key: cord-0745689-u043ljtx
authors: Chinnadayyala, Somasekhar R.; Cho, Sungbo
title: Electrochemical Immunosensor for the Early Detection of Rheumatoid Arthritis Biomarker: Anti-Cyclic Citrullinated Peptide Antibody in Human Serum Based on Avidin-Biotin System
date: 2020-12-28
journal: Sensors (Basel)
DOI: 10.3390/s21010124
sha: 2d1c86b70b8f7812cd999bc3306a2c097bfa4765
doc_id: 745689
cord_uid: u043ljtx

Rheumatoid arthritis (RA) is a chronic autoimmune disease that produces a progressive inflammatory response that leads to severe pain, swelling, and stiffness in the joints of hands and feet, followed by irreversible damage of the joints. The authors developed a miniaturized, label-free electrochemical impedimetric immunosensor for the sensitive and direct detection of arthritis Anti-CCP-ab biomarker. An interdigitated-chain-shaped microelectrode array (ICE) was fabricated by taking the advantage of microelectromechanical systems. The fabricated ICE was modified with a self-assembled monolayer (SAM) of Mercaptohexanoic acid (MHA) for immobilization of the synthetic peptide bio-receptor (B-CCP). The B-CCP was attached onto the surface of SAM modified ICE through a strong avidin-biotin bio-recognition system. The modified ICE surface with the SAM and bio-molecules (Avidin, B-CCP, Anti-CCP-ab and BSA) was morphologically and electrochemically characterized. The change in the sensor signal upon analyte binding on the electrode surface was probed through the electrochemical impedance spectroscopy (EIS) property of charge-transfer resistance (R(ct)) of the modified electrodes. EIS measurements were target specific and the sensor response was linearly increased with step wise increase in target analyte (Anti-CCP-ab) concentrations. The developed sensor showed a linear range for the addition of Anti-CCP-ab between 1 IU mL(−1) → 800 IU mL(−1) in phosphate buffered saline (PBS) and Human serum (HS), respectively. The sensor showed a limit of detection of 0.60 IU mL(−1) and 0.82 IU mL(−1) in the PBS and HS, respectively. The develop bio-electrode showed a good reproducibility (relative standard deviation (RSD), 1.52%), selectivity and stability (1.5% lost at the end of 20th day) with an acceptable recovery rate (98.0% → 101.18%) and % RSD’s for the detection of Anti-CCP-ab in spiked HS samples.

Nearly 1% of the world's population is affected by RA, a chronic autoimmune and degenerative disease [1] [2] [3] . The exact cause for the generation of autoimmune antibodies (AAb) is still unknown, but it is believed that the triggering mechanism caused by genetic (HLA-DR1 and HLA-DR4) and environmental (smoking and pathogens) factors producing autoimmune antibodies attack their own cells [4, 5] . In brief, the citrullination of peptides in Type-II collagen and vimentin produces Citrulline in the place of arginine [6] . Meanwhile, the production of IgM Rheumatoid factor (RF) and Anti-cyclic citrullinated peptide/protein antibodies (Anti-CCP-ab) produces immune complexes with specific antigens that accumulate at the inflamed joints. Early detection of RA indeed plays a vital role in preventing irreversible joint erosion. Almost 70% of the people with a positive Anti-CCPab in their serum have a 5-year risk of developing RA [7] . The impact of anti-rheumatic biosensor finds a suitable position compared to the other electrochemical transduction mechanisms for developing miniaturized point-of-care-testing (POC) applications.

Furthermore, advancements in MEMS has introduced micro-/nanoelectrode's and miniaturized sensing transducers in EIS based transducer platforms for selective, fast and sensitive detection of protein/peptide biomarkers [39, 40] . The MEMS fabrication of an interdigitated chain shaped micro electrode array with a simple electronic circuitry for impedance immunosensing of Anti-CCP-ab provides mass production of electrode arrays with low cost and sample loadings. By considering the collective advantages of aforementioned techniques (SAM, MEMS and EIS), has made the present electrochemical immunosensing strategy competitive with other CCP detection immunosensing techniques.

