enzymatic biosensors based on the use of metal oxide nanoparticles
TRANSCRIPT
REVIEWARTICLE
Enzymatic biosensors based on the use of metaloxide nanoparticles
Xinhao Shi & Wei Gu & Bingyu Li & Ningning Chen &
Kai Zhao & Yuezhong Xian
Received: 9 May 2013 /Accepted: 16 August 2013 /Published online: 29 August 2013# Springer-Verlag Wien 2013
Abstract Over the past decades, various techniques havebeen developed to obtain materials at a nanoscale level todesign biosensors with high sensitivity, selectivity and effi-ciency. Metal oxide nanoparticles (MONPs) are of particularinterests and have received much attention because of theirunique physical, chemical and catalytic properties. This re-view summarizes the progress made in enzymatic biosensorsbased on the use of MONPs. Synthetic methods, strategies forimmobilization, and the functions of MONPs in enzymaticbiosensing systems are reviewed and discussed. The article issubdivided into sections on enzymatic biosensors based on (a)zinc oxide nanoparticles, (b) titanium oxide nanoparticles, (c)iron oxide nanoparticles, and (d) other metal oxidenanoparticles. While substantial advances have been made inMONPs-based enzymatic biosensors, their applications to realsamples still lie ahead because issues such as reproducibilityand sensor stability have to be solved. The article contains 256references.
Keywords Metal oxide nanoparticles . Enzyme . Biosensor .
Zinc oxide . Titanium oxide . Iron oxide
Introduction
Over the past decades, nanomaterials have attracted extensiveinterests due to their importance in basic scientific researchand potential technological applications. From the point ofview of scientific research, it is well known that the physicaland chemical properties of materials at nanoscale are
obviously different from those of bulk materials because ofthe quantum size effect, small size effect, surface/interfaceeffect and macroscopic quantum tunneling effect.Nanoparticles or nanocrystals, as the fundamental units fornanostructured materials, play very important roles innanoscience. Specifically, metal oxide nanoparticles(MONPs) have attracted much attention for their optical,magnetic and electronic properties.
The fascinating size and shape dependence of physico-chemical properties make MONPs suitable for a wide varietyof applications such as catalysis, organic light emitting diodes,electrochemical energy storage, sensors, etc. It is well knownthat metal oxides have tremendous importance in the field ofheterogeneous catalysis. Debecker andMutin [1] reviewed theprogress of synthesis of MONPs based on non-hydrolytic sol-gel method for catalytical applications. Due to their excep-tional electronic properties, transition metal oxides have beenextensively studied for organic electronics applications.Meyer and coworkers [2] summarized the recent developmentof transition metal oxides such as MoO3, V2O5 and WO3 inorganic light emitting diodes and organic photovoltaic cells.Meanwhile, metal oxide nanostructures are promising elec-trode materials for lithium ion batteries and supercapacitors.Jiang and colleagues [3] reported the advances in metal oxide-based hybrid nanostructure for electrochemical energy stor-age. The emerging nanotechnology opens new exciting op-portunities to explore analytical applications of the nanostruc-tured metal oxide materials. Due to their special shapes,extraordinary chemical and physical properties, metal oxidenanostructures have great promise in the chemical and bio-logical sensing system. It is well known that MONPs not onlyhave high surface area, good biocompatibility and chemicalstability, but also display fast electron transfer ability. All thesefeatures make MONPs ideal immobilization matrices as wellas transduction platform and/or mediators. For example,Shaidarova [4, 5] conducted a series of researches on
X. Shi :W. Gu :B. Li :N. Chen :K. Zhao :Y. Xian (*)Department of Chemistry, East China Normal University,Shanghai 200062, Chinae-mail: [email protected]
Microchim Acta (2014) 181:1–22DOI 10.1007/s00604-013-1069-5
chemically modified electrodes using metal oxides as modi-fiers. The results indicate that metal oxides can improve thesensitivity the electrode obviously.
