Table of Contents Author Guidelines Submit a Manuscript
Biochemistry Research International
Volume 2016, Article ID 1545206, 11 pages
Research Article

Fabrication and Optimization of ChE/ChO/HRP-AuNPs/c-MWCNTs Based Silver Electrode for Determining Total Cholesterol in Serum

1Centre for Biotechnology, Maharshi Dayanand University, Rohtak, Haryana 124001, India
2Department of Bio & Nano Technology, Guru Jambheshwar University of Science & Technology, Hisar, Haryana 125001, India

Received 12 October 2015; Accepted 20 December 2015

Academic Editor: Hans-Jürgen Apell

Copyright © 2016 Kusum Lata et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.


The developed method used three enzymes comprised of cholesterol esterase, cholesterol oxidase, and peroxidase for fabrication of amperometric biosensor in order to determine total cholesterol in serum samples. Gold nanoparticles (AuNPs) and carboxylated multiwall carbon nanotubes (cMWCNTs) were used to design core of working electrode, having covalently immobilized ChO, ChE, and HRP. Polyacrylamide layer was finally coated on working electrode in order to prevent enzyme leaching. Chemically synthesised Au nanoparticles were subjected to transmission electron microscopy (TEM) for analysing the shape and size of the particles. Working electrode was subjected to FTIR and XRD. The combined action of AuNP and c-MWCNT showed enhancement in electrocatalytic activity at a very low potential of 0.27 V. The pH 7, temperature 40°C, and response time of 20 seconds, respectively, were observed. The biosensor shows a broad linear range from 0.5 mg/dL to 250 mg/dL (0.01 mM–5.83 mM) with minimum detection limit being 0.5 mg/dL (0.01 mM). The biosensor showed reusability of more than 45 times and was stable for 60 days. The biosensor was successfully tested for determining total cholesterol in serum samples amperometrically with no significant interference by serum components.

1. Introduction

With increasing mortality rate due to cardiovascular diseases (CVDs) in present scenario, it is necessary to develop more advanced methods for diagnosis. These advanced diagnostic methods should sense the disease at an early stage and prevent it from being fatal. Cholesterol is considered as risk factor when the blood cholesterol is above the normal level and so causes the risk of cardiovascular disease (CVD) [1]. In addition, high blood pressure or diabetes may also increase the risk even more. Elevated level of cholesterol in blood is one of the factors responsible for coronary artery disease, hypertension, nephritic syndrome or cirrhosis, atherosclerosis, heart attack, and stroke [2]. When too much of cholesterol circulates in the blood, it slowly builds up layer inside the inner walls of the arteries which makes them narrow and less flexible [2].

There are several methods such as calorimetric method [3], liquid/gas chromatographic method, HPLC, spectrophotometric methods, and thermistor based assays used to determine cholesterol concentration [48]. The above methods are fast, accurate, and sensitive but suffer from limitations: they require trained manpower, they require sample pretreatment, a lot of time is required, and they are only confined to laboratory lacking on-site monitoring. A promising alternate to these methods is a biosensor which is able to determine the cholesterol more rapidly and to a more sensitive level with a plus point of portability [9]. The biosensor assembly comprised three components: biorecognition layer (enzyme in this case) which specifically interacts with analyte and generates the biological response, a transducer which senses these responses and processes the biological response to a measurable signal, and a display unit which is the third component. Transducers are an important part of assembly of biosensor in determining accuracy and sensitivity [10]. Immobilizing ChO on various supports helps in directly determining concentration of cholesterol in different samples. As serum cholesterol is present in the form of ester, in order to determine total cholesterol, ChE is required along with ChO. Cholesterol esterase first hydrolyses the esterified cholesterol and is further oxidized by cholesterol oxidase for producing cholest-4-en-3-one and hydrogen peroxide (H2O2). In amperometric biosensors electric potential is applied on H2O2 which get oxidized to produce electrons and the flow of electrons produces current. The current generated is directly proportional to cholesterol concentration in serum:A new approach to reduce interference is the use of horseradish peroxidase (HRP). HRP has redox centre associated with ferroheme/ferriheme pair. Conversion of reduced state to oxidized state is done through direct transfer of electrons. In its 3D configuration HRP has heme group present in outer region which enhances the direct transfer of electrons between redox centre and conducting sites present on transducer [11]. Regeneration of HRP is done via direct electron transfer: Immobilizing enzyme on suitable support may lower the Michaelis constant or it may enhance bimolecular rate constant, which improves the biosensor performance [1215]. Cholesterol hydrolysing enzymes ChO and ChE have been immobilized on conducting polymers [16] like polypyrrole films [17], PVC Strip [18], PB/polypyrrole (PPy) composite film [19], cellulose acetate/carbon electrode [20], cellulose acetate/Pt electrode [21], electropolymerised PPy films [22], poly 3-thiopheneacetic acid film/Pt electrode [23] and PANI–pTSA-Ag/ITO [11], and sol-gel films [24]. Evolution of nanoscale materials has revolutionised the field of biosensors also. The nanoscale dimensions, their graphitic surface chemistry, and electrocatalytic properties of carbon nanotubes make them an interesting material for sensing purpose. Single and multiwalled carbon nanotubes [25, 26], MWCNTs [27], CNT-chitosan/GCE [28], Fe3O4-SiO2/MWCNT [29], graphene modified graphite electrode [30], graphene/Pt NPs [31], Pt/Au ZnO nanorods [32], NSPANI-AuNP-GR/ITO [33], AuNPs/Au electrode [34], graphite-teflon matrix [35], and Pt-Pd bimetallic nanoparticle decorated grapheme [36] are some of the supports which have been used for the transduction of generated biological signals to electrical signals for cholesterol determination. PVC has also been used to immobilize cholesterol hydrolysing enzymes. ChO and ChE were covalently immobilised on surface of PVC beaker which act as reaction cell and HRP was incorporated in carbon electrode [37].