In the present study, we developed an impedimetric immunosensor by taking the advantage of avidin-biotin interaction systems to attach the cyclic-citrullinated peptide (CCP) on the surface of SAM modified (6-mercaptohexanoic acid) interdigitated chain shaped microelectrode arrays (ICE). As a proof-of-concept, a synthetic peptide (biotin conjugated cyclic-citrullinated peptide; B-CCP) was selected as the bio-receptor to immobilize on the transducer surface for selective detection of the arthritis AAb (Anti-CCP-ab). The change in sensor response upon analyte binding on electrode surface is probed through the electrode interfacial property (charge transfer resistance; R ct ) of EIS. The sensor was miniaturized (14 × 3.5 mm) and can be combined to fabricate a portable immunosensing device to detect Anti-CCP-ab for POC testing. The developed immunosensor (ICE/MHA/EDC-NHS/Avidin/Biotin-CCP/BSA) can selectively detected Anti-CCP-ab in HS within 10 min. Furthermore, the avidin-biotin bio-recognition system and SAM of MHA-modified ICE surface provided an excellent platform for the detection of rheumatoid biomarker by preserving the bio-activity of the immunogen (B-CCP). Based on the available studies and to best of our knowledge, this is the first report on miniaturized ICE configuration for rheumatoid marker detection in PBS and HS samples. The mechanism of the impedance sensing and schematic representation of the major electrode modification steps are presented in Figure 1 . EIS biosensors provides signal out-put by using periodic small AC perturbations and responds to signal change caused by the binding of bio-analytes to the immobilized biorecognition elements on the electrode surface [38] . Due to these advantages an impedance based biosensor finds a suitable position compared to the other electrochemical transduction mechanisms for developing miniaturized point-of-care-testing (POC) applications. Furthermore, advancements in MEMS has introduced micro-/nanoelectrode's and miniaturized sensing transducers in EIS based transducer platforms for selective, fast and sensitive detection of protein/peptide biomarkers [39, 40] . The MEMS fabrication of an interdigitated chain shaped micro electrode array with a simple electronic circuitry for impedance immunosensing of Anti-CCP-ab provides mass production of electrode arrays with low cost and sample loadings. By considering the collective advantages of aforementioned techniques (SAM, MEMS and EIS), has made the present electrochemical immunosensing strategy competitive with other CCP detection immunosensing techniques.

In the present study, we developed an impedimetric immunosensor by taking the advantage of avidin-biotin interaction systems to attach the cyclic-citrullinated peptide (CCP) on the surface of SAM modified (6-mercaptohexanoic acid) interdigitated chain shaped microelectrode arrays (ICE). As a proof-of-concept, a synthetic peptide (biotin conjugated cyclic-citrullinated peptide; B-CCP) was selected as the bio-receptor to immobilize on the transducer surface for selective detection of the arthritis AAb (Anti-CCP-ab). The change in sensor response upon analyte binding on electrode surface is probed through the electrode interfacial property (charge transfer resistance; Rct) of EIS. The sensor was miniaturized (14 × 3.5 mm) and can be combined to fabricate a portable immunosensing device to detect Anti-CCP-ab for POC testing. The developed immunosensor (ICE/MHA/EDC-NHS/Avidin/Biotin-CCP/BSA) can selectively detected Anti-CCP-ab in HS within 10 min. Furthermore, the avidin-biotin bio-recognition system and SAM of MHA-modified ICE surface provided an excellent platform for the detection of rheumatoid biomarker by preserving the bio-activity of the immunogen (B-CCP). Based on the available studies and to best of our knowledge, this is the first report on miniaturized ICE configuration for rheumatoid marker detection in PBS and HS samples. The mechanism of the impedance sensing and schematic representation of the major electrode modification steps are presented in Figure 1 . The schematic illustration of the electrode surface modification with MHA-SAM, EDC-NHS coupling chemistry for avidin immobilization, avidin-biotin bio-recognition system for synthetic peptide (CCP) binding on electrode surface as bio-receptor, BSA binding on electrode surface to prevent non-specific binding of the bio-analyte of interest (Anti-CCP-ab) (b). Mechanism of EIS sensing of rheumathritis biomarker, Anti-CCP-ab in [Fe(CN) 6 3−/4− ] electrolyte probed through the sensitive changes in electrode interfacial property (R ct ) upon bio-analyte binding on the modified electrode surface (c). 

Biotin-labelled cyclic citrullinated peptide (Biotin-CCP) (4166 IU/mL) (Peptide sequence: Biotin-HQCHQEST-Cit-GRSRGRCGRSGS-COOH) with a disulfide bond between the Cyc3 and Cyc16 residues was procured from Peptron Inc. (Daejon, South Korea). Anti-cyclic citrullinated peptide antibody (Anti-CCP-ab) (4160 IU mL −1 ) was procured from Bioss Antibodies Inc. (Woburn, Massachusetts, USA.). 6-Mercaptohexanoic acid (MHA), Hemoglobin, Potassium ferrocyanide (K 4 [Fe(CN) 6 ]·3H 2 O), potassium ferricyanide (K 3 [Fe(CN) 6 ]), 1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide (EDC), N-Hydroxysuccinimide (NHS), Avidin from egg white (≥10 Units/mg protein, ≥98%), Bovine serum albumin (BSA), and human serum were purchased from Sigma-Aldrich (USA). Anti-Interferon-γantibody (Anti-IFN-γ-ab), Anti-insulin-antibody (Anti-insulin-ab), IgM-Rheumatoid factor (IgM-RF), Anti-C-reactive-protein-antibody (Anti-CRP-ab), Human-Immunoglobulin-G-antibody (Human-IgG-ab) were procured from Abcam (Cambridge, UK). Phosphate buffered saline (PBS-137 mM NaCl, 2.7 mM KCl, 4.3 mM Na 2 HPO 4 , and 1.4 mM KH 2 PO 4 ; pH 7.4) and 1 × PBS containing 0.05% Tween 20 were procured from Tech and Innovation (Gangwon, South Korea). All solutions were prepared using deionized water (DI; 18.2 MΩ cm) from Purescience (Jungwon, South Korea). All other chemicals were of analytical reagent grade and are used without any further purification.

