Application of Conducting Poly(aniline-co-Pyrrole) Film
to Cholesterol Biosensor
Pratima R. Solanki, Suman Singh, Nirmal Prabhakar, M. K. Pandey, B. D. Malhotra
Biomolecular Electronics and Conducting Polymer Research Group, National Physical Laboratory,
Dr. K. S. Krishnan Marg, New Delhi-110012, India
Received 21 June 2006; accepted 12 January 2007
DOI 10.1002/app.26198
Published online 24 May 2007 in Wiley InterScience (www.interscience.wiley.com).
ABSTRACT: Cholesterol oxidase (ChOx) has been covalently immobilized onto poly(aniline-co-pyrrole), electrochemically deposited onto indium-tin-oxide (ITO) glass
plates, using glutaraldehyde as a crosslinker. These poly
(An-co-Py)/ChOx films have been characterized using UV–
visible spectroscopy fourier transform infrared spectroscopy, scanning electron microscopy, and photometric and
amperometric techniques, respectively. The poly(An-coPy)/ChOx bioelectrodes have been utilized for cholesterol
estimation in the range of 1–10 mM. The ChOx activity in
INTRODUCTION
Cholesterol is known to play an important role in the
membrane and outer layer of plasma lipoproteins.
Determination of cholesterol concentration in blood
and serum is a fundamental parameter for the prevention and diagnosis of a number of clinical disorders
such as heart diseases, atherosclerosis, hypertension,
cerebral thrombosis, and coronary and peripheral vascular diseases.1–4 Many enzymatic and nonenzymatic
methods5–8 have been reported for the measurement
of cholesterol. The nonenzymatic methods are highly
time-consuming, require expert manpower, expensive
chemicals, and are unsuitable for rapid and automated analysis of cholesterol serum. Enzymatic methods for the determination of cholesterol involve complicated procedures and high cost because of the use
of expensive enzymes in each assay.9,10 Attempts
have been made to develop sensitive, selective, rapid,
reliable, and low cost biosensors for the determination
of cholesterol in serum and blood.11–14 The stability of
the enzymatic electrodes for biosensor application can
be achieved by immobilization of enzyme on suitable
matrices. Immobilization of cholesterol oxidase
Correspondence to: B. D. Malhotra (bansi.malhotra@gmail.
com).
Contract grant sponsor: DST; contract grant numbers:
DST/TSG/ME/2002/19, DST/TSG/CLP041332.
Contract grant sponsor: CSIR.
Journal of Applied Polymer Science, Vol. 105, 3211–3219 (2007)
C 2007 Wiley Periodicals, Inc.
V
poly(An-co-Py)/ChOx bioelectrode has been found to be
the highest at pH 7.0 at 258C. The sensitivity and stability
of poly(An-co-Py)/ChOx bioelectrode have been experimentally determined as 93.35 mA/mM and 10 weeks at
48C, respectively. Ó 2007 Wiley Periodicals, Inc. J Appl Polym
Sci 105: 3211–3219, 2007
Key words: polyaniline; polypyrrole; copolymer; cholesterol; cholesterol oxidase; biosensor; electrochemical polymerization
(ChOx) on various matrices such as conducting polymers,15–17 sol-gels,18–20 self-assembled monolayers
(SAM),21,22 carbon paste,23 cellulose acetate,24 nanoparticles,25 graphite–teflon composite matrix,26 etc.
have been carried out using various immobilization
procedures such as physical adsorption,27,28 entrapment,27 covalent linkage,21,29 etc.
