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REVIEW 1
2
Electrochemical enzymatic biosensors based on metal micro-/nanoparticles-3
modified electrodes: a review 4
5
Nina D. Dimcheva*, Elena G. Horozova 6
7
Department of Physical Chemistry, Plovdiv University, 24, Tsar Assen Street, BG-4000 8
Plovdiv, Bulgaria 9
10
Received 17 March 2014; Revised 6 June 2014; Accepted 6 June 2014 11
12
13
The functions of metal structures of micro- or nano-dimensions in the sensing 14
mechanisms of amperometric enzyme-based biosensors are considered in the light of the 15
principles of detection of the latter. The applications of metal mono- or bimetallic 16
nanoparticles-modified materials as catalytic electrodes in the fabrication of first-generation 17
and the role which metal nanoparticles play in promoting or enhancing the electron transfer 18
rates in third-generation electrochemical biosensors are reviewed. Some examples of gold 19
NPs functionalised with enzymes via gold–thiol chemistry as a strategy for enzyme 20
immobilisation and spatial orientation when developing amperometric biosensors are also 21
discussed. 22
2014 Institute of Chemistry, Slovak Academy of Sciences 23
24
Keywords: nanoparticles, biosensors, electrocatalysis, direct electron transfer (DET) 25
26
27
Introduction 28
29
The first historical proof of the fabrication of metal nanoparticles dates back to the 30
times of the Roman Empire, as evidenced by an artefact currently in the British museum – the 31
dichroic Lycurgus Cup. Due to the incorporation of gold (Au) and silver (Ag) nanoparticles in 32
*Corresponding author, e-mail: [email protected]
2
the glass, its colour appears greenish in a reflected light or ruby-red when light is transmitted 33
through the glass (Freestone et al., 2007). In the Middle Ages, Au nanoparticles of different 34
sizes were used to produce intensively-coloured glass for the stained-glass windows of the 35
cathedral churches of Europe, e.g. Notre Dame de Paris (Aili & Liedberg, 2010). Nowadays, 36
the ever-increasing interest in fabricating metal nanoparticles results from the diversity of 37
their possible applications,, ranging from tumour diagnosis (Wilson, 2008) through 38
electrocatalysts for energy production (Alexeyeva et al., 2006; Bron, 2008; El-Deab, 2010; 39
El-Deab & Ohsaka, 2002a, 2003, 2006, 2007; El-Deab et al., 2005a; Erikson et al., 2009; 40
Lima et al., 2010; Plyasova et al., 2006; Ramos et al., 2010; Sekol et al., 2013) to plasmonic 41
resonance-based sensing (Chandrasekharan & Kamat, 2001; Freeman et al., 1996; Gartia et 42
al., 2013; Ghosh & Pal, 2007; Ishikawa et al., 1996; Jäckel & Feldmann, 2012), e.g. surface 43
plasmon resonance (SPR) or surface-enhanced Raman scattering (SERS). This broad 44
spectrum of applications for nanosized metal particles predetermines the diversity of the 45
protocols for their fabrication, such as wet chemical techniques (Bharathi & Lev, 1997; Sau & 46
Rogach, 2012; Turkevich & Kim, 1970; Turkevich et al., 1951, 1953), photo-decomposition 47
(Krasnansky et al., 1991) and thermal decomposition of salts (Mao et al., 2013; Xue et al., 48
2001), vapour deposition (Whyman, 1996), sputtering (Ishikawa et al., 1996; Mizsei et al., 49
1998; Terauchi et al., 1995), acoustic (Mizukoshi et al., 1997) or radio-frequency-based 50
(Terauchi et al., 1995) methods and miscellaneous electrochemical-deposition techniques 51
(Chikae et al., 2006; Dai & Compton, 2006; Dobbs et al., 2006; El-Deab, 2010; El-Deab & 52
Ohsaka, 2002a; El-Deab et al., 2005b, 2006; Fu et al., 2010; Gao et al., 2005; Gloaguen et al., 53
1999; Ilias et al., 2013; Ma et al., 2009; Plyasova et al., 2006; Quinn et al., 2005; Sau & 54
Rogach, 2012; Tang et al., 2012; Wang et al., 2008, 2009), etc. Due to the numerous 55
advantages which they offer, e.g. the opportunity to tune the particle size and distribution 56
(Plyasova et al., 2006), improved mechanical stability (El-Deab, 2010) and better electrical 57
contact (El-Deab & Ohsaka, 2007; El-Nagar et al., 2013) with the underlying substrate, 58
electrochemical techniques for the deposition of metal nanoparticles on conductive supports 59
are favoured for producing electrocatalysts applicable in either electroanalysis (Zhang et al., 60
2013) or energy-producing devices (Alexeyeva et al., 2006; Bron, 2008; El-Deab, 2009; El-61
Deab & Ohsaka, 2002b, 2003, 2006, 2007; El-Deab et al., 2005a, 2005b, 2005c, 2006; 62
Erikson et al., 2009; Sekol et al., 2013; Shao et al., 2013). 63
Biosensor technologies represent one of the research areas in which nano-materials 64