X-ray photoelectron spectroscopy (XPS) elemental surface analysis was carried out using a PHI 5000 Versa Probe (Ulvac-PHI) spectrometer (Japan) with monochromator A1 Kα (1486.6 eV). Survey scan was first recorded and then region scans were measured for the S(2p) and C(1s) photoelectron binding energy regions. A 50 eV band pass energy, 1 eV step size and 200 µm × 200 µm X-ray spot size were used for measuring survey scan (range = 1200 to −5 eV). For C1s and S2p region scans a pass energy of 20 eV and 0.1 eV step size were used. All the region scans were fitted by a standard Gaussian curve fit with Shirley background subtraction [41] . Atomic force microscopy (AFM) measurements were obtained on an ambient air scanning probe microscope (XE-100 Park systems, South Korea). A typical non-contact mode was used to record the images using the XEP software. The scanning region was approximately 2 × 2 µm 2 , with a resolution of 0.05 nm and scan rate of 0.5 Hz. The surface morphology and composition of elements were investigated using scanning electron microscopy (Hitachi S-4700 (Japan) with an operating accelerated voltage of 15 kV and energy dispersive X-ray.

Cyclic voltammetry (CV) was carried out in a three-electrode configuration (Compact-Stat potentiostat, Eindhoven, Netherlands) consisting of a working electrode (WE) (bare and modified ICEs), a counter electrode (CE) (Platinum coil), and a reference electrode (RE) (Ag/AgCl). The cyclic voltammograms (CVs) were carried out in 5 mM [Fe(CN) 6 ] 3− in 1 × PBS (10 mM, Phosphate buffered saline) (pH 7.4), at a sweep rate of 50 mV s −1 within a potential range of −0.2 V to +0.5 V vs. Ag/AgCl external RE. The electrochemical impedance spectroscopy (EIS) measurements were carried out in 5 mM [Fe(CN) 6 ] 3− / 4− (1:1) in 1 × PBS, at room temperature (RT) (24 • C) using a two-electrode setup. The spectra were measured by selecting an alternating current perturbation voltage with a root mean square value of 0.05 V in a frequency range of 0.1 Hz-1 MHz and three points were collected for a decade of frequency. The measured impedance spectra were fitted by using a suitable equivalent circuit model consisting of solution resistance (R s ), electrode interfacial capacitance (CPE) and charge transfer resistance (R ct ). The fitting of the EIS spectra was carried out by ZView-a non-linear curve fitting software from Scribner Associates Inc. (Southern Pines, NC, USA). 

A gold (Au) based ICE array was fabricated on a glass slide substrate (14 × 3.5 × 0.5 mm 3 ). The conductive Titanium and Au (thickness: 25 and 50 nm, respectively) layers were deposited by an electron beam evaporator. Subsequently, a pair of conductive pads and interdigitated chain shaped electrode fingers, consisting of 5 µm spacing and width for WE and CE/RE were developed by the lift-off process. For measuring electrochemical impedance spectra, a polystyrene cell culture plate (96-well) with 400 µL volume capacity was used as an electrolyte reservoir. A homemade adapter was fabricated to connect the WE and CE/RE conductive pads of ICE to the potentiostat.

The ICE electrode array was washed with successive solutions of ethanol (99.5%), and water for 2 min via ultra-sonication and purged under N 2 gas to remove surface bound impurities. The SAM was immobilized on the electrode surface by incubating the electrodes in 50 mM MHA prepared in 99.5% ethanol for overnight (12 h) at room temperature. The MHA modified electrode was rinsed with pure ethanol followed by DI water to remove loosely bound thiol moieties. Additional rinsing was carried out to remove the H-bonded thiol moieties by sonicating the electrode in absolute ethanol for 2 min. After sonication, the electrodes were washed with DI water dried under low stream of N 2 gas. The terminal -COOH groups of the MHA-SAM modified electrode was activated by EDC (75 mM)/NHS (5 mM) solution (30 min incubation at room temperature) for Biotin-CCP binding. The EDC-NHS activated electrodes were washed by 1 × PBS followed by DI water. 10 µL of 100 µg mL −1 of avidin was dropped onto the surface of MHA/EDC-NHS electrode and incubated for 1 h in the humid chamber to prevent drying of the electrode surface. The avidin was immobilized covalently by a coupling reaction between the -NH 2 group of the avidin and the EDC-NHS activated MHA moieties on the electrode surface. After avidin immobilization the electrodes were washed with 1 × PBS to remove the loosely bound avidin. 10 µL of 50 µg mL −1 of Biotin-CCP was dropped on the electrode surface and incubated in humid chamber for 30 min. The Biotin-CCP added is immobilized on the electrode surface through avidin-biotin bio-recognition system. The electrodes (ICE/MHA/EDC-NHS/Avidin-Biotin-CCP) formed were washed with 1 × PBS to remove any unbound Biotin-CCP. Subsequently the electrodes were washed with 1 × PBS buffer containing 0.05% Tween-20 and 0.5% BSA for 2 min to prevent the non-specific binding of the target protein, thus forming ICE/MHA/EDC-NHS/Avidin/B-CCP/BSA bio-electrode.