Nanofabricated metal oxides also have been successfullyapplied in the field of biosensing system. Recently, some re-views concentrated on nanostructured metal oxides based bio-sensors were published. For example, Haun [6] reviewed theuse of magnetic nanoparticles for detection of biomolecules andcells based on magnetic resonance effects. Xu and Wang [7]summarized the applications of magnetic micro/nano particlesin the development of immuno-, enzyme, DNA and aptamerelectrochemical biosensors. The application of nanostructuredZnO in the field of biosensing system also was reviewed [8, 9].Very recently, Solanki and coworkers [10] demonstrated theprogress of application of nanostructured metal oxide (NMO)in biosensors. They provided a comprehensive comment onenzymes, nucleic acids, antibodies and whole cell-based NMObiosensing system. However, until now, a review focus onenzymatic biosensors based on MONPs has not been reported.It is well known that enzymes and enzyme mimetics can offergreat amplification power through efficient catalytic turnover ofsubstrates. The combination of enzymes with MONPs couldprovide a versatile platform for biosensing with various signalreadout strategies, such as electrochemical, colorimetric, fluo-rimetric, chemiluminescence and so on. In this paper, we aim torepresent a comprehensive and critical review of the progressand future perspectives of MONPs based enzymatic biosensingsystem. The review is structured in accordancewith the kinds ofMONPs and is subdivided into sections on (a) zinc oxidenanoparticle-based enzymatic biosensors, (b) titanium oxidenanoparticle-based enzymatic biosensors; (c) iron oxidenanoparticle-based enzymatic biosensors, and (d) on other met-al oxide nanoparticle-based enzymatic biosensors. It should bepointed out that, in some MONPs based biosensing systems,the recognition mechanisms is not based on the direct reactionbetween enzyme and analyte, for example, iron oxidenanoparticles as enzyme mimetics and some examples ofimmunobiosensors. In order to make more comprehensiveunderstanding the roles of MNOPs in enzymatic biosensingsystem, above-mentioned contents were also involved in thisreview.
Zinc oxide nanoparticle based enzymatic biosensors
As a semiconductor material, nanostructured ZnO has re-ceived broad attention. Tremendous efforts have been madeto synthesize nanostructured ZnO, including solid–vapourphase thermal sublimation technique and wet-chemical syn-thesis. Recently, various strategies exploited to grow ZnOnanostructures were reviewed and these controllable syntheticmethods enabled the versatile applications in the fields of solarcells [11], sensors [12], photocatalysis [13], and luminescent
materials [14], etc. Figure 1 shows the typical TEM images ofZnO nanoparticles synthesized with controlled sizes and mor-phologies using [Zn(c-C6H11)2] as precursor at room-temperature [15].
As a biomimetic material, ZnO provides a versatile plat-form for biomolecules loading [16]. ZnO nanoparticles withhigh isoelectric point are suitable for the adsorption of low-isoelectric point enzymes for biosensor fabrication (Table 1).
A mediator-free Tyr biosensor based on ZnO nanoparticleswas developed by Li for the determination of phenolic com-pounds [31]. In this work, ZnO nanoparticles prepared by ahydrothermal method were dispersed in the chitosan solutionto form ZnO/chitosan matrix, and then Tyr was adsorbed onZnO nanoparticles by electrostatic interactions for phenolbiosensing. In addition, the direct electrochemistry of hemo-globin (Hb) [44], microperoxidase [45], GOx [17, 46], andHRP [28] were observed at ZnO nanoparticles modified elec-trode. In order to improve the conductivity and enhance theelectron transfer, Au nanoparticles [29, 30], reduced grapheneoxide [18] and MWCNTs [19] were modified on the surfaceof electrode with ZnO nanoparticles and the direct electrontransfer between the enzyme and electrode were realized.
Due to its simplicity and free pretreatment, electrochemicaltechniques have gainmuch interest for growing ZnO nanostruc-tures. Ahmad et al. [47] fabricated a cholesterol biosensor basedon Pt-ZnO nanomaterials, in which ZnO nanospheres wereelectrochemical deposited on the glassy carbon (GC) electrode.As shown in Fig. 2, the morphology characterizations demon-strate ZnO nanospheres with diameter over the range of 10–200 nm. The doped Pt nanoparticles assembled on the surfaceof the first spherical agglomerate and finally the nanocompos-ites display a fullerene-like spherical shape with diameters ofabout 50–200 nm. Functionalized with ChOx by physicaladsorption, the biosensor exhibits a very high sensitivity of1886.4 mA M−1 cm−2 to cholesterol with a response time lessthan 5 s. Deshpande [48] developed a potentiometric glucosebiosensor using core-shell nanocomposite based on zinc oxideencapsulated chitosan-graft-poly(vinyl alcohol) (ZnO/CHIT-g-PVAL). In this system, ZnO/CHIT-g-PVALwas synthesized bywet-chemical method. The nanocomposite was coated on thesurface of indium-tin oxide (ITO) glass substrate and GOx wasfurther immobilized through the electrostatic interaction. Theobtained biosensor shows a linear potential response to theglucose concentration ranging from 2.0 μM to 1.2 mM. Aphotoelectrochemical system based on GOx/ZnO nanoparticleswas described by Ren [49]. The experimental results show thatthe photovoltaic effect of the ZnO nanoparticles could enhancethe catalytic activity of GOx and improve the sensitivity ofglucose biosensor. The detection limits of enzyme electrodecontaining ZnO nanoparticles in the dark and under illumina-tion were 5.6×10−6 M and 1.1×10−4 M, respectively.