In the present method, the combination of three enzymes was used for the development of electrochemical biosensor by immobilization of three enzymes (ChO, ChE, and HRP) on AuNPs and c-MWCNT based electrode for determining cholesterol in serum cholesterol.

2. Materials and Methods

2.1. Chemicals and Reagents

Cholesterol esterase was purified from Pseudomonas species (165.8 Units/g); 4-amino-phenazone, Triton X-100, cholesteryl acetate, and carboxylated multiwalled carbon nanotubes (c-MWCNTs) were purchased from Sigma Chemical Co., USA. Cholesterol oxidase from Streptomyces sp. (500 units/10 mg) and horseradish peroxidase (HRP) (80 U/mg) were obtained from SISCO Research Laboratory Pvt. Ld., Mumbai. Silver wire was purchased from local market. All other chemicals used during the experimentation were of analytical grade. Gold nanoparticles (AuNPs) were synthesised at Centre for Biotechnology, Maharshi Dayanand University, Rohtak.

2.2. Instrumentation

Potentiostat (PSTAT mini 910, Metrohm, Switzerland) was used for all electrochemical studies. Ultrasonication was done with Chrom Tech Ultrasonic Liquid Processor. For TEM JEM-2100F microscope (AIRF, JNU, New Delhi) was used; Varian 7000 FTIR spectrometer (AIRF, JNU, New Delhi) was used for performing Fourier transform infrared (FTIR) spectroscopy. X-ray diffraction (XRD) facility for gold nanoparticles and c-MWCNTs was provided by Department of Physics, M.D. University, Rohtak. Shimadzu corporation UV 2450 spectrophotometer was used for spectrophotometric measurement at Centre for Biotechnology.

2.3. Synthesis of Gold Nanoparticles

Chemical synthesis of gold nanoparticles was done using citrate reduction method [38]. 100 mL of 0.001% gold chlorous acid (HAuCl4) was boiled at 97°C with continuous stirring using magnetic stirrer. Then, the 1% sodium citrate solution was added; within 4 to 5 min solution turns wine red and was further heated for 4 to 5 min and then cooled down at room temperature. Finally centrifuged pellets were dried for further use. Transmission electron microscopy (TEM) of the synthesised AuNPs was done on commercial basis at AIRF, JNU, New Delhi, for the confirmation of shape of newly synthesised nanoparticles and size range of particles.

2.4. Fabrication of ChE/ChO/HRP-AuNPs/c-MWCNT Modified Silver Working Electrode

Fabrication strategy of working electrode comprised mixing c-MWCNTs and gold nanoparticles (AuNPs) in paraffin oil in fixed proportion until a consistent paste is obtained. A plastic hollow tube (3 cm × 4 mm) was filled with the nanomaterial passed obtained above. The silver (Ag) wire was cleaned with ethanol and ddH2O by sonication and then inserted in the paste filled tube for achieving the electrical contact. Then the above electrode was allowed to dry and then immersed in a mixture of ChO, ChE, and HRP solution for 2 hrs, so that the enzyme can bind on electrode surface. The carboxyl (COOH) group present on MWCNTs forms amide bond with the amino group present on the enzyme leading to the formation of covalent bond. Then, the electrode surface was covered with a thin film of polyacrylamide (PAA) which helps in preventing enzyme from leaching.

2.5. Characterisation of Carbon Based Working Electrode

The nanomaterial based core of working electrode (AuNPs/c-MWCNTs/Ag electrode) and enzyme bound electrode (ChE/ChO/HRP-AuNP/c-MWCNTs/Ag electrode) were characterised using Varian 7000 FTIR spectrometer (at AIRF, JNU, New Delhi); before coating with PAA Fourier transform infrared (FTIR) spectroscopy, sample preparation was done in KBr. X-ray diffraction (XRD) studies were also performed to analyse the stability of c-MWCNTs on mixing with AuNPs. Scanning Electron Microscopy (SEM) was done for analysing the modifications in the surface morphology of the working electrode at different stages of fabrication.