Conducting polymers have recently attracted much
attention as suitable matrices for the immobilization
of biomolecules,30–35 since these can efficiently transfer electric charge produced during a biochemical
reaction. Conducting polymers such as polypyrrole
(PPy) and polyaniline (PANI) are attractive matrices
since they contribute towards the speed, sensitivity,
versatility, considerable flexibility, bio-compatibility,
and improvement in the shelf-life of biosensing electrodes due to electrostatic binding between biomolecule and conducting polymers.16,36,37 The exclusion
properties of PPy films provide selectivity for biosensors against interferents present in biological media,
particularly electroactive endogenous anionic species
such as ascorbate and urate.38 PANI is considered an
attractive polymer having two redox potentials to
facilitate enzyme-polymer charge transfer. The majority of the studies have been restricted to homopolymers only, prepared either by chemical or electrochemical techniques.34,35
Vidal et al.39 have reported an amperometric cholesterol biosensor based on the electrochemically
polymerized pyrrole on a layer of Prussian-blue (PB)
onto the Pt electrode for electro-catalytic detection of
H2O2 produced during the enzymatic reaction of
3212
cholesterol and ChOx. The influence of the formation
of SAMs on the Pt surface, stability of the PB layer,
and the formation of an outer layer of Nafion (Nf) as
a means of improving selectivity were studied. The
shelf-life of this cholesterol biosensor was found to
be about 25 days. Singh et al. have reported electrochemical coimmobilization of cholesterol esterase
and ChOx onto PPy films to estimate total cholesterol.29 The sensitivity, apparent Km, and the shelflife of these PPy/ChEt/ChOx electrodes were found
to be as 0.15 mA/mM, 9.8 mM, and about 4 weeks at
48C, respectively. A mediator-based amperometric
cholesterol biosensor has been developed by entrapment of the ChOx enzyme and charge transfer mediator using both artificial (ferrocene derivative) and
natural (flavin nucleotide) in a PPy layer.17 ChOx
and potassium ferricyanide physically immobilized
onto electrochemically prepared dodecylbenzene sulfonate (DBS)-doped PPy films were used to estimate
cholesterol.40 These Chox/DBS-PPy/ITO electrodes
showed linearity in the range of 2–8 mM of cholesterol and the electrodes were stable for about 3
months. A cholesterol biosensor developed by
depositing layer-by-layer nanothin films of polystyrenesulfonate and ChOx onto microperoxidase-11
(MP-11), which was covalently linked with Au-alkanethiol electrodes showed linearity in the range of
0.2–3.0 mM.41 Lin and Yang42 immobilized ChOx
(COD) on the surface of polyacrylonitrile (PAN) hollow fiber dialyzer using glutaraldehyde as a crosslinker. This bioelectrode showed poor storage stability retaining 53% of its initial activity of ChOx in 30
days. A bi-enzymatic biosensor has been fabricated
using horseradish peroxidase and ChOx enzymes
physically entrapped onto the surface of a pyrolitic
graphite electrode for free cholesterol estimation.43
An amperometric cholesterol biosensor based on
covalent immobilization of cholesterol esterase
(ChEt) and cholesterol oxidase (ChOx) onto electrochemically prepared PANI films.15 The linearity and
shelf-life of this ChEt/ChOx/PANI electrode was
obtained as 50–500 mg/dL and 6 weeks, respectively. An optical biosensor has been reported based
on the coimmobilization of cholesterol esterase,
ChOx, and peroxidase onto electrochemically prepared PANI film (PANI/ChEt/ChOx/POD).16 The
linearity range of this (PANI/ChEt/ChOx/POD)
electrode has been observed as 50–500 mg/dL and
shelf-life as 6 weeks, respectively. All these cholesterol biosensors suffer from either low range of linearity and poor stability.
Composites, copolymers, and double layers having
conductive matrix can be prepared when two monomers having conductive homopolymers are polymerized, and the conductive product with different
properties than those of homopolymers could be
obtained.44
Journal of Applied Polymer Science DOI 10.1002/app
SOLANKI ET AL.
The commercial exploitation of the conducting
polymer based biosening devices is linked with their
ease of processability. The processability can be
enhanced either by making substitution into the aromatic nucleus or copolymerizing in such a way that
there is variation in the torsion angle between adjacent phenyl rings of the polymer.45 Desired properties of PANI, such as mechanical strength, can be
enhanced by mixing it with a polymer that has good
mechanical properties. PANI is a unique polymer
that has a nitrogen heteroatom incorporated between
phenyl rings along with polymer chain. This structure provides flexibility and allows the existence of
three different oxidation states that are leucoemeraldine, emeraldine, and pernigraniline. Leucoemeraldine and pernigraniline forms of PANI are not stable
and they will return to the state of emeraldine under
atmospheric environment. Moreover, copolymerization is known to be an easy and powerful method
for obtaining polymer with desired properties, and
are thus widely used in the production of commercial polymers including fundamental investigations
of structural-property relationships.46–49 Aniline and
pyrrole can be copolymerized by oxidative chemical copolymerization.50,51 Electrochemical copolymerization of pyrrole and aniline has been reported
using various solvents and acetonitrile in the presence of an organic acid trifluoroethanoic acid
(CF3COOH), tetraethyl ammonium tetrafluoroborate,
or tetramethyl ammonium trifluoro methane sulfonate as electrolyte.52,53 In the present article we have
electrochemically synthesized copolymer film of aniline and pyrrole for the immobilization of ChOx.