play important roles in the sensing process. As defined by IUPAC (IUPAC, 2005–2014), a 65
biosensor is a device that makes use of specific biochemical reactions catalysed by a 66
3
biological element for molecular recognition, such as isolated enzymes, antigens/antibodies, 67
nucleic acids, tissues, organelles or whole cells in order to detect chemical compounds, 68
usually by electrical, thermal or optical signals. 69
Electrochemical biosensors possess two main advantages over the other types of 70
biosensors: (i) susceptibility to miniaturisation, and (ii) facility of operation with electrical 71
response – current, potential, or conductivity, which could be easily processed using relatively 72
inexpensive instrumentation. 73
Depending on the type of the measurable response, they could be sub-divided into 74
three types: (i) amperometric – the measurable response is the current, which varies upon 75
addition of the enzyme substrate; (ii) potentiometric – the potential difference between the 76
working and the reference electrode measured under equilibrium conditions (no current 77
flowing) is the electrode response; (iii) impedimetric – the impedance of the electrode is the 78
measurable response. Biosensors measuring the conductivity changes upon the addition of the 79
enzyme substrate can be also considered in this group. 80
Among the electrochemical biosensors, enzyme-based amperometric biosensors 81
represent the most commonly used group; this functions on the basis of monitoring the current 82
variation at a polarised electrode, induced by the reaction/interaction of the bio-recognition 83
element with the analyte of interest. Furthermore, amperometric enzyme-based biosensors 84
can, on their part, be classified into three categories in accordance with the mode of action 85
(Montornes et al., 2008): (i) first-generation biosensors: the signal corresponds to the 86
electrochemical reaction of an active reagent (monitoring the decrease in the current) or 87
product (monitoring the increase in the current) that is involved in biochemical transformation 88
of the target compound; (ii) second-generation biosensors: the architecture of these biosensors 89
includes a redox mediator either freely diffusing or spatially confined on the electrode surface 90
(small molecular mass compounds, able to effectively shuttle electrons between the electrode 91
surface and the enzyme active site); in this mode, the concentration of the target analyte 92
taking part in the biochemical reaction is proportional to the response resulting from the 93
oxidation/reduction of the mediator; (iii) third-generation biosensors: the bio-component is 94
capable of directly (mediators-free) exchanging electrons between the active site of the 95
enzyme and the transducer (Ghindilis et al., 1997; Gorton et al., 1999); consequently, the 96
concentration of analyte is directly proportional to the redox current generated at the polarised 97
electrode. The third-generation biosensors possess the advantages of simplicity of 98
construction, exclusion of additional supportive substances (e.g. mediator), increase in 99
4
specificity for towards target analyte, removal of interferences due to the usually low 100
polarisation potential at the working electrode, etc. 101
In the past decade, several review papers comprehensively discussed the uses of the 102
magnetic, optical, chemical and physical properties of nanoparticles of different natures in 103
bioanalytical techniques (de Dios & Díaz-García, 2010; Doria et al., 2012; Luo et al., 2006) 104
such as immune-assay, plasmonic biosensors, nucleic acids-based sensors, etc. The current 105
review focuses in particular on the roles played by metal nano- and microparticles-modified 106
electrodes in the first- and third-generation amperometric biosensors – they may have 107
electrocatalytic properties towards the redox transformation of a reaction product or reagent, 108
may bind to the biocatalyst, thereby retaining it closer to the electrode surface, they may also 109
affect enzyme-orientation or reduce the distance between its active site and the electrode 110
surface. Second-generation biosensors will be excluded from this review since they require a 111
redox-active species able to switch between the oxidised and the reduced form in order to 112
mediate the electron transport between the electrode and the enzyme active site. 113
114
115
First-generation biosensors 116
117
The simplest way to construct an enzyme electrode working for the first-generation 118
(1G) amperometric biosensors is to put a biocatalyst in contact with a catalytic electrode. As 119