2.6. Assembly of Cholesterol Biosensor

An amperometric cholesterol biosensor was assembled using ChE/ChO/HRP-AuNPs/c-MWCNT Ag as enzyme immobilized working electrode, Ag/AgCl pure as reference, and Pt wire as auxiliary electrode connected via Potentiostat.

2.7. Electrochemical Study of ChO/ChE/HRP-AuNPs/c-MWCNT Ag Electrode

Cyclic voltammetry (CV) studies, Electrochemical Impedance Spectroscopy (EIS), and all other amperometric detections throughout the experiment were performed on a Potentiostat (PSTAT mini 910, Metrohm) using three-electrode system in electrochemical cell. All of the cyclic voltammetric measurements were performed at room temperature and were continuously recorded from −0.4 to +0.4 V with different scan rates (25, 50, and 100 mV/s).

2.8. Kinetic Study of Present Method

Kinetic properties of newly developed method were studied which include optimum pH, temperature, response time, effect of substrate (cholesteryl acetate) concentration, , and .

2.9. Evaluation of the Present Method

Evaluation of present method was carried out with respect to linearity, minimum detection limit, and percent analytical recovery along with precision and accuracy. The effect of interfering species on performance of biosensor was studied. The storage stability with time and repeatability of present method were also analyzed.

2.9.1. Linear Working Range and Minimum Detection Limit

Linearity range and minimum detection range were calculated by plotting values against the values of standard graph.

2.9.2. Analytical Recovery

Reliability of the method was tested using different concentrations of cholesteryl acetate (100 mg/dL and 200 mg/dL) (2.33 mM and 4.66 mM) by spiking the serum samples and mean analytical recoveries of cholesteryl acetate were determined.

2.9.3. Precision

The reproducibility of the present method and the total cholesterol level was determined in the sample on the same day (within batch) and in the same sample after storage at 4°C for one week (between batches); coefficients of variation (CVs) were calculated for the present method.

2.9.4. Accuracy

For determining accuracy of newly developed method, the 10 serum samples were spiked with cholesteryl acetate and then tested by standard Bayer’s enzo kit and also by present method ; then the values obtained by both methods were co-related and regression equation was obtained.

2.9.5. Effect of Interfering Substances

The response of the present method was analyzed in the presence of interfering substances found in serum such as pyruvate, glucose, citrate, Ca2+, uric acid, ascorbic acid, acetone, urea, and bilirubin. The effect of interference by these substances was determined by adding the interfering species in the reaction mixture one by one at their physiological concentration.

2.10. Storage Stability and Reusability of the Present Method

Before every use the enzyme electrode was cleaned using washing buffer (0.01 M phosphate buffer saline, pH 7.2 with 0.1% tween 20). The stability of the working electrode was investigated over a period of 60 days, when stored at 4°C. The response of working electrode was measured once in every 5 days.

2.11. Application of the Newly Developed Method

Blood samples (1 mL each) with different age and sex group were collected from healthy persons and persons suffering from disease due to elevated cholesterol level after 12 hours of fasting, at Pt. BDS PGIMS, Rohtak. The blood samples were centrifuged at 1500 ×g for 5 min and resulting supernatant (serum) was collected for determination of cholesterol level. The test for the serum total cholesterol was carried out by the present method. ChO, ChE, and HRP immobilized onto the working electrode surface catalyze the hydrolysis of cholesteryl acetate and produce H2O2 which is then oxidized by HRP. HRP itself is regenerated as it passes the electron to the electrode directly. Current produced in the process is directly proportional to the concentration of the H2O2 produced which itself is directly proportional to total cholesterol.

3. Results and Discussion

3.1. Characterization of Gold Nanoparticles (AuNPs)

The lab synthesised AuNPs were characterized by transmission electron microscopic (TEM) study. The data showed that nanoparticles were of spherical shape ranging from 10 to 30 nm in size (Figures 1(a), 1(b), and 1(c)).

Figure 1: Transmission electron microscopy (TEM) of gold nanoparticles. (a) Aggregates of gold nanoparticles, (b) dimensions of a tuft of nanoparticles, and (c) enlarged image for size analysis.
3.2. Analysis of Gold Nanoparticles Decorated c-MWCNTs by XRD

Structural stabilization of MWCNTs and working electrode (AuNPs/c-MWCNT) was examined by XRD characterization, as analysed characteristic peaks of c-MWCNTs (Figure 2, Curve (a)) persisted even in the diffraction peaks of AuNPs and c-MWCNT paste (Figure 2, Curve (b)). Peaks appeared at 19.6 and 21.5 which are the unique characteristic peaks of c-MWCNTs which also are present in Curve (b) ensuring that the typical graphitic signature structure of c-MWCNTs is stable even when AuNPs were mixed with c-MWCNT.