These poly(An-co-Py)/ChOx bioelectrodes have been
characterized using Fourier transform infrared spectroscopy (FTIR), scanning electron microscopy
(SEM), UV–visible spectroscopy and utilized for the
estimation of cholesterol by amperometric and optical techniques, respectively.
EXPERIMENTAL
Cholesterol oxidase (ChOx), (4 U/mL, EC 1.1.36,
from pseudomonas species), and peroxidase (40 U/
mL, EC 1.136, from pseudomonas fluorescens)
enzymes were procured from Sigma Chemical, USA.
Potassium phosphate (monobasic and dibasic salt),
o-dianisidine, and other chemicals were of analytical
grade. Aniline (Sigma) and pyrrole (Aldrich) were
distilled prior to being used.
Potentiostat/Galvanostat-273A (Princeton Applied
Research) was used for electrochemical synthesis
and amperometric studies of copolymer poly(An-coPy) in potentiostatic mode. Indium-tin-oxide (ITO)
coated glass plates (Balzers), sheet resistance 15 O/
cm, were used as substrates for deposition of desired
polymeric film that were used as working electrodes.
APPLICATION OF CONDUCTING POLYANILINE-co-PYRROLE FILM
3213
Figure 1 (a) Cyclic voltammogram of poly(An-co-Py) film in phosphate buffer (50 mM, pH 7.0) and (b) Cyclic voltammogram of poly(An-Py)/ChOx bioelectrode in phosphate buffer (50 mM, pH 7.0).
Platinum foil (counter electrode) was obtained from
the Johnson-Mathey. Millipore water purification system (Milli Q1075) was used to obtain deionized water.
UV–visible spectrophotometer (Shimadzu 160A) was
used to measure the ChOx activity. FTIR studies
were recorded using Perkin–Elmer Spectrum BX
and SEM photographs were recorded using SEM
(LEO 440).
For synthesis of poly(An-co-Py) copolymer, a mixture of 20 mL of 0.1M sulfuric acid and 1 : 1 ratio of
aniline and pyrrole monomer solution was stirred
until homogeneous mixture was obtained. ITO glass
plates were used as substrates for copolymer film
deposition and the electrochemical polymerization
was carried out at 0.8 V. The electrical conductivity of
poly(An-co-Py) film was found to be 3.1 10 2 S/cm
while the conductivity of PPy and PANI has been calculated as 2.8 10 2 and 2.0 10 2 S/cm measured
by four points probe method. The poly(An-co-Py) film
was dried at room temperature and was washed with
buffer prior to being used.54 The cyclic voltammetric
(CV) studies of copolymer film were done between
0.2 and 1.3 V.
The enzyme solutions of ChOx (4.0 U/mL) and
peroxidase (40.0 U/mL) were prepared afresh in
phosphate buffer (50 mM, pH 7.0). Cholesterol solution was prepared using Triton X-100 as surfactant.
First cholesterol was dissolved in 10 mL of Triton
X-100. It was gently heated until it became clear and
transparent solution.
Poly(An-co-Py)/ChOx bioelectrodes were prepared
by covalent immobilization of ChOx by using glutaraldehyde as the crosslinking agent. The poly(An-coPy)/ChOx bioelectrodes were kept overnight for
drying and were thoroughly washed with phosphate
buffer solution to get rid off any loosely bound
enzyme prior to be used.
RESULTS AND DISCUSSION
Cyclic voltammetric studies
Figure 1(a) shows the CV response of a poly(An-coPy) films, the prominent oxidation peaks seen at 0.8 V
(PPy) and 0.3 V (PANI) in phosphate buffer (50 mM,
pH 7.0) observed at the scan rate of 20 mV/s confirm
the synthesis of copolymer. The lower value of amperometric current observed for poly(An-co-Py)/
ChOx bioelectrode has been attributed to the slow
electron transfer rate in the electrode due to nonconducting nature of the ChOx enzyme [Fig. 1(b)].
The surface concentration of anions in the poly
(An-co-Py) electrode is calculated using BrownAnson model equation15
Ip ¼
n2 F2 I AV
4RT
(1)
Figure 2 FTIR of (a) polypyrrole (PPy), (b) polyaniline
(PANI), (c) poly-(An-co-Py)/ChOx, and (d) poly-(An-co-Py)
bioelectrodes.