Recently, Kim developed a fluorescence glucose bio-sensor based on the collisional quenching mechanism
2 X. Shi et al.
(Fig. 3) [50]. ZnO nanocrystals were synthesized usingmercaptoundecanoic acid (MUA) as capping agent andbiolinker. Through covalent modification, GOx wasimmobilized onto ZnO nanocrystals. The resulting ZnO-MUA-GOx bioconjugate shows a linear decrease in thephotoluminescence (PL) intensity due to the collisionalquenching by H2O2 generated from enzymatic reaction overthe range of 1.6 to 33.3 mM.
Titanium oxide nanoparticle based enzymatic biosensors
TiO2 is one of the most prominent materials in various appli-cations related to catalysis, photovoltaic devices, sensors andpaintings. Over the past decades, tremendous efforts for syn-thesis, modifications and applications of TiO2 nanomaterialshave been conducted and a series of reviews have demonstrat-ed the breakthroughs in these fields. Since Cosnier and co-workers [51] reported an amperometric glucose biosensorbased on mesoporous TiO2 films in 1997, the applica-tions of nanostructured TiO2 for enzyme immobilizationand biosensor design have attracted considerable atten-tion. Through physical adsorption or covalent immobili-zation, different enzymes have been modified onto thesurface of TiO2 nanoparticles [52–58]. The detail infor-mation for these enzymatic biosensors is listed inTable 2.
It has been reported that the morphology and structure ofTiO2 nanomaterials have important effects on the performance
of biosensor. Li [74] reported that size-controllable and well-dispersed TiO2 nanodots could be directly fabricated on ITOelectrodes through a facile PSIA method. The sensitivity ofthe biosensors was significantly increased by adjusting theaverage size of the TiO2 nanodots from 30 to 79 nm. Xie [93]demonstrated that TiO2 nanoparticles with different morphol-ogies and sizes could be achieved by controlling the synthesisconditions, such as reaction time, solution pH, temperatureand growth precursors. Figure 4 shows different morphologiesof TiO2 nanospheres in Xie’s work, in which TiO2
nanoparticles were prepared within different hydrothermalreaction time. The TiO2 nanosphere shows a pretty core-shell structure and the size is successfully controlled varyingwith time. After coated HRP and TiO2 onto GC electrode withNafion, the direct chemistry of HRP was observed.
TiO2 is very famous for its unique photocatalytic ability,which is favorable for photoelectrochemical applications.Li [94] reported construction of a competitive photo-electrochemical immunosensor for alpha-fetoprotein (AFP) de-tection using TiO2 nanoparticles to enhancement the detectionsensitivity. Figure 5 shows the fabrication process of thephotoelectrochemical immunosensor and correspondingelectron-transfer mechanism.
Iron oxide nanoparticle based enzymatic biosensors
Well-established magnetic nanoparticles with appropriate sur-face chemistry have been widely used in pollution
Fig. 1 TEMmicrographs of ZnOnanoparticles. a ZnO nanorodsgrown under standard conditions;b ZnO nanodisks following aslow oxidation/evaporationprocess in THF (2 weeks); c ZnOnanodisks using dodecylamine(DDA) instead ofhexadecylamine (HDA) as thestabilizing ligand under standardconditions; d ZnO nanodisksusing octylamine (OA) instead ofHDA under standard conditions[ref. 15]
Enzymatic biosensors 3
remediation [95], chemical or biological separation [96],bioimaging [97, 98], targeted drug delivery [99–101], diseasesdiagnostics and therapy [102, 103], enzyme immobilization[104], biosensing [105, 106], etc. Among them, iron oxidenanoparticles, such as Fe3O4 and γ-Fe2O3, are the most prom-ising candidates. Controlling the size, size distribution, shape,crystal structure, defect distribution and surface structure ofiron oxide nanoparticles is very important for their applica-tions. Over the past decades, numerous synthetic approacheshave been developed for synthesis of iron oxide nanoparticles.The advances in the synthesis, protection as well as surfacefunctionalization were reviewed by different authors. Figure 6shows an example of controlled synthesis iron oxidenanoparticles in reference [107].