Figure 2: X-ray diffraction patterns of c-MWCNTs (a) and AuNP/c-MWCNTs (b).
3.3. Confirmation of Covalent Immobilization by FTIR

FTIR spectra of AuNPs/c-MWCNTs showed absorption peaks near 1011 cm−1, 1545 cm−1, and 2250 cm−1, which are signature peaks of CNTs. After immobilization of enzyme, that is, ChE/ChO/HRP-AuNPs/c-MWCNTs, a new signature peak appeared at 1537 cm−1 and 1630 cm−1 and a broad peak rose at 3287 cm−1 which is due to carbonyl stretch and amide bond.

3.4. Surface Morphology of the Newly Fabricated Electrode

Surface morphology of the working electrode was analysed using Scanning Electron Microscopy at the different stages of fabrication. A visual change had been noticed in the morphological characteristic of the electrode surface with the deposition of material. The SEM images of working electrode without and with enzyme have been shown in Figure 3.

Figure 3: SEM images of (a) electrode without enzyme and (b) with enzyme.
3.5. Electrochemical Analysis of ChE/ChO/HRP-AuNPs/c-MWCNT Ag Electrode

The electrochemical study of working electrode was carried out by using cyclic voltammetry. For determination of reduction potential of HRP immobilized on electrode core, it was immersed in 0.01 M H2O2 for 30 min and then washed with distilled water before performing cyclic voltammetry. Cyclic voltammetry of ChE/ChO/HRP-AuNPs/c-MWCNT Ag electrode was reported from −0.4 and +0.8 V at particular scanned rates of 25 mV/s, 50 mV/s, and 100 mV/s (Figure 4). An optimum scan rate of 50 mV/s was perceived for the above fabricated biosensor. The reproducibility of the fabricated biosensor was examined by running four CV cycles at scan rate of 50 mV/s (Figure 5). During the entire examination, a sharp peak at 0.27 V was observed; this arises as a result of oxidation of HRP present on electrode. So, it was estimated that ChE/ChO/HRP-AuNPs/MWCNT Ag electrode offered ultimate signal and least noise at 0.27 V and was further employed to analytical determinations. The biosensor works at lower potential in comparison to other available biosensors which is due to the large surface area of gold nanoparticles and their highly conductive nature.

Figure 4: Cyclic voltammogram of ChE/ChO/HRP-AuNPs/c-MWCNTs Ag electrode at various scan rates.
Figure 5: Cyclic voltammogram. (A) ChE/ChO/HRP-AuNPs/c-MWCNTs; (B) bare silver electrode.
3.6. Kinetic Study of the Present Method

To improve the working performance of the biosensor various parameters such as working potential, temperature, time, and concentration of substrate and pH value on the fabricated biosensor were analyzed.

3.6.1. Response for Working Potential

The response of current with varying applied potential on the biosensor had been shown in Figure 6. The working potential was skipped from 0.0 V to 0.7 V. With the increase in working potential, increase in steady-state current response was observed. Firstly, it showed a significant increase in current value from +0.1 V to +0.27 V and then reached a level from +0.27 V to +0.5 V and declined slightly after +0.5 V. Therefore, +0.27 V was selected as the working potential for detection of cholesterol by the biosensor.

Figure 6: Response of current with applied potential.
3.6.2. Response for pH

The pH of reaction buffer was varied in the pH range, pH 4.5 to 8.0, to find the optimum pH using sodium succinate buffer (pH 4.5–5.5) and sodium phosphate buffer (pH 6.0–8.0) at a final concentration of 0.02 M. All other variants were of standard assay condition except pH. Optimum pH was found to be 7 for the biosensor (Figure 7).

Figure 7: Effect of pH on current response of the present method.
3.6.3. Response for Temperature

The response of biosensor for continuous raise of temperature by 5°C from 20°C to 60°C was interrogated. It was found that the biosensor showed maximum response at 40°C (Figure 8). The microenvironment provided by support used for immobilization makes it thermally stable and maintains its biological activity.

Figure 8: Effect of incubation temperature on the response of present method.
3.6.4. Response with Time

The amperometric response was measured from 5 s to 60 s at interval of 10 s. The response time increases from 5 to 20 s and later attains stability (Figure 9).

Figure 9: Response time of the current method.
3.6.5. Response for Substrate Concentration

A linear relationship among the substrate concentration from 0.5 mg/dL to 250 mg/dL and current was observed. The current approach gave a hyperbolic curve between current response and cholesteryl acetate concentration. A significant response was observed up to a concentration of 500 mg/dL (Figure 10).