stated above, the detection of the analyte is based on the monitoring of the current variation 120
due to the redox transformation of either an electroactive product or a reagent of the 121
biocatalysed process. Accordingly, a hydrogen peroxide-producing or -consuming enzyme or 122
protein is often used as a biocatalyst, although two non-oxidative enzymes, urease and 123
acetylcholinesterase (AChE), are also known to work for the first-generation amperometric 124
biosensors. In this case, the metal nano- or microparticles (NPs or MPs)-modified transducer 125
may function as either the electrocatalysts of the response-generating process or they act as 126
anchors to which the enzyme is attached. 127
128
129
Biosensors based on detection of enzymatically produced hydrogen peroxide 130
131
Hydrogen peroxide (H2O2) is usually generated as a by-product in most of the 132
enzyme-catalysed oxidative reactions, where its quantity is directly proportional to the 133
5
concentration of the analyte of interest – the enzyme substrate. H2O2 is the electrochemically 134
active compound and might be electrocatalytically oxidised on solid platinum (Pt) electrodes 135
at an applied potential of 0.6 V (vs Ag/AgCl) (Charmantray et al., 2013). Several examples, 136
however, have shown that the electro-oxidation of enzymatically generated H2O2 onto the 137
electrodes modified with Pt NPs (Olivia et al., 2004), Pt NPs–CNT composite (Zhao et al., 138
2007), Ir NPs (Hsu et al., 2010) or with bimetallic Pd/Pt microdeposits (Horozova et al., 139
2000) affords a more sensitive determination than the bulk Pt electrode. 140
The main drawback of this type of sensing is that, at the operating potentials at which 141
the electrooxidation of H2O2 takes place (i.e. above 0.5 V), organic compounds such as 142
ascorbic or uric acids, some neurotransmitters, antioxidants, pigments, drugs, etc., normally 143
present in the real samples, could be co-oxidised, thereby contributing to the electrode 144
response, which consequently results in overestimated analyte levels. One strategy to 145
overcome this issue is to cover the electrode surface with a perm-selective membrane to 146
restrict the access of the potentially interfering compounds (Kirwan et al., 2007). A much 147
more successful strategy, however, is to electrochemically reduce the peroxide at operating 148
potentials close to 0 V over electrodes modified with metal – mostly iron, hexacyanoferrates 149
(Karyakin, 2001), such as Prussian Blue (also known as artificial peroxidase). Although the 150
preparation of these modifiers is easy, their applications are rather limited because they form a 151
stable film only under acidic conditions, whilst at neutral and slightly alkaline pH they 152
dissolve and tend to lose their catalytic activity. 153
An alternative to the hexacyanoferrate-modified transducers for first-generation 154
biosensors which provides a stable electrode response over a pH range of 3 to 11, was 155
proposed previously (Dimcheva et al., 2002a, 2002b). These first-generation biosensors were 156
based on conventional graphite electrodes onto which a thin layer of bimetallic catalytic 157
phase, consisting of palladium (Pd) and Pt, was allowed to grow through electrodeposition at 158
a constant potential. Subsequent studies showed that the electrocatalytic activity towards 159
H2O2 reduction depended on the ratio at which the two metals were deposited (Dodevska et 160
al., 2006; Nagaiah et al., 2013). Hence, the biosensors thus produced exhibited a practically 161
interference-free response towards the target analyte (Dodevska et al., 2010; Horozova et al., 162
2009) due to the near-zero operating potential. Detailed SEM studies of the electrodeposited 163
bimetallic phases (Nagaiah et al., 2013) demonstrated that the deposits consisted of nanosized 164
crystallites which formed bigger agglomerates upon piling up, the shape and dimensions of 165
which were closely dependent on the ratio of the two metals. In the same study, XRD 166
confirmed that the two co-deposited metals formed alloys, thus explaining why their catalytic 167
6
activity towards H2O2 electroreduction greatly exceeded those of the solely Pd or Pt deposits. 168
Several examples of first-generation biosensors where the detection principle resides in the 169
electroreduction of the enzymatically generated H2O2 are summarised in Table 1. As seen 170
from the examples presented, in all the cases the detection of H2O2 is performed over the 171