Journal of Applied Polymer Science DOI 10.1002/app
3214
SOLANKI ET AL.
Figure 3 (a) Scanning electron micrographs of an electrochemically synthesized polyaniline (PANI) film. (b) Polypyrrole
(PPy) film. (c) Copolymer poly(An-co-Py) film. (d) Copolymer (poly(An-co-Py) containing immobilized ChOx.
where n is the number of electrons transferred (2), F
is Faraday constant (96,584 C/mol), I* the surface
concentration of the poly(An-Py) films (mol/cm2), A
is the surface area of the electrode (1 cm2), V the
scan rate (20 10 3 V/s), R the gas constant (8.314
J/mol K), and T is the absolute temperature (298 K).
The calculated surface concentration (I*) of anions in
poly(An-co-Py) films is 1.9 10 9 mol/cm2.
FTIR studies of PPy, PANI, poly(An-co-Py),
and poly(An-co-Py)/ChOx bioelectrodes
FTIR spectra were recorded for PPy, PANI, poly(Anco-Py)/ChOx, and poly(An-co-Py) [Fig. 2(a–d)],
respectively. Characteristic peaks seen at 1535, 1488,
1301, 1165, 960, 892, and 739 cm 1 indicate the presence of PANI chain back-bone Figure 2(b). The peaks
Journal of Applied Polymer Science DOI 10.1002/app
Figure 4 Photometric response of poly(An-co-Py)/ChOx
bioelectrode as a function of time. [Color figure can be
viewed in the online issue, which is available at www.
interscience.wiley.com.]
APPLICATION OF CONDUCTING POLYANILINE-co-PYRROLE FILM
3215
Figure 5 (a) Photometric response of poly(An-co-Py)/ChOx bioelectrode in immobilized solution phase as a function of
cholesterol concentration (mM), in phosphate buffer (50 mM, pH 7.0). (b) UV spectra for poly(An-co-Py)/ChOx bioelectrode as a function of cholesterol concentration (1–10 mM) in phosphate buffer (50 mM, pH 7.0). [Color figure can be
viewed in the online issue, which is available at www.interscience.wiley.com.]
at 1535 and 1488 cm 1 reveal the C¼
¼C vibration of
quinoid benzoid rings. The peaks at 1584 and
¼N and C N
1496 cm 1 indicate the presence of C¼
vibration in PPy [Fig. 2(a)]. The 1541 and 1718 cm 1
peaks seen in Figure 2(c) are due to amide I and amide
II linkage of the ChOx enzymes. The broad peak
obtained at 3300 cm 1 indicates the N H stretching
vibration of both aniline and pyrrole Figure 2(d).51
Photometric studies for poly(An-co-Py)/
ChOx bioelectrode
The following biochemical reaction occurs as a result
of interaction of ChOx with cholesterol:
ChOx
Cholesterol þ O2 ! Cholestenone þ H2 O2
(2)
POD
H2 O2 þ o-dianisidineðredÞ ! 4H2 O
þ Quinonemine dyeðoxiÞ ðcolored productÞ
SEM studies for polyaniline, polypyrole, poly
(An-co-Py), poly(An-co-Py)/ChOx bioelectrodes
Figure 3 shows the SEM images of PANI, PPy, and
poly(An-co-Py) films with and without ChOx. PANI
film shows rough or spongy type structure, whereas
PPy film exhibits granulated structure.49 The SEM
picture of copolymer film shows uniform distribution of fibers and granules arising due to pyrrole-coaniline molecules [Fig. 3(c)].44 The immobilization of
ChOx enzyme onto the poly(An-co-Py) electrode
decreases the roughness and granular nature of surface. It appears that enzyme has been stationed at
pores of the poly(An-co-Py) electrode indicating
smoother surface [Fig. 3(d)].
Figure 6 UV spectra of poly(An-co-Py) as a function of
different units of ChOx enzyme.
ð3Þ
The enzyme activity of ChOx was assayed in
free and in the immobilized phase by measuring the
absorbance of colored compound formed as a result
of biochemical reaction [eq. (3)]. In the free phase,
the absorbance was measured by adding 10 mL of
ChOx in the reaction mixture consisting of 3.0 mL
phosphate buffer (50 mM, pH 7.0), 0.1 mL cholesterol solution (4 mM), 50 mL peroxidase (40 U), and
0.05 mL of o-dianisidine (1%) at 500 nm. The enzyme
activity of poly(An-co-Py)/ChOx bioelectrode was
determined by incubating the electrode in the reac-
Figure 7 Photometric response of poly(An-co-Py)/ChOx
bioelectrode as a function of pH in solutional immobilized
phase.