Figure 10: Effect of cholesteryl acetate concentration on the present method.
3.6.6. Resolving and Values

The (app) and (app) values were resolved by estimating the slope and intercept for the reciprocal plot of current versus cholesteryl acetate concentrations, that is, double reciprocal plot or Lineweaver-Burk plot. The and values obtained were 58.7 mgdL−1 and 0.9 mAs−1, respectively (Figure 11).

Figure 11: Lineweaver-Burk plot of the present method.
3.7. Assessment of the Current Method
3.7.1. Linear Range for Working and Minimum Limit of Detection

Both the linear range for working and minimum limit of detection of a biosensor are considered while interrogating the performance of a biosensor. In the current method, the standard graph between substrate concentration and current response was used for estimation of linear range for working and minimum limit of detection. The linear range for working offered by current biosensor is 0.5 mg/dL–250 mg/dL and minimum limit of detection limit is 0.5 mg/dL which is far better than previous announced biosensors (Table 1).

Table 1: Analytical recovery calculated by using added cholesteryl acetate in serum sample.
3.7.2. Analytical Recovery

By analytical recovery of added enzyme cholesteryl acetate reliability of the current biosensor was calculated (Table 1). The mean analytical recoveries for 100 mg/dL and 200 mg/dL of added cholesteryl acetate were 99.1% and 98.6%, respectively.

3.7.3. Precision

The concentration of total cholesterol was calculated on the same day (within batch) and in the same sample after storage at 4°C for one week (between batches) in the serum sample repeatedly to examine the reproducible nature of the current biosensor. The values for coefficients of variation (CVs) were < 0.61% and < 0.98% for within batch and between batches, respectively (Table 2). The results were far better than various earlier reported methods (Table 6).

Table 2: Within batch and between batches coefficients of variation for determination of total cholesterol in serum samples.
3.7.4. Accuracy

The level of cholesteryl acetate added to serum samples was computed by using the standard method, that is, enzo kit and current method , and accuracy of the current biosensor was analysed (Figure 12). The regression equation was used to attain cholesteryl acetate results for newly fabricated working electrode with a good correlation as compared to standard method. All these results showed that the current biosensor offers excellent accuracy.

Figure 12: Correlation between cholesteryl acetate concentrations in serum determined by standard enzo kit method (-axis) and by the present method (-axis).
3.7.5. Interference Study

Among the various serum substances investigated for possible interference on the response of the present method, none caused any significant interference on the performance of cholesterol biosensor. Effect of different substances on the working of biosensor has been shown in Table 3.

Table 3: Effect of different serum substances on the working of CH biosensor.
3.8. Reliability and Stability

The biosensor was reliable and stable. When stored at 4°C, the sensor was stable up to one month and after 35 uses in second month its performance was reduced (Figure 13). Only 45% activity of the biosensor remained at the end of the 2nd month (Figure 14). In comparison to the reported biosensors it showed better stability (Table 6). The immobilization of ChO, ChE, and HRP on AuNPs/c-MWCNTs Ag based working electrode was credited by good stability, reliability, and reproducibility. Further enzyme degrading and leaching was prevented by coating the biosensor with polyacrylamide which also increases the stability of biosensor.

Figure 13: Reusability of the present method.
Figure 14: Storage stability of the present method.
3.9. Application of the Newly Developed Method

Concentration of cholesterol was determined in different samples by the newly developed biosensor. Table 4 represents the total cholesterol in serum of probably healthy individuals including males and females of different age group computed by the current biosensor. The total cholesterol level was found between 154.17 and 225.89 mg/dL for males and 144.56 and 225.58 mg/dL for females which is in normal range. Table 5 outlines the different working parameters of freshly fabricated biosensor.

Table 4: Total cholesterol level in serum of probably healthy individuals calculated by current biosensor.
Table 5: Working parameters of the newly developed method.
Table 6: Comparison of the present method with previously reported biosensor for total cholesterol determination.

4. Conclusion

A fresh biosensor was fabricated exploiting the conductive properties of Au nanoparticles and c-MWCNT paste. Covalent immobilisation of ChO, ChE, and HRP on the working electrode was insured by FTIR. This ChE/ChO/HRP-AuNPs/c-MWCNTs modified Ag electrode exhibits enhanced sensitivity in a linear range of 0.5 mg/dL–250 mg/dL (0.01 mM–5.83 mM), quick response time (<20 s), low limit of detection (0.5 mg/dL) (0.01 mM), reproducibility of more than 55 times, and stability of 2 months. A good correlation was obtained with that of standard method. Further, the working electrode was coated with polyacrylamide polymer which provides long time stability and high reusability to the biosensor. The work contributed a competent amperometric approach for detection of total cholesterol in serum.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.


The authors are thankful to Department of Physics, Maharishi Dayanand University, Rohtak, for providing the XRD facility and Jawaharlal Nehru University, New Delhi, for providing facilities for SEM, TEM, and FTIR analysis. Special thanks are due to PGIMS Rohtak for providing serum samples.