potential range of −0.1–0.2 V, in neutral buffers. Under such operating conditions, it is 172
scarcely conceivable that some of the substances normally present in real samples, such as 173
glutathione or other antioxidants, neurotransmitters, phenols, etc. might be electrochemically 174
active and contribute to the electrode response. Therefore, as discussed above, the reduced 175
working potentials warrant a practically interference-free assay of the target analyte. 176
177
178
Two further examples of first-generation biosensors 179
180
Urease is a hydrolase-type enzyme which catalyses the hydrolysis of urea to 181
ammonium and bicarbonate ions according to the equation (Singh et al., 2008): 182
183
NH2CONH2 + 3H2O 2NH4 + OH– + HCO3
urease –+ (1) 184
185
Because the pH of the medium changes upon release of these ions, urease-based 186
potentiometric biosensors are quite commonly used for urea monitoring. This type of 187
biosensors was extensively discussed in two recent reviews (Dhawan et al., 2009; Singh et al., 188
2008), and will not be considered here as being beyond the scope of this review. 189
Electrodeposited rhodium nanoparticles were recently reported as exhibiting a 190
significant catalytic effect on the electro-oxidation of enzymatically liberated ammonia 191
(Velichkova et al., 2011) by the urease-based amperometric biosensor. A similar effect was 192
reported by Jia et al. (2011) due to the Pt-nanoflowers-decorated transducer of their biosensor 193
for urea. Some other nanoparticles-modified electrode materials have been found to contribute 194
to increased sensitivity of the determination, e.g. Ag NPs (Crespilho et al., 2009), Au NPs 195
(Do et al., 2011), or Au NPs-polymer composite material (Tiwari et al., 2009); however the 196
role of the metal nanoparticles is not justified. 197
Acetylcholinesterase (AChE) also belongs to the hydrolases group; it plays a key role 198
in the nervous system of mammalian organisms as one of the factors responsible for 199
transmitting nerve impulses to the cholinergic synapses (Arduini et al., 2010). It may readily 200
7
be inhibited by a variety of toxic compounds: heavy metals, nicotine and neuroparalytic gases, 201
medications for the treatment of Alzheimer’s or Parkinson’s diseases, or pesticides 202
(organophosphorous and carbamate types). The enzyme catalyses the hydrolysis of 203
acetylcholine to choline and acetic acid. Since none of these reaction products is 204
electrochemically active, acetylthiocholine is often used as an enzyme substrate (Pandey et 205
al., 2000). The principle of the detection of AChE enzyme inhibitors using acetylthiocholine 206
as the enzyme substrate lay in the following three stages (Arduini et al., 2010; Stoytcheva et 207
al., 1998). Stage 1: AChE catalyses the hydrolysis of acetylthiocholine to thiocholine and 208
acetic acid at ambient temperature: 209
210
Acetylthiocholine + H2O Thiocholine + CH3COOHAChE
(2) 211
212
Both the non-enzymatic and the enzymatic hydrolysis of acetylthiocholine to thiocholine 213
depended on the pH of the solution and were found to slow down in basic media; stage 2: 214
electrochemical oxidation of thiocholine onto the electrode surface: 215
216
2Thiocholine Disulphide + 2H+ + 2e–anodic oxidation
(3) 217
218
The process takes place with the transfer of one electron from the thiocholine and the 219
subsequent dimerisation of the intermediate to disulphide. When conventional electrodes are 220
used (Martorell et al., 1994; Marty et al., 1992, 1995), thiocholine electro-oxidation proceeds 221
at potentials greater than 0.7 V (vs SCE); stage 3: upon the inhibition of the AChE enzyme, 222
the thiocholine oxidation current decreases. The extent of enzyme inhibition is determined in 223
accordance with the equation: 224
225
%100InhibitionS
IS
I
II (4) 226
227
where IS is the steady-state electrode response to the control solution (at the large thiocholine 228
concentration present); II is the enzyme electrode response at the same thiocholine 229
concentration plus a given inhibitor concentration. 230
A simple and versatile technique for enzyme immobilisation based on gold-thiol 231
chemistry is the spontaneous chemisorption of the sulphur-containing organic compound 232
8
(cysteamine, mercaptobenzothiazole, etc.) on the colloid gold-modified electrode surfaces, 233
thereby forming a self-assembled monolayer, SAM, to which the AChE enzyme is attached 234
through intermolecular complexes (Du et al., 2008, 2009; Liu & Lin, 2006; Pedrosa et al., 235
2007; Somerset et al., 2009). This immobilisation approach provides conformational 236