Journal of Applied Polymer Science DOI 10.1002/app
3216
SOLANKI ET AL.
Figure 8 (a) Photometric response of poly(An-co-Py)/ChOx bioelectrode as a function of temperature in the presence
of cholesterol (4 mM) and phosphate buffer (50 mM, pH 7.0). (b) Arrehenius plot for the effect of temperature on
the response of poly(An-co-Py)/ChOx bioelectrode in the presence of cholesterol (4 mM) and phosphate buffer (50 mM,
pH 7.0).
tion mixture for 60 s. Figure 4 shows the photometric response of poly(An-co-Py)/ChOx bioelectrode as
a function of reaction time. The decreased absorbance obtained for the poly(An-co-Py)/ChOx bioelectrode compared to poly(An-co-Py) electrode might
be due to the fact that some of the active sites of
enzymes get engaged in making covalent bonds
with glutaraldehyde resulting in the reduced availability of number of sites for reaction with substrate.
Effect of substrate concentration for
poly(An-co-Py)/ChOx bioelectrode
The photometric response of the poly(An-co-Py)/
ChOx bioelectrode in immobilized and solution phase
was studied with different concentration of cholesterol varying from 1 to 10 mM [Fig. 5(a)]. Velocity
(change in absorbance per minute) is almost linearly
proportional to the cholesterol concentration upto
about 10 mM where after it reaches a saturation point.
The apparent Km value of the poly(An-co-Py)/ChOx
bioelectrode was obtained as 4 mM. Figure 4(b) shows
Figure 9 Amperometric response of poly(An-co-Py)/
ChOx bioelectrode as a function of pH using cholesterol (4
mM) in phosphate buffer (50 mM, pH 7.0).
Journal of Applied Polymer Science DOI 10.1002/app
the UV spectra of different cholesterol concentrations
and the peak obtained at 240 nm corresponds to cholestenone formation [eq. (2)].
Enzyme loading on poly(An-co-Py) film
Figure 6(a,b) exhibits the UV spectra of ChOx
obtained in solution and immobilized phase indicating increased activity of ChOx with increase in
enzyme units (U/ml).
Study of pH variation on the poly(An-co-Py)/ChOx
bioelecrode
pH can affect the activity of enzyme by changing the
structure or by changing the charge on substrate
Figure 10 Amperometric response of poly(An-co-Py)/
ChOx (-l-), PANI (-~-), and PPy (-^-) bioelectrodes as a
function of cholesterol concentration (1–10 mM) using
phosphate buffer (50 mM, pH 7.0).
APPLICATION OF CONDUCTING POLYANILINE-co-PYRROLE FILM
3217
TABLE I
Effect of Interferents on the Amperometric Response (mA/cm2) of Poly(An-co-Py)/ChOx bioelectrode
Electrode
Cholesterol
concentration
(4 mM)
Cholesterol
(4 mM) þ Lactate
(2 mM)
Cholesterol
(4 mM) þ uric
acid (0.2 mM)
Cholesterol
(4 mM) þ glucose
(5 mM)
Poly(An-co-Py)
1.10
1.01
1.40
1.32
binding or catalysis. Figure 7 shows the absorbance
change between the pH range of 5.5–8.5 for poly(Anco-Py)/ChOx bioelectrode and in solution phase
resulting in a bell-shaped profile. Absorbance
increases with increase in pH range (pH 5.5–7.0) giving rise to a broad peak, whereas the value of absorbance decreases with the increase in pH beyond
7.5. It appears that at the low pH (5.5), negatively
charged enzyme (Enz ) protonates and loses its negative charge (e ): Enz þ Hþ?EnzH. At high pH
(8.5), positively charged substrate (SHþ) ionizes and
loses its positive charge: SHþ?S þ Hþ. Interaction
of SHþ and Enz at extreme pH values will result in
the reduction of the effective concentration of Enz
and SHþ, which in turn will reduce the value of the
absorbance. The optimum pH (Fig. 7) is obtained
between 7.0 and 7.5 in free and in immobilized state.