The Energy dispersive x-ray spectroscopy analysis (EDX) were performed to confirm the atomic ratios and elemental composition of the modified electrodes (SEM/EDX), by carrying out measurements over the randomly selected areas. The EDX of the bare ICE surface shows almost Au (due to 50 nm Au coating) and minor amounts of Si, O and C (due to the underlying glass substrate) ( Figure S1a ). The elemental composition of the ICE/MHA shows major quantities of C, O (due to the MHA functionalization) and Au stemming from gold substrate, and minor quantities of S from MHA-SAM ( Figure S1b ). AFM topography images were recorded to study the surface morphology of the electrode functionalized with MHA-SAM. Figure 2a shows the polycrystalline surface of the bare gold ICE surface with an average roughness of 3.753 nm. The electrode modified with MHA-SAM was changed into a smooth topography and homogenous aligned structure with an average roughness of 1.18 nm when compared to the bare ICE ( Figure 2b ). The results demonstrate the successful modification of bare ICE electrode surface with MHA-SAM.

peak fitting components are shown in Figure 2c ,d. Binding energies (BEs) of carbon (C1s) are observed at 285.01 eV, 287.22 eV and 281.24 eV (Figure 2c ). The main peak detected at 285.01 eV correlates to the adventitious carbon. The shoulder peak at 287.22 eV is ascribed to the O − C = O functional group. The peak at BEs 281.24 eV endorsed to Au-C interaction [42] . All the peaks were normalized by shifting of the C-C peak to 285 eV. The S2p deconvolution region scans show a distinct peak at 161.70 eV corresponding to the Au-S interaction in the ICE/SAM surface [43] . 

The optimization of the electrochemical response is a critical factor to obtain the best sensor performance in terms of linear range, detection limit and sensitivity. The experimental conditions such as Biotin-CCP concentration (5, 10, 25, 50, 75, 100 and 125 μg mL −1 ), Biotin-CCP incubation time (10, 20, 30, 40 , 50 and 60 min) and pH (5.4, 6.4, 7.4, 8.4, 9.4) and immunoreaction incubation time (1, 2, 5, 10, 15, 20, 25 and 30 min) of the sensor were optimized, by maintaining the concentration of Anti-CCP-ab as constant (20 IU mL −1 ). In Figure 3a , the sensor was optimized for B-CCP concentration by adding the various concentrations of B-CCP (5 μg mL −1 → 125 μg mL −1 ) for sensor fabrication. The impedance To analyse the SAM functionalization on the ICE surface, elemental dispersive X-ray and elemental mapping analysis was performed on the ICE/MHA electrodes. The survey spectrum for ICE/MHA electrodes show peaks corresponding to C, S and Au ( Figure S2 ). The high-resolution region scans of C1s and S2p for ICE/MHA along with the respective peak fitting components are shown in Figure 2c ,d. Binding energies (BEs) of carbon (C1s) are observed at 285.01 eV, 287.22 eV and 281.24 eV (Figure 2c ). The main peak detected at 285.01 eV correlates to the adventitious carbon. The shoulder peak at 287.22 eV is ascribed to the O−C=O functional group. The peak at BEs 281.24 eV endorsed to Au-C interaction [42] . All the peaks were normalized by shifting of the C-C peak to 285 eV. The S2p deconvolution region scans show a distinct peak at 161.70 eV corresponding to the Au-S interaction in the ICE/SAM surface [43] .