  1. M. Kratz, “Dietary cholesterol, atherosclerosis and coronary heart disease,” in Atherosclerosis: Diet and Drugs, vol. 170 of Handbook of Experimental Pharmacology, pp. 195–213, Springer, Berlin, Germany, 2005. View at Publisher · View at Google Scholar
  2. G. J. Miller, “High density lipoproteins and atherosclerosis,” Annual Review of Medicine, vol. 31, pp. 97–108, 1980. View at Publisher · View at Google Scholar · View at Scopus
  3. S. Kroger and B. Danielsson, “Calorimetric biosensors,” in Handbook of Biosensors and Electronic Noses. Medicine, Food and the Environment, pp. 279–298, CRC Press, Oxford Science Publications, New York, NY, USA, 1997. View at Google Scholar
  4. Y. Kayamori, H. Hatsuyama, T. Tsujioka, M. Nasu, and Y. Katayama, “Endpoint colorimetric method for assaying total cholesterol in serum with cholesterol dehydrogenase,” Clinical Chemistry, vol. 45, no. 12, pp. 2158–2163, 1999. View at Google Scholar · View at Scopus
  5. D. M. Amundson and M. Zhou, “Fluorometric method for the enzymatic determination of cholesterol,” Journal of Biochemical and Biophysical Methods, vol. 38, no. 1, pp. 43–52, 1999. View at Publisher · View at Google Scholar · View at Scopus
  6. T. C. Huang, V. Wefler, and A. Raftery, “A simplified spectrophotometric method for determination of total and esterified cholesterol with tomatine,” Analytical Chemistry, vol. 35, no. 11, pp. 1757–1758, 1963. View at Publisher · View at Google Scholar · View at Scopus
  7. C. C. Allain, L. S. Poon, C. S. Chan, W. Richmond, and P. C. Fu, “Enzymatic determination of total serum cholesterol,” Clinical Chemistry, vol. 20, no. 4, pp. 470–475, 1974. View at Google Scholar
  8. V. Raghavan, K. Ramanathan, P. V. Sundaram, and B. Danielsson, “An enzyme thermistor based assay for total and free cholesterol,” Clinica Chimica Acta, vol. 289, no. 1-2, pp. 145–158, 1999. View at Publisher · View at Google Scholar · View at Scopus
  9. A. Vikas and C. S. Pundir, “Biosensors: future analytical tools, sensors & transducers,” FJournal, vol. 76, pp. 935–936, 2007. View at Google Scholar
  10. S. V. Dzyadevych, V. N. Arkhypova, A. P. Soldatkin, A. V. El'skaya, C. Martelet, and N. Jaffrezic-Renault, “Amperometric enzyme biosensors: past, present and future,” IRBM, vol. 29, no. 2-3, pp. 171–180, 2008. View at Publisher · View at Google Scholar · View at Scopus
  11. R. K. Basniwal, R. P. S. Chauhan, S. Parvez, and V. K. Jain, “Development of a cholesterol biosensor by chronoamperometric deposition of polyaniline-Ag nanocomposites,” International Journal of Polymeric Materials and Polymeric Biomaterials, vol. 62, no. 9, pp. 493–498, 2013. View at Publisher · View at Google Scholar · View at Scopus
  12. U. Hanefeld, L. Gardossi, and E. Magner, “Understanding enzyme immobilisation,” Chemical Society Reviews, vol. 38, no. 2, pp. 453–468, 2009. View at Publisher · View at Google Scholar
  13. A. Sassolas, L. J. Blum, and B. D. Leca-Bouvier, “Immobilization strategies to develop enzymatic biosensors,” Biotechnology Advances, vol. 30, no. 3, pp. 489–511, 2012. View at Publisher · View at Google Scholar · View at Scopus
  14. C. Spahn and S. D. Minteer, “Enzyme immobilization in biotechnology,” Recent Patents on Engineering, vol. 2, no. 3, pp. 195–200, 2008. View at Publisher · View at Google Scholar · View at Scopus
  15. S. Datta, L. R. Christena, Y. Rani, and S. Rajaram, “Enzyme immobilization: an overview on techniques and support materials,” 3 Biotech, vol. 3, no. 1, pp. 1–9, 2013. View at Publisher · View at Google Scholar
  16. X. Wang and S. Uchiyama, “Polymers for biosensors construction,” in State of the Art in Biosensors—General Aspects, T. Rinken, Ed., chapter 3, pp. 67–84, InTech, Rijeka, Croatia, 2013. View at Publisher · View at Google Scholar
  17. S. Singh, A. Chaubey, and B. D. Malhotra, “Amperometric cholesterol biosensor based on immobilized cholesterol esterase and cholesterol oxidase on conducting polypyrrole films,” Analytica Chimica Acta, vol. 502, no. 2, pp. 229–234, 2004. View at Publisher · View at Google Scholar · View at Scopus