Due to their superior biocompatibility and large surfacearea, iron oxide nanoparticles can be used as nanocarrier forenzyme. GOx is the most widely used enzyme in the field ofenzyme biosensor. Other enzymes, such as hydrolase, HRP,Mb, Hb, creatinase, Lac, lactate dehydrogenase (LDH) andnicotinamide adenine dinucleotide (NAD+), etc. were success-fully immobilized on the surface of iron oxide nanoparticlesvia physical adsorption or covalent immobilization. Differentkinds of biosensors based on electrochemical and opticalmethods were developed for application in various fields,which were listed in Tables 3 and 4, respectively.
In 2004, an enzyme biosensor based on iron oxidenanoparticles was reported by Rossi [176]. In this work,GOx-Fe3O4 nanoparticle bioconjugate was synthesized by
Table 1 ZnO nanoparticles for enzyme immobilization and the performance of enzymatic biosensors
Analyte Enzyme Matrix Immobilizationmethod
Analyticalmethod
Performances Reference
Analytical range Limit ofdetection
Glucose GOx porous ZnO Electrostatic Amperometric 0.05×10−5–8.2×10−3 M 1×10−5 M [17]
Glucose GOx ZnO/RGO Electrostatic Amperometric 2×10−5–6.24×10−3 M 2×10−5 M [18]
Glucose GOx ZnO/CNTs Adsorption Amperometric 6.67×10−6–1.29×10−3 M 2.22×10−6 M [19]
Glucose GOx ZnO Crosslinking Amperometric 0–4×10−3 M 2×10−6 M [20]
Glucose GOx ZnO/Cu Electrostatic Amperometric 1×10−3–1.5×10−2 M − [21]
Glucose GOx ZnO/CNTs Electrostatic Amperometric 1×10−4–1.6×10−2 M 2.50×10−7 M [22]
Glucose GOx hollow ZnO Electrostatic Amperometric 5.0×10−6–1.315×10−2 M 1.0×10−6 M [23]
Cholesterol ChOx ZnO Adsorption Amperometric 1×10−9–5×10−7 M 0.37±0.02×10−9 M [24]
Cholesterol ChOx Pt/Au/ZnO Electrostatic Amperometric 1×10−7–7.593×10−4 M 3×10−8 M [25]
Cholesterol ChOx ZnO Electrostatic Amperometric 1.2×10−2–1.293×10−2 M − [26]
Cholesterol ChOx ZnO Electrostatic Amperometric 25–400 mg·dL−1 − [27]
H2O2 HRP ZnO Electrostatic Amperometric 2×10−5–3.5×10−4 M [28]
H2O2 HRP ZnO/Au Electrostatic Amperometric 1.5×10−5–1.1×10−3 M 9.0×10−6 M [29]
H2O2 HRP ZnO/Au Covalent Amperometric 1.5×10−6–4.5×10−4 M 7.0×10−7 M [30]
Phenol Tyr ZnO Electrostatic Amperometric 1.5×10−7–6.5×10−5 M 5.0×10−8 M [31]
Phenol Tyr ZnO Electrostatic Amperometric 1.5×10−7–4.0×10−5 M 8.0×10−8 M [32]
Urea Urease ZnO Electrostatic Amperometric 1×10—3–1×10−1 M − [33]
Urea Urease ZnO Electrostatic Amperometric − 13.5 mg·dL−1 [34]
Uric acid Uricase ZnO Electrostatic Amperometric 5.0×10−6–1.0×10−3 M 2.0×10−6 M [35]
Uric acid Uricase ZnO/CNTs Electrostatic Amperometric 5.0×10−6–1×10−3 M − [36]
Uric acid Uricase ZnO Adsorption Amperometric 1×10−4–5.9×10−4 M 2.56×10−6 M [37]
Xanthine XOD ZnO/CNTs/polyaniline
Electrostatic Amperometric 1×10−7–1×10−4 M 1×10−7 M [38]
Xanthine XOD ZnO/polypyrrole Electrostatic Amperometric 8×10−7–4×10−5 M 8×10−7 M [39]
Acetylcholineand choline
ChOx ZnO Adsorption Amperometric Ach: 1.0×10−6–1.5×10−3 MCh: 0–1.6×10−3 M
Ach: 6.0×10−7 MCh: 5.0×10−7 M
[40]
L-lactate LOD ZnO/CNTs Electrostatic Amperometric 2×10−4–2×10−3 M 6×10−6 M [41]
Pesticide AChE ZnO Electrostatic Amperometric 2.5×10−7–1.5×10−6 and1.75×10−6–1×10−5 M
1×10−8 M [42]
Creatinine Creatinine amidohydrolase,creatine amidino-hydrolase and SAO
ZnO/CNTs/polyaniline
Electrostatic Amperometric 1×10−5–6.50×10−4 M 5×10−7 M [43]
GOx glucose oxidase; ChOx choline oxidase; HRP horseradish peroxidase; Tyr Tyrosinase; XOD xanthine oxidase; LOD lactate oxidase; AChEacetylcholinesterase