The optimization of the electrochemical response is a critical factor to obtain the best sensor performance in terms of linear range, detection limit and sensitivity. The experimental conditions such as Biotin-CCP concentration (5, 10, 25, 50, 75, 100 and 125 µg mL −1 ), Biotin-CCP incubation time (10, 20, 30, 40 , 50 and 60 min) and pH (5.4, 6.4, 7.4, 8.4, 9.4) and immunoreaction incubation time (1, 2, 5, 10, 15, 20, 25 and 30 min) of the sensor were optimized, by maintaining the concentration of Anti-CCP-ab as constant (20 IU mL −1 ). In Figure 3a , the sensor was optimized for B-CCP concentration by adding the various concentrations of B-CCP (5 µg mL −1 → 125 µg mL −1 ) for sensor fabrication. The impedance change (∆R ct ) of the developed sensors increased as the B-CCP loading on the electrode surface is increased from 5.0 to 50 µg mL −1 , whereas no significant change in the sensor response was detected over 50 µg mL −1 , due to electrode saturation effect. Hence, a concentration of 50 µg mL −1 B-CCP was selected for the later experiments. The optimum B-CCP incubation time for total immobilization of the synthetic peptide was optimized by incubating the B-CCP attached electrode for different time intervals (10 min → 60 min). The impedance signal linearly increased with increase in the B-CCP incubation time up to 30 min, whereas the electrode response was saturated over 30 min of the B-CCP incubation suggesting a 30 min B-CCP incubation is optimum for the sensor fabrication ( Figure 3b ). In case of pH value optimization, the sensor response is measured in different pH buffers ranging from (pH 5.4 → pH 9.4). The change in impedance (∆R ct ) increases with rise in pH value till 7.4, and decreases with the increase in pH value, suggesting that the optimal pH for immunoreaction is 7.4 ( Figure 3c ). However, at extreme acidic or alkaline pH conditions the proteins tend to denature and aggregate. The optimization of the immunoreaction incubation time between Biotin-CCP and Anti-CCP-ab was carried out for different time periods (1 → 30 min). The ∆R ct increases with rise in immunoreaction incubation time till 10 min, and the signal is not significantly increased above the 10 min of Anti-CCP-ab incubation, demonstrating that the optimum incubation time for the immunoreaction is 10 min (Figure 3d ). In precise the optimized sensor conditions are a pH value of 7.4, 50 µg mL −1 of B-CCP concentration, a 30 min B-CCP incubation time and a 10 min Anti-CCP-ab incubation time.

change (ΔRct) of the developed sensors increased as the B-CCP loading on the electrode surface is increased from 5.0 to 50 μg mL −1 , whereas no significant change in the sensor response was detected over 50 μg mL −1 , due to electrode saturation effect. Hence, a concentration of 50 μg mL −1 B-CCP was selected for the later experiments. The optimum B-CCP incubation time for total immobilization of the synthetic peptide was optimized by incubating the B-CCP attached electrode for different time intervals (10 min → 60 min). The impedance signal linearly increased with increase in the B-CCP incubation time up to 30 min, whereas the electrode response was saturated over 30 min of the B-CCP incubation suggesting a 30 min B-CCP incubation is optimum for the sensor fabrication ( Figure  3b ). In case of pH value optimization, the sensor response is measured in different pH buffers ranging from (pH 5.4 → pH 9.4). The change in impedance (ΔRct) increases with rise in pH value till 7.4, and decreases with the increase in pH value, suggesting that the optimal pH for immunoreaction is 7.4 (Figure 3c) . However, at extreme acidic or alkaline pH conditions the proteins tend to denature and aggregate. The optimization of the immunoreaction incubation time between Biotin-CCP and Anti-CCP-ab was carried out for different time periods (1 → 30 min). The ΔRct increases with rise in immunoreaction incubation time till 10 min, and the signal is not significantly increased above the 10 min of Anti-CCP-ab incubation, demonstrating that the optimum incubation time for the immunoreaction is 10 min (Figure 3d ). In precise the optimized sensor conditions are a pH value of 7.4, 50 μg mL −1 of B-CCP concentration, a 30 min B-CCP incubation time and a 10 min Anti-CCP-ab incubation time. The electrode interfacial property (charge-transfer resistance: R ct ) was obtained by fitting the measured EIS spectra to an equivalent-circuit model (ZView; Scribner Associates Inc., Southern Pines, USA) as shown in Figure 4d . The EIS spectra of the bare ICE surface (Figure 4a , curve i) displays a small semicircle with R ct of 15640 Ω, which is characteristic for a bare gold electrode with no diffusional limiting process at lower frequencies, which is an additional benefit of the developed ICE microelectrodes. The diameter of the semicircle was substantially increased with a R ct of 978,900 Ω, due of the surface modification of ICE with mercaptohexanoic acid (Figure 4a, curve ii) , suggesting that the alkanethiol film created an electrical hindrance for the electrons transfer between the [Fe(CN) 6 ] 3− / 4− redox probe and the electrode surface. The semicircle diameter was significantly decreased with a R ct of 86,520 Ω (Figure 4a, curve iii) , after the EDC-NHS carbodiimide coupling reaction with the terminal -COOH of MHA-SAM, suggesting that formation of succinimide ester on the SAM modified electrode surface facilitating the fast electron transfer between the electrode and the interface. The semicircle diameter is slightly increased (R ct : 120,400 Ω) with the linking of avidin on the SAM surface, due to the development of electron-blocking layer on the ICE surface by successful immobilization of avidin (Figure 4a , curve iv). The ICE/MHA/EDC-NHS/B-CCP impedance spectrum shows an increase in diameter of semicircle with a R ct of 197,400 Ω (Figure 4a , curve v) due to the formation of electron transfer obstruction layer on the electrode surface by the immobilization of B-CCP synthetic peptide, which is a highly non-conductive biological material. The rinsing of the electrode with 1 × PBS buffer containing 0.05% Tween-20 and 0.5% BSA for 2 min has again increased (R ct : 265,500 Ω) the diameter of the semicircle (Figure 4a , curve vi), due to the binding of BSA on ICE surface to prevent non-specific binding of the Anti-CCP-ab onto the ICE surface. Figure 4a curve vii shows a great increase in diameter of the semicircle (R ct : 421,700 Ω) when incubated with the Anti-CCP-ab for 10 min, suggesting the binding of analyte with the target and results in decrease in electron transfer rate by formation of ferrocyanide transport obstruction layer between the electrode surface and the electrolyte. The measured impedance spectra are consistent with the CV results (Figure 4c ) demonstrating that the B-CCP has bound to the covalently attached avidin and the ICE/MHA/EDC-NHS/B-CCP/BSA immunosensor is successfully developed. Table 1 summary of the extrapolated fitting results of the measured EIS spectra for the circuit elements shown in Figure 4d . Table 1 . EIS parameters of the bare and modified ICEs extrapolated by fitting the measured spectra to the equivalent circuit model shown in Figure 3d . 