flexibility of the enzyme and hence assures a more efficient biocatalytic process, albeit 237
enabling the formation of a thicker diffusion layer that reduces electrode sensitivity. An even 238
simpler method for AChE immobilisation is to chemisorb it directly on the surface of Au NPs 239
without the need for additional thiolated linkers (Du et al., 2007a, 2007b; Marinov et al., 240
2010; Shulga & Kirchhoff, 2007), since its protein shell contains terminal SH-groups. The 241
obvious challenge in this case, however, entails retaining the enzyme-functionalised NPs on 242
the electrode, which is implemented by either their incorporation in a porous membrane 243
(Marinov et al., 2010) or by inclusion in a composite film cast on the surface of the working 244
electrode (Du et al., 2007a, 2007b), thereby yielding a stable but thick catalytic layer that 245
triggers additional diffusion limitations. Direct growth of Au NPs on the surface of a compact 246
graphite electrode through electrodeposition allows for a much better electrical contact 247
between the two conductive materials, resulting in a much improved electrode sensitivity 248
towards thiocholine (Dimcheva et al., 2013a). Self-assembly of the AChE enzyme to the Au 249
NPs thus deposited yielded a membrane-free and, hence, fast-responding AChE-based 250
biosensor with a storage stability exceeding one month. 251
252
253
Direct electron transfer promoted by metal nanoparticles and its application in third-254
generation biosensors 255
256
The role of metal nanosized particles in third-generation biosensors is much more 257
complex, since it is believed that, in many cases, they promote the direct electron transfer 258
(DET) process between the electrode and the enzyme active site by shortening the distance 259
between them or by orienting the enzyme upon its immobilisation (Liu et al., 2003; Pingarrón 260
et al., 2008). The most systematically DET-promoting abilities of Au NPs have been explored 261
in relation to the development of cathodes for the enzymatic biofuel cells bearing multi-262
copper oxidases–laccases (Brondani et al., 2013; Krikstolaityte et al., 2014; Rahman et al., 263
2008) or bilirubin oxidases (Mano & Edembe, 2013; Pita et al., 2013), as catalysts for ORR 264
(oxygen reduction reaction). 265
9
Some of the earlier reports on the direct electrochemistry promoted by the 266
nanoparticles of noble metals concerned haem-containing redox proteins such as myoglobin 267
(Dimcheva et al., 2011; Liu & Ju, 2003), haemoglobin (Zhao et al., 2006) and the larger 268
molecule of the peroxidase enzyme (Di et al., 2005). Catalase also belongs to the haem-269
containing enzymes; it consists of four sub-units forming a tetramer with the huge molecular 270
mass of 275 kDa and its active site was found to be buried deep in the protein shell; all these 271
conditions suggest the electrochemical inactivity of the enzyme. Huang et al. (2011), 272
however, observed direct electrochemistry and electrocatalysis with catalase immobilised on 273
an Au NPs-amine-functionalised graphene composite, most probably due to the reduced 274
distance between the enzyme active centre and the electrode. In all of the examples discussed 275
above, where the direct electrochemistry of haem-containing proteins/enzymes was 276
established, it was further used to construct third-generation amperometric biosensors for 277
H2O2. 278
Although glucose oxidase, a flavoprotein with the active site placed deeply inside the 279
protein globule, is considered to be electrochemically inactive, several recent studies have 280
reported on its direct electrochemistry and electrocatalysis applicable in third-generation 281
glucose biosensors (Cui et al., 2014; Haghighi & Tabrizi, 2013; Holland et al., 2011; Liu & 282
Huang, 2012; Palanisamy et al., 2014; Ragupathy et al., 2009; Xu et al., 2012; Yu et al., 283
2014). In connection with this, a very successful strategy to greatly increase the biosensor 284
sensitivity towards its substrate (glucose) by electrically wiring the enzyme via highly ordered 285
nanostructures has been developed by Adeloju and co-workers (Cui et al., 2014; Xu et al., 286
2012). Their glucose nanobiosensor arrays exhibited extraordinary operational characteristics 287
(Cui et al., 2014), e.g. a limit of detection below 1 µM and a linear dynamic range spanning 288
three orders of magnitude (5–6000 µM) and the capacity to respond interference-free to 289
glucose in real samples. 290
Another interesting example of a flavoenzyme believed to be electrochemically inert, 291