4 X. Shi et al.
covalent immobilizing GOx on amino-modified magneticnanoparticles. The experimental results show that
functionalization of the magnetic nanoparticle surface withamino groups greatly increases the amount and activity of
Fig. 2 a a) SEM image of ZnOnanospheres. b) TEM(transmission electronmicroscopy) image along withEDS (energy dispersive X-rayspectroscopy) of ZnOnanospheres. (c) HRTEM (high-resolution transmission electronmicroscopy) image of individualZnO nanosphere. (d–f) TypicalSEM images of the as-depositedPt-incorporated ZnOnanospheres. (d) Low-magnification image of sphericalagglomerates of nanospheres. (e)Individual agglomerate spheretaken from the arrow point in (d).(f) Pt−ZnO nanospheres on thesurface of self-assembledmicrospheres from the arrowpoint in (e); b Cyclicvoltammetric sweep curve of theNafion/ChOx/PtZONS/GCEelectrode in the absence (CVa)and in the presence (CV c) of100 μM cholesterol in PBsolution (pH 6.8) at a scan rate of50 mV·s−1; CV curve of theNafion/ChOx/ZnO/GCEelectrode in the presence of100 μM cholesterol (CV b) in PBsolution (pH 6.8) at scan rate of50 mV·s−1; c Amperometricresponse of the biosensor basedon ZnO and Pt−ZnO nanospheresto different cholesterolconcentrations at +0.2 V in stirredpH 6.8 PB solutions [ref. 47]
Fig. 3 a Variation in PL spectra with H2O2 concentration, and b schematic presenting a collisional quenching mechanism causing decrease in PLintensity of ZnO nanocrystals [ref. 50]
Enzymatic biosensors 5
the enzyme. Using Ru(phen)3 as oxygen-sensitive fluores-cence probe, the GOx conjugated magnetic nanoparticles
could be used as a glucose sensors. In Margo’s work [177],γ-Fe2O3 nanoparticles (20–40 nm) with well-defined
Table 2 Enzymatic biosensors based on TiO2 nanoparticles
Analyte Enzyme Matrix Immobilizationmethod
Analytical method Performances Reference
Analytical range Limit ofdetection
Glucose GOx TiO2/CNTs Covalent Amperometric 1.8×10−6–2.66×10−4 M 4.4×10−7 M [59]
Glucose GOx TiO2/G Adsorption Amperometric 0–8×10−3 M – [60]
Glucose GOx TiO2/Au/CNTs
Electrostatic Amperometric 6×10−6–1.2×10−3 M 1×10−7 M [61]
Glucose GOx TiO2 Adsorption Amperometric 0–3×10−3 M − [62]
Glucose GOx TiO2 Covalent Amperometric 1.53×10−4–1–1.3×10−3 M 5.1×10−5 M [63]
Glucose GOx TiO2/SiO2 Adsorption Phosphorescent 1.0×10−9–1.0×10−2 M 1.2×10−10 M [64]
Glucose GOx TiO2/Ru Crosslinking Potentiometric 100–500 mg·−1 – [65]
Glucose GOx Cu/TiO2 Adsorption Amperometric 5×10−7–3×10−3 M – [66]
Glucose GOx TiO2/Au − Electrochemiluminescence 5.0×10−7–4.0×10−3 M 2.5×10−7 M [67]
Glucose GOx TiO2/PVA-g-PVP
Entrapment Amperometric 0–9×10−3 M − [68]
Glucose GOx TiO2 Entrapment Amperometric 5×10−4–1×10−3 M − [69]
Glucose,glutamateand urea
Urease, glucosedehydrogenaseand GDH
TiO2 Entrapment Fluorimetric Urea: 1×10−5–8×10−3 MGlucose: 4×10−5–1×
10−2 MGlutamate: 1×10−5–1×
10−2 M
Urea: 3