The binding of Anti-CCP-ab on the modified ICE surface and change in the electrode interfacial impedance was sensitively detected through impedimetric measurements of the electrodes in a frequency range of 0.1 Hz to 1 MHz. The change is impedance was detected by fitting the measured spectra to an equivalent circuit model (Figure 3d) , where the changes in electrode interfacial impedance is calculated in terms of Chargetransfer resistance (R ct ). The developed Anti-CCP-ab immunosensor was well characterized by measuring the changes in R ct , which represents the resistance of the electrode at lower frequencies. The results suggest that the change in R ct of the modified ICE electrode upon anti-CCP-ab addition is a critical factor for the quantitative determination of AAb in PBS and HS. Hence, the R ct was measured for a range of Anti-CCP-ab concentrations (0.1 IU mL −1 → 800 IU mL −1 ) on the modified electrode. The sensor response was represented as change in R ct denoted as ∆R ct . The ∆R ct was calculated by using the formula ∆R ct = (R a − R 0 )/R 0 ; where R a and R 0 are the R ct of the modified electrode in the presence and absence of the analyte respectively. To assess the electrode response to Anti-CCP-ab addition, the developed ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was incubated with different concentrations of Anti-CCP-ab prepared in 1 × PBS for 10 min. The impedance measurements were then carried out in 5 mM [Fe(CN) 6 −3/-4 ] (1:1) redox probe prepared in 1× PBS. As shown in Figure 5a , the R ct values linearly increased with increasing Anti-CCP-ab concentration. The ∆R ct was also proportionate to the linear increase in Anti-CCP-Ab concentrations on the electrode over a range of 1 IU mL −1 → 800 IU mL −1 (Figure 5b) . The regression equation for the sensor response in PBS was ∆R ct = 0.5060 + 0.00313*C anti-ccp-ab(PBS) with a correlation coefficient of 0.9986 (Figure 5b ). 