Effect of temperature on poly(An-co-Py)/ChOx
bioeletrode
The thermal stability of poly(An-co-Py)/ChOx bioelectrode enzyme has been studied by measuring the absorbance at different temperatures ranging from 26 to
438C [Fig. 8(a)] in the presence of cholesterol (4 mM)
and phosphate buffer (50 mM, pH 7.0). It has been
observed that the rate of reaction increases with temperature up to 338C and the optimum temperature
range was obtained at 33–368C owing to increased kinetic energy of the reacting molecules. Figure 8(b)
shows variation of log (absorbance) as a function of reciprocal temperature (Arrehenius plot). The activation
energy of poly(An-co-Py)/ChOx bioelectrode has been
calculated using the following equation.
dðlog kÞ
Ea
¼
dt
2:303RT
(4)
Slope ¼ Ea/2.303RT, where Ea is the activation energy,
R the gas constant, and T is the temperature. The calculated activation energy observed at lower temperature (368C) was about 73 kJ/mol and beyond this temperature the activation energy is much higher than the
lower temperature revealing that poly(An-co-Py)/
ChOx bioelectrode has the highest activity in the
range of 26–368C. The storage stability of the poly(Anco-Py)/ChOx bioelectrode was found to be about 10
weeks when stored at 48C.
TABLE II
Characteristics of Conducting Polymer Based Cholesterol Biosensors
Electrode
used
Pt Prussian
Blue
polypyrrole
Polypyrrole/
PVS
Polypyrrole/
PVS
Polypyrrole/
DBS
Polyaniline
Sensing element
Cholesterol oxidase,
chytochrome
P450seck 201E
Cholesterol oxidase,
cholesterol esterase
Cholesterol oxidase,
cholesterol esterase
Cholesterol oxidase,
potassium ferricyanide
Cholesterol oxidase,
cholesterol esterase
Polyaniline
Cholesterol oxidase,
cholesterol esterase,
peroxidase
Polypyrrole
Cholestrol oxidase,
Ferrocene monocarboxylic
acid
Poly (An-co-Py) Cholesterol oxidase
Immobilization
techniques
Entrapment
Linearity
(mM)
Shelf-life Sensitivity
(days) (mA/mM) Reference
Amperometric
25
0.441
39
1–8
Optical
30
–
55
1–8
Amperometric
60
0.15
30
2–8
Amperometric
90
–
40
Covalent linkage
1.29–12.93 Amperometric
45
2.9 10
Covalent linkage
1.29–12.93 Optical
45
1.62
16
–
56
Electrochemical
entrapment
Electrochemical
entrapment
Physical adsorption
0.025–0.35
Transducer
used
Electrochemical
entrapment
0.3
Amperometric
10
Covalent linkage
1–10
Amperometric/
optical
75
5
15
0.93 102 Present
work
Journal of Applied Polymer Science DOI 10.1002/app
3218
SOLANKI ET AL.
Amperometric studies of poly(An-co-Py)/ChOx
bioelectrode
References
Amperometric response is based on the measurement of current generated by dissociation of H2O2
produced in eq. (2)
H2 O2 !2Hþ þ O2 þ 2e
(5)
Figure 9 shows the effect of pH on amperometric
response of poly(An-co-Py)/ChOx bioelectrode in the
presence of phosphate buffer (50 mM). The optimum
pH is observed at pH 7.0. Figure 10 shows the effect
of cholesterol concentration on the amperometric
response of poly(An-co-Py)/ChOx, PANI/ChOx and
PPy/ChOx bioelectrodes with the range of 1–10 mM.
The sensitivity of these poly(An-co-Py)/ChOx, PANI/
ChOx and PPy/ChOx bioelectrodes was found to be as
93.3, 69.0, and 32.2 mA/mM, respectively.
Interference studies for poly(An-co-Py)/ChOx
bioelectrode
The effect of interferents (uric acid, lactate and glucose) has been studied on the amperometric
responses of poly(An-co-Py)/ChOx bioelectrode by
adding the normal physical concentration (uric acid
(0.2 mM); lactate (2 mM); and glucose (5 mM) in the
reaction mixture. It has been found that the presence
of interferents have negligible effect on the current
obtained (Table I).
Table II gives the comparison of the characteristics
of cholesterol biosensor based on copolymer [poly
(An-co-Py)], present work and homopolymers viz
PPy and PANI as reported in literature.