  18. A. Gahlaut, A. K. Chhillar, Ashish, and V. Hooda, “Development of analytical method based on enzymatic PVC strip for measurement of serum total cholesterol,” International Journal of Biotechnology & Biochemistry, vol. 2, pp. 185–195, 2012. View at Google Scholar
  19. J.-C. Vidal, E. Garcia, and J.-R. Castillo, “Development of a platinized and ferrocene-mediated cholesterol amperometric biosensor based on electropolymerization of polypyrrole in a flow system,” Analytical Sciences, vol. 18, no. 5, pp. 537–542, 2002. View at Publisher · View at Google Scholar · View at Scopus
  20. V. Hooda and C. S. Pundir, “Cholesterol biosensor based on HRP incorporated carbon paste electrode wrapped with CA membrane enzyme laminate,” International Journal of Biotechnology & Biochemistry, vol. 7, pp. 617–635, 2011. View at Google Scholar
  21. Vikas and C. S. Pundir, “Fabrication of Pt based amperometric cholesterol biosensor using cellulose acetate membrane,” Journal of Scientific and Industrial Research, vol. 67, no. 4, pp. 299–306, 2008. View at Google Scholar · View at Scopus
  22. A. Kumar, P. Rajesh, A. Chaubey, S. K. Grover, and B. D. Malhotra, “Immobilization of cholesterol oxidase and potassium ferricyanide on dodecylbenzene sulfonate ion-doped polypyrrole film,” Journal of Applied Polymer Science, vol. 82, no. 14, pp. 3486–3491, 2001. View at Publisher · View at Google Scholar · View at Scopus
  23. P.-C. Nien, P.-Y. Chen, and K.-C. Ho, “Fabricating an amperometric cholesterol biosensor by a covalent linkage between poly(3-thiopheneacetic acid) and cholesterol oxidase,” Sensors, vol. 9, no. 3, pp. 1794–1806, 2009. View at Publisher · View at Google Scholar · View at Scopus
  24. S. Singh, R. Singhal, and B. D. Malhotra, “Immobilization of cholesterol esterase and cholesterol oxidase onto sol-gel films for application to cholesterol biosensor,” Analytica Chimica Acta, vol. 582, no. 2, pp. 335–343, 2007. View at Publisher · View at Google Scholar · View at Scopus
  25. P. Norouzi, F. Faridbod, E. Nasli-Esfahani, B. Larijani, and M. R. Ganjali, “Cholesterol biosensor based on MWCNTs-MnO2 nanoparticles using FFT continuous cyclic voltammetry,” International Journal of Electrochemical Science, vol. 5, no. 7, pp. 1008–1017, 2010. View at Google Scholar · View at Scopus
  26. J.-Y. Yang, Y. Li, S.-M. Chen, and K.-C. Lin, “Fabrication of a cholesterol biosensor based on cholesterol oxidase and multiwall carbon nanotube hybrid composites,” International Journal of Electrochemical Science, vol. 6, no. 6, pp. 2223–2234, 2011. View at Google Scholar · View at Scopus
  27. G. Li, J. M. Liao, G. Q. Hu, N. Z. Ma, and P. J. Wu, “Study of carbon nanotube modified biosensor for monitoring total cholesterol in blood,” Biosensors and Bioelectronics, vol. 20, no. 10, pp. 2140–2144, 2005. View at Publisher · View at Google Scholar · View at Scopus
  28. H. Zhang, R. Liu, and J. Zheng, “Selective determination of cholesterol based on cholesterol oxidase-alkaline phosphatase bienzyme electrode,” Analyst, vol. 137, no. 22, pp. 5363–5367, 2012. View at Publisher · View at Google Scholar · View at Scopus
  29. T. T. Baby and S. Ramaprabhu, “Non-enzymatic glucose and cholesterol biosensors based on silica coated nano iron oxide dispersed multiwalled carbon nanotubes,” in Proceedings of the International Conference on Nanoscience, Technology and Societal Implications (NSTSI '11), pp. 1–6, IEEE, Bhubaneswar, India, December 2011. View at Publisher · View at Google Scholar · View at Scopus
  30. R. Manjunatha, G. Shivappa Suresh, J. Savio Melo, S. F. D'Souza, and T. Venkatarangaiah Venkatesha, “An amperometric bienzymatic cholesterol biosensor based on functionalized graphene modified electrode and its electrocatalytic activity towards total cholesterol determination,” Talanta, vol. 99, pp. 302–309, 2012. View at Publisher · View at Google Scholar · View at Scopus
  31. V. N. Psychoyios, G.-P. Nikoleli, N. Tzamtzis et al., “Potentiometric cholesterol biosensor based on ZnO nanowalls and stabilized polymerized lipid film,” Electroanalysis, vol. 25, no. 2, pp. 367–372, 2013. View at Publisher · View at Google Scholar · View at Scopus