The binding of Anti-CCP-ab on the modified ICE surface and change in the electrode interfacial impedance was sensitively detected through impedimetric measurements of the electrodes in a frequency range of 0.1 Hz to 1 MHz. The change is impedance was detected by fitting the measured spectra to an equivalent circuit model (Figure 3d) , where the changes in electrode interfacial impedance is calculated in terms of Charge-transfer resistance (Rct). The developed Anti-CCP-ab immunosensor was well characterized by measuring the changes in Rct, which represents the resistance of the electrode at lower frequencies. The results suggest that the change in Rct of the modified ICE electrode upon anti-CCP-ab addition is a critical factor for the quantitative determination of AAb in PBS and HS. Hence, the Rct was measured for a range of Anti-CCP-ab concentrations (0.1 IU mL -1 → 800 IU mL -1 ) on the modified electrode. The sensor response was represented as change in Rct denoted as ΔRct. The ΔRct was calculated by using the formula ΔRct = (Ra − R0)/R0; where Ra and R0 are the Rct of the modified electrode in the presence and absence of the analyte respectively. To assess the electrode response to Anti-CCP-ab addition, the developed ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was incubated with different concentrations of Anti-CCP-ab prepared in 1 × PBS for 10 min. The impedance measurements were then carried out in 5 mM [Fe(CN)6 -3/-4 ] (1:1) redox probe prepared in 1× PBS. As shown in Figure 5a , the Rct values linearly increased with increasing Anti-CCP-ab concentration. The ΔRct was also proportionate to the linear increase in Anti-CCP-Ab concentrations on the electrode over a range of 1 IU mL -1 → 800 IU mL -1 (Figure 5b) . The regression equation for the sensor response in PBS was ΔRct = 0.5060 + 0.00313*Canti-ccp-ab(PBS) with a correlation coefficient of 0.9986 (Figure 5b ). Moreover, the calculated limit of detection (LOD) of the sensor was 60 mIU mL −1 (S/N = 3). The LOD was calculated by using an expression (3*SE/slope) [44] . where SE is calculated by dividing the standard deviation of the blank, by the square root of the number of blank observations [40] and slope is the sensitivity of the calibration curve. The sensor shows a LOD of 0.6 IU mL −1 (PBS). The EIS response studies clearly shows that R ct increased linearly with step wise increase of Anti-CCP-ab concentration on the electrode surface. The effect can be explained by the formation of a kinetic barrier for the transfer of electrons due to the step-wise increase in the concentration of Anti-CCP-ab, which binds to the immobilized B-CCP on the SAM modified ICE surface. The ∆R ct of the modified ICE electrode was adopted as a parameter for the quantification of the sensor signal to detect Anti-CCP-ab via specific immunoreactions on the electrode surface. In this fashion, the developed bio-electrode established a proof-of-concept for the direct and label-free detection of Anti-CCP-ab without further amplification of the electrical signal. The immunosensor displayed a good dynamic ranges and detection limits in comparison to the other Anti-CCP-ab biosensors reported in the past decade ( Table 2 ). In order to construct a good linear calibration curve and to avoid the matrix effects a dilute human serum solution (1% v/v) in 1 × PBS buffer was prepared. HS containing different concentrations of Anti-CCP-ab were loaded on to the modified ICE electrode surface and incubated for 10 min in a humid chamber to react with B-CCP immobilized on the electrode surface. After incubation with HS containing different concentrations of AAb, impedance spectra were measured in 5 mM [Fe(CN) 6 −3/−4 ] electrolyte solution. In comparison to the blank electrode, HS (anti-CCP-ab) added electrode impedance was increased with linear increase in concentration of analyte (Figure 5c ). The ∆R ct was also proportionate to the linear increase of Anti-CCP-ab concentration over a range of 0.1 IU mL −1 → 800 IU mL −1 . The regression equation for sensor response in HS was ∆R ct = 0.3877 + 0.00192*C anti-ccp-ab(HS) with a correlation coefficient of 0.9983 (Figure 5d ). Moreover, the calculated limit of detection (LOD) of the sensor was 0.82 IU mL −1 (S/N = 3). The impedance signal measured with HS samples are dependent on concentration of Anti-CCP-ab. The calibration curve constructed for determination of Anti-CCP-ab in HS is used for analysis of real samples.

The interference of the ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode is studied by measuring the impedance signal in the presence and absence of different proteins co-exist in the HS. The interfering proteins selected for the study are Anti-IFN-γ-ab (100 pg mL −1 ), Anti-insulin-ab (200 pg mL −1 ), IgM-RF (50 IU mL −1 ), Anti-CRP-ab (200 pg mL −1 ), Human-IgG-ab (100 pg mL −1 ), Hemoglobin (15 mg mL −1 ), Anti-CCP-ab (10 IU mL −1 ). The con-centration of the interferents selected is two folds greater than the expected concentration levels of the healthy individuals. These interferents prepared in 1 × PBS are added to the ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode separately and electrode response is obtained in a frequency range of 0.1 Hz-1 MHz. Figure 6a shows that no significant interference was detected in the determination of Anti-CCP-ab in the presence of the selected interring agents. The results established that the high specificity of the immobilized B-CCP synthetic peptide used for the detection of the target analyte and a good selectivity of the electrochemical impedance transducer at the optimized experimental conditions. IgG-ab (100 pg mL -1 ), Hemoglobin (15 mg mL -1 ), Anti-CCP-ab (10 IU mL -1 ). The concentration of the interferents selected is two folds greater than the expected concentration levels of the healthy individuals. These interferents prepared in 1 × PBS are added to the ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode separately and electrode response is obtained in a frequency range of 0.1Hz-1MHz. Figure 6a shows that no significant interference was detected in the determination of Anti-CCP-ab in the presence of the selected interring agents. The results established that the high specificity of the immobilized B-CCP synthetic peptide used for the detection of the target analyte and a good selectivity of the electrochemical impedance transducer at the optimized experimental conditions.

The freshly prepared ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was stored in 1 × PBS at 4 °C and the impedance signal was measured as a function of time. The stability of the developed ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was assessed by measuring the Rct at a regular intervals of 5 days for 20 days. Figure 6b shows that the developed bioelectrode retained ~98.5% of its activity at the end of 20 days. 