but exhibiting direct electrochemistry when immobilised on metal NPs-modified electrodes, is 292
cholesterol oxidase (Karimi et al., 2012; Zhu et al., 2013). Similarly, third-generation 293
cholesterol biosensors demonstrate low limits of detection, high sensitivity and excellent 294
selectivity towards the analyte of interest. 295
Au NPs were found to be useful in promoting DET processes even for the more 296
complex oxidative enzyme – the two-domain sulphite oxidase (Frasca et al., 2012). The 297
strong electrocatalytic effect on the oxidation of sulphite was the basis for constructing a fast-298
responding and highly sensitive third-generation sulphite biosensor. Analogously, direct 299
10
electrochemistry and electrocatalysis by chemisorbed ascorbate oxidase (a multi-copper 300
oxidase, MCO) triggered by Au NPs-modified electrodes was recently reported by our group 301
(Dimcheva et al., 2013b; Dodevska et al., 2013). It is generally believed that two-substrate 302
MCOs only work for third-generation biosensors towards oxygen reduction, due to the 303
internal electron transfer between the three active centres of these enzymes, and that they can 304
eventually oxidise their second substrate (bilirubin, phenols or L-ascorbate) solely under de-305
oxygenated conditions. The AOx enzyme chemisorbed on Au NPs, however, demonstrates 306
the somewhat unusual ability to work for the third-generation L-ascorbate biosensor even 307
under oxygenated conditions. It is possible that a part of the enzyme binds to the Au NPs in 308
close proximity to the ascorbate-linking site (T1), thereby creating a shortcut between it and 309
the underlying electrode which renders the internal electron transport a less favourable 310
pathway. Comparing the electrode response towards L-ascorbate in the absence and in the 311
presence of oxygen, it may be estimated that approximately 1/3 of the enzyme chemisorbs 312
onto the Au NPs in this unusual conformation. Comparative experiments have shown that, on 313
a flat solid gold electrode, the AOx enzyme chemisorbs, shows the ability to 314
electrochemically reduce oxygen, but does not electrocatalytically oxidise L-ascorbate under 315
aerated conditions (Dimcheva et al., 2014). 316
317
318
Conclusions 319
320
In brief, the most beneficial feature of the micro-/nanoparticles-modified transducers, 321
in view of the development of first-generation amperometric biosensors, is their 322
electrocatalytic activity towards the target compound, which is an electroactive either reagent 323
or product of the enzyme-catalysed process. In addition, when the modifiers are Au NPs or Pt 324
NPs, the nanostructures may serve as anchors to which the biocatalyst is attached, largely 325
using the gold–thiol or platinum–thiol chemistry. 326
DET is an exclusive feature of the oxidative enzymes/proteins: their active sites 327
consist of either metal clusters (e.g. Fe/S or Cu clusters) or redox molecules (haemin, FAD, 328
NADH, PQQ), which are buried in the protein shell. Achieving the direct electrochemistry of 329
the enzyme and electrocatalysis in the presence of its typical substrate is the necessary 330
prerequisite to construct third-generation biosensors with exclusive selectivity and greatly 331
improved operational characteristics. Metal NPs or MPs may trigger these two events or may 332
even provoke some unexpected modifications of the electrocatalytic activity. 333
11
334
335
Acknowledgements. The authors gratefully acknowledge the financial support received 336
from the Bulgarian National Science Fund (grant no. DVU-02/38) and the technical help 337
received from the student, Boris Dzhuvinov (Computer Science, University of Plovdiv). 338
339
340
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Table 1. First-generation amperometric biosensors with H2O2 electrocatalytic reduction as response-generating process 765
766
Analyte Immobilised enzyme Electrode modifier Ea/V Reference
Glucose Glucose oxidase Pd/Pt alloys (MPs) 0 Dimcheva et al. (2002b); Dodevska et al. (2006); Nagaiah et al. (2013)
Pt nanowires 0 Yang et al. (2006)
Fe NPs −0.1 Comba et al. (2010)
Pt NPs −0.1 Choi et al. (2007)
Pd NPs n.a. Lim et al. (2005)
Cholesterol Cholesterol oxidase CNT + Pt NPs n.a. Qiaocui et al. (2005)
Glutamate Glutamate oxidase Au NPs 0.135 Batra and Pundir (2013)
L-Lysine L-Lysine oxidase Au NPs + Pt NPs 0.2 Chauhan et al. (2013)
Xanthine Xanthine oxidase Pd/Pt alloys (MPs) −0.05 Dodevska et al. (2010); Horozova et al. (2009)
a) All operating potentials (E) were measured against Ag/AgCl; n.a. means not available. 767
768