  32. R. Khan, A. Kaushik, P. R. Solanki, A. A. Ansari, M. K. Pandey, and B. D. Malhotra, “Zinc oxide nanoparticles-chitosan composite film for cholesterol biosensor,” Analytica Chimica Acta, vol. 616, no. 2, pp. 207–213, 2008. View at Publisher · View at Google Scholar · View at Scopus
  33. D. Saini, R. Chauhan, P. R. Solanki, and T. Basu, “Gold-nanoparticle decorated graphene-nanostructured polyaniline nanocomposite-basedbienzymatic platformform cholesterol sensing,” ISRN Nanotechnology, vol. 2012, Article ID 102543, 12 pages, 2012. View at Publisher · View at Google Scholar
  34. M. Zhang, R. Yuan, Y. Chai et al., “A biosensor for cholesterol based on gold nanoparticles-catalyzed luminol electrogenerated chemiluminescence,” Biosensors and Bioelectronics, vol. 32, no. 1, pp. 288–292, 2012. View at Publisher · View at Google Scholar · View at Scopus
  35. N. Peña, G. Ruiz, A. J. Reviejo, and J. M. Pingarrón, “Graphite-teflon composite bienzyme electrodes for the determination of cholesterol in reversed micelles. Application to food samples,” Analytical Chemistry, vol. 73, no. 6, pp. 1190–1195, 2001. View at Publisher · View at Google Scholar
  36. S. Cao, L. Zhang, Y. Chai, and R. Yuan, “Electrochemistry of cholesterol biosensor based on a novel Pt-Pd bimetallic nanoparticle decorated graphene catalyst,” Talanta, vol. 109, pp. 167–172, 2013. View at Publisher · View at Google Scholar · View at Scopus
  37. V. Hooda, A. Gahlaut, H. Kumar, and C. S. Pundir, “Biosensor based on enzyme coupled PVC reaction cell for electrochemical measurement of serum total cholesterol,” Sensors and Actuators B: Chemical, vol. 136, no. 1, pp. 235–241, 2009. View at Publisher · View at Google Scholar · View at Scopus
  38. J. Turkevich, P. C. Stevenson, and J. Hillier, “A study of the nucleation and growth processes in the synthesis of colloidal gold,” Discussions of the Faraday Society, vol. 11, pp. 55–75, 1951. View at Publisher · View at Google Scholar · View at Scopus
  39. J.-L. Besombes, S. Cosnier, P. Labbé, and G. Reverdy, “Improvement of the analytical characteristics of an enzyme electrode for free and total cholesterol via laponite clay additives,” Analytica Chimica Acta, vol. 317, no. 1–3, pp. 275–280, 1995. View at Publisher · View at Google Scholar · View at Scopus
  40. R. Foster, J. Cassidy, and E. O'Donoghue, “Electrochemical diagnostic strip device for total cholesterol and its subfractions,” Electroanalysis, vol. 12, no. 9, pp. 716–721, 2000. View at Google Scholar · View at Scopus
  41. E. García-Ruiz, J. C. Vidal, M. T. Aramendía, and J. R. Castillo, “Design of an interference-free cholesterol amperometric biosensor based on the electrosynthesis of polymeric films of diaminonaphthalene isomers,” Electroanalysis, vol. 16, no. 6, pp. 497–504, 2004. View at Publisher · View at Google Scholar · View at Scopus
  42. E. Salinas, V. Rivero, A. A. J. Torriero, D. Benuzzi, M. I. Sanz, and J. Raba, “Multienzymatic-rotating biosensor for total cholesterol determination in a FIA system,” Talanta, vol. 70, no. 2, pp. 244–250, 2006. View at Publisher · View at Google Scholar · View at Scopus
  43. S. Singh, P. R. Solanki, M. K. Pandey, and B. D. Malhotra, “Covalent immobilization of cholesterol esterase and cholesterol oxidase on polyaniline films for application to cholesterol biosensor,” Analytica Chimica Acta, vol. 568, no. 1-2, pp. 126–132, 2006. View at Publisher · View at Google Scholar · View at Scopus
  44. A. Ahmadalinezhad and A. Chen, “High-performance electrochemical biosensor for the detection of total Cholesterol,” Biosensors and Bioelectronics, vol. 26, no. 11, pp. 4508–4513, 2011. View at Publisher · View at Google Scholar · View at Scopus
  45. N. Batra, M. Tomar, and V. Gupta, “ZnO–CuO composite matrix based reagentless biosensor for detection of total cholesterol,” Biosensors and Bioelectronics, vol. 67, pp. 263–271, 2015. View at Publisher · View at Google Scholar · View at Scopus