication steps of the ApoA1 aptasensor.

    Figure 2

    Figure 2. TEM images of (A) MoS2, (B) ZrO2, and (C) MoS2/ZrO2/Naf.

    Figure 3

    Figure 3. Layer-by-layer characterization of ApoA1 aptasensor. (A) Cyclic voltammograms of (a) bare SPCE, (b) SPCE/Naf, (c) SPCE/MoS2/ZrO2/Naf, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt, (f) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA, and (g) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM [Fe(CN)6]3–/4– and 0.1 M KCl. (B) Cyclic voltammograms of (a) bare SPCE, (b) SPCE/MoS2/ZrO2/Naf, (c) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA, and (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM Ru[(NH3)]63+ and 0.1 M NaCl. (C) EIS of (a) bare SPCE, (b) SPCE/MoS2/ZrO2/Naf, (c) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BS, and (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM [Fe(CN)6]3–/4– and 0.1 M KCl.

    Figure 4

    Figure 4. (A) ECL layer-by-layer characterization of ApoA1 aptasensor: (a) bare SPCE, (b) SPCE/MoS2/ZrO2/Naf, (c) SPCE/MoS2/ZrO2/Naf/CS/GLUT, (d) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA, and (e) SPCE/MoS2/ZrO2/Naf/CS/GLUT/Apt/BSA/ApoA1. Chronocoulometry of (B) (a) aptasensor in the absence of ApoA1 and (b) aptasensor in the presence of ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM [Fe(CN)6]3-/4- and 0.1 M KCl and (C) (a) aptasensor in the absence of ApoA1 and (b) aptasensor in the presence of ApoA1 recorded in 0.01 M PBS solution (pH 7.4) containing 5 mM Ru[(NH3)]63+ and 0.1 M NaCl. The insets show the bar graph representations of the CC data.

    Figure 5

    Figure 5. Analytical performance of the aptasensor. (A) ECL response of the proposed aptasensor in detecting ApoA1 from concentrations: (a) 0.1 pg/mL, (b) 1 pg/mL, (c) 10 pg/mL, (d) 50 pg/mL, (e) 100 pg/mL, (f) 5 pg/mL, (g) 750 pg/mL, and (h) 1000 pg/mL in PBS (0.01 M, pH 7.4) containing 5 mM TPrA. (B) Calibration curve of ApoA1 aptasensor at concentrations ranging from 0.1 pg/mL to 1000 pg/mL. (C) Calibration curve of fabricated aptasensor (ECL) and ELISA (absorbance) for ApoA1 detection.

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  • Supporting Information

    Supporting Information


    The Supporting Information is available free of charge at https://pubs.acs.org/doi/10.1021/acsomega.2c04300.

    • Additional information including (Section S1) materials and methods, (Section S2) electrochemical ECL detection, (Section S3) nanomaterials characterization, (Section S4) experimental conditions optimization, (Section S5) comparison of analytical performances of APOA1 detection methods, and (Section S6) selectivity, reproducibility, and stability of the aptasensor (PDF)


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