Reproducibility is an important factor for the potential application of the immunosensor in clinical diagnostics. Thus, the reproducibility of the fabricated ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was verified by sensing Anti-CCP-ab (10 IU mL -1 ) on three independently prepared ICE/MHA/EDC-NHS/B-CCP/BSA bio-electrodes. The RSD calculated for the three measurements was 1.52%, suggesting that the fabricated immunosensor shows an acceptable reproducibility. The reproducibility for the three different ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode (R0) was also verified in 1 × 

The freshly prepared ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was stored in 1 × PBS at 4 • C and the impedance signal was measured as a function of time. The stability of the developed ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was assessed by measuring the R ct at a regular intervals of 5 days for 20 days. Figure 6b shows that the developed bioelectrode retained~98.5% of its activity at the end of 20 days.

Reproducibility is an important factor for the potential application of the immunosensor in clinical diagnostics. Thus, the reproducibility of the fabricated ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode was verified by sensing Anti-CCP-ab (10 IU mL −1 ) on three independently prepared ICE/MHA/EDC-NHS/B-CCP/BSA bio-electrodes. The RSD calculated for the three measurements was 1.52%, suggesting that the fabricated immunosensor shows an acceptable reproducibility. The reproducibility for the three different ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode (R 0 ) was also verified in 1 × PBS, and the results demonstrated a RSD of 1.02%. A very good reproducibility and stability is endorsed due to a robust Avidin-Biotin interaction system and covalent immobilization of avidin molecules on the gold surface, which created a bio-compatible substrate and prevents the removal of bio-receptors from the modified ICE surface. moreover, the presented impedimetric interdigitated microelectrode array sensor shows several advantages compared to the other reported methods for CCP detection. The developed assay (a) is label-free, (b) mass production of ICE at low cost, (c) no Warburg diffusion at lower frequencies, (d) requirement of low sample volumes (10 µL), (e) low-cost sample preparation, (f) a low assay time and (e) direct signal readout in the form of an electrical signal.

To validate the practical application of the developed ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode, Anti-CCP-ab was quantified in spiked HS samples. The analysis was carried out by spiking five different concentrations of Anti-CCP-ab (1.0, 10, 20, 50 and 500 IU mL −1 ) into 1% v/v PBS diluted HS samples. The HS samples spiked with bioanalyte were loaded onto the developed ICE/MHA/EDC-NHS/B-CCP/BSA bio-electrode. Three different measurements for each concentration was obtained and the average of three measurements was calculated and the recovery rates with the %RSD was tabulated. In Table 3 , the measured Anti-CCP-ab concentration in spiked human serum samples using the developed immunosensor was found to be 0.98, 9.95, 19 .98, 50.59 and 499.02 IU mL −1 . The calculated recoveries are 98.0% (n = 3), 99.9% (n = 3), 99.5% (n = 3), 101.18% (n = 3) and 99.80 (n = 3), respectively. The results suggest that the biosensor shows a good recovery rate for the five samples with no significant variation between the spiked and the found Anti-CCP-ab concentrations. Thus, the ICE/MHA/EDC-NHS/B-CCP/BSA bioelectrode fabricated can be potentially used for the accurate quantification of the Anti-CCP-ab's in the real samples. 

Miniaturized electrochemical impedance immunosensor based on Interdigitated microelectrode array for selective detection of Anti-CCP-ab was developed through a simple Biotin-Avidin recognition system. The avidin is attached on the ICE surface by modification of electrode with MHA-SAM and the functionalization of the ICE with SAM is characterized through AFM, EDX, CV, XPS, EIS. SAM provided a bio-compatible environment to attach and preserve the bio-activity of the B-CCP. The Avidin-Biotin recognition system provided significant stability to the CCP bound onto the electrode surface. The sensor is successfully validated as an impedimetric biosensor for the quantification of Anti-CCP-Ab in PBS and HS. The biosensor showed a linear range of 1 IU mL −1 → 800 IU mL −1 and a detection limit of 0.60 IU mL −1 (PBS). Additionally, the microscale design of the sensor (3.5 × 14 mm) enabled the ICE to easily assemble with a portable-potentiostat making the bio-electrode suitable for POC testing. The fabricated bioelectrode is economical and feasible for mass production and the detection has not required any fluorophores. It sensor can applied for detection of arthritis AAb (Anti-CCP-ab) in individuals at early stages of disease development.

Supplementary Materials: The following are available online at https://www.mdpi.com/1424 -8220/21/1/124/s1, Figure S1 . Energy dispersive x-ray spectroscopy of the bare ICE and the 6-Mercaptohexanoic acid modified ICE surface; Figure S2 . X-ray photoelectron spectroscopy survey spectra of the 6-mrcaptohexanoic acid functionalized on the electrode surface. 

No new data were created or analyzed in this study. Data sharing is not applicable to this article.

The authors declare no conflict of interest.

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