CONCLUSIONS
It has been shown that ChOx can be immobilized
onto electropolymerized poly(An-co-Py) film. The
sensitivity of poly(An-co-Py)/ChOx bioelectrode has
been achieved as 93.3 mA/mM, which is much higher
than PANI/ChOx (69.0 mA/mM) and PPy/ChOx
(32.2 mA/mM). These poly(An-co-Py)/ChOx bioelectrodes have response time of 30 s with the stability of 70 days. The presence of interferents such as
glucose, uric acid, and lactate in solution does not
alter the observed amperometric response. Experiments are being conducted to estimate the cholesterol
concentration in serum as well as blood samples
using the poly(An-co-Py)/ChOx bioelectrode.
We are grateful to Dr. Vikram Kumar, Director, National
Physical Laboratory, New Delhi, for his keen interest, and
encouragement to carry on this research work. We thank
Dr. S.P. Singh, Mr. Sunil K. Arya, and Ms. Kavita Arora
for interesting discussions.
Journal of Applied Polymer Science DOI 10.1002/app
1. Harrison, T. R. Harrison, Principles of Internal Medicine, Vol.
II; McGraw-Hill: New York, 1998.
2. NIH Consensus Conference, Triglycerides, High-density Lipoprotein and Coronary Disease, J Am Med Assoc 1993, 269, 505.
3. Wotherspoon, A. T. L.; Ansell, R. O.; Books, C. J. W. J Steroid
Biochem Molecular Biology 2000, 72, 169.
4. Nauck, M.; Marz, W.; Haas, B.; Wieland, H. Handbook of Electrophoresis; CRC Press: Boca Raton, FL, 1980; Vol. 1, p 78.
5. Charpentier, L.; Murr, N. E. I. Anal Chim Acta 1995, 318,
89.
6. Stadtmam, T. C. In Colowic, S.; Kaplan, N., Eds. Academic
Press: New York, 1957; p 392.
7. Abell, L. L.; Levy, B. B.; Brodie, B. B.; Kendall F. E. In Methods
of Enzymology; Seligon, D., Ed.; Academic Press: New York,
1958; p 26.
8. Brahim, S.; Narinesingh, D.; Guiseppi-Elie, A. Biosens Bioelectron 2002, 17, 53.
9. Zak, B. Am J Clin Pathol 1957, 27, 583.
10. Karube, I.; Hara, K.; Matsuoka, H.; Suzuki, S. Anal Chim Acta
1982, 139, 127.
11. Chaubey, A.; Malhotra, B. D. Biosens Bioelectron 2002, 17,
441.
12. Malhotra, B. D.; Chaubey, A.; Singh, S. P. Anal Chim Acta, to
appear.
13. Malhotra, B. D.; Chaubey, A. Sens Actuat B 2003, 91, 117.
14. Gerard, M.; Chaubey, A.; Malhotra, B. D. Biosens Bioelectron
2002, 17, 345.
15. Singh, S.; Solanki, P. R.; Pandey, M. K.; Malhotra, B. D. Anal
Chim Acta 2006, 568, 126.
16. Singh, S.; Solanki, P. R.; Pandey, M. K.; Malhotra, B. D. Sens
Actuat B 2006, 115.
17. Vidal, J. C.; Garcia-Ruiz, E.; Castillo, J. R. J Pharm Biomedical
Anal 2000, 24, 51.
18. Kumar, A.; Malhotra, B. D.; Grover, S. K. Anal Chim Acta
2000, 414, 43.
19. Kumar, A.; Pandey, R. R.; Brantley, B. Talanta 2006, 69, 700.
20. Li, J.; Peng, T.; Peng, Y. Electroanal 2003, 15, 1031.
21. Ayra, S. K.; Solanki, P. R.; Singh, R. P.; Pandey, M. K.; Datta,
M.; Malhotra B. D. Talanta 2006, 69, 918.
22. Gobi, K. V.; Mizutani, F. Sens Actuat B 2001, 80, 272.
23. Gilmartin, M. A. T.; Hart, J. P. Analyst 1994, 119, 2331.
24. Situmorang, M.; Alexander, P. W.; Hibbert, D. B. Talanta 1999,
49, 639.
25. Kouassi, G. K.; Irudayara, J.; McCarty, G. J Nanobiotechnol
2005, 1.
26. Pena, N.; Ruiz, G.; Reviejo, A. J.; Pingarron, J. M. Anal Chem
2001, 73, 1190.
27. Sharma, A. L.; Singhal, R.; Kumar, A.; Pande, R. K. K.;
Malhotra, B. D. Biotechnol Bioeng 2004, 85, 277.
28. Arora, K.; Chaubey, A.; Singhal, R. Singh, R. P; Pandey, M. K.;
Samanta, S. B.; Chand, S.; Malhotra, B. D. Biosens Bioelectron
2006, 21, 1777.
29. Campuzao, S.; Galvez, R.; Pedrero, M.; De Villena, F. J. M.
J Electroanal Chem 2002, 562, 92.
30. Singh, S.; Chaubey, A.; Malhotra, B. D. Anal Chim Acta 2004,
502, 229.
31. Chaubey, A.; Pandey, K. K.; Singh, V. S.; Malhotra, B. D. Anal
Chim Acta 2000, 407, 97.
32. Kajiya, Y.; Tsuda, R.; Yoneysms, H. J Electroanal chem 1991,
301, 155.
33. Malhotra, B. D.; Ghosh, S.; Chander, R. J Appl Polym Sci 1990,
40, 1049.
34. Chaubey, A.; Pande, K. K.; Pandey, M. K.; Singh, V. S. Appl
Biochem Biotech 2001, 96, 239.
35. Sharma, A. L.; Annapoorni, S.; Malhotra, B. D. Current Appl
Phys 2003, 3, 239.
APPLICATION OF CONDUCTING POLYANILINE-co-PYRROLE FILM
36. Prabhakar, N.; Arora, K.; Singh, S. P.; Pandey, M. K.,
Singh, H.; Malhotra, B. D. Anal Chim Acta 2007, 1, 84.
37. MacDiarmid, A. G.; Chiang, J. C.; Richter, A. F.; Epstein, A.
J Synth Met 1987, 18, 285.
38. Cooper, J. C.; Hammerle, M.; Schuhmann, W.; Schmidt, H. L.
Biosens Bioelectron 1993, 8, 65.
39. Vidal, J. C.; Espuelas, J.; Garcia-Ruiz, E.; Castillo, J. R. Talanta
2004, 64, 655.
40. Kumar, A.; Chaubey, R. A.; Grover, S. K.;. Malhotra, B. D.
J Appl Polym Sci 2001, 82, 3486.
41. Vengatajalabathy Gobi, K.; Fumio Mizutani. Sens Sensors B
2001, 80, 272.
42. Lin, C. C.; Yang, M. C. Biomaterials 2003, 24, 549.
43. Zotti, G.; Musiani, M.; Zecchin, S.; Schiavon, G. Chem Mater
1998, 10, 480.
44. Cakmak, G.; Kucukyavuz, Z.; Kucukyavuz, S. Synth Met 2005,
151, 10.
45. Suman; Singhal, R.; Sharma, A. L.; Malhotra, B. D.; Pundir,
C. S. Sens Actuat B 2005, 107, 768.
3219
46. Talu, M.; Kabasakaloglu, M.; Oskoui, H. R. J Polym Sci A:
Polym Chem 1996, 34, 2981.
47. Encyclopedia of Polymer Science and Engineering; Kroschwitz, J. I., Ed. Wiley: New York, 1985; Vol. 4, p 193.
48. Sharma, A. L.; Saxena, V.; Annapoorni, S.; Malhotra, B. D.
J App Polym Sci 2001, 81, 1460.
49. Lim, V. W. L.; Kang, E. T.; Neoh, K. G.; Ma, Z. H.; Tan, K. L.
Appl Surf Sci 2001, 181, 317.
50. Kim, J. W.; Cho, C. H.; Liu, F.; Choi, H. J.; Joo, J. Synth Met
2003, 17, 135.
51. Sari, B.; Talu, M. Synth Met 1998, 94, 221.
52. Fusalba, F.; Belanger, D. J Phys Chem B 1999, 103, 9044.
53. Bongiovanni, C.; Ferri, T.; Poscia, A.; Varalli, M.; Santucci, R.;
Desideri, A. Bioelectrochemistry 2001, 54, 17.
54. Pandey, S. S. Thesis, University of Gorakhpur, 1995.
55. Singh, S.; Chaubey, A.; Malhotra, B. D. J Appl Polym Sci 2004,
91, 3769.
56. Vidal, J. C.; Garcia, E.; Castilo, J. R. Anal Sci 2002, 18,
537.
Journal of Applied Polymer Science DOI 10.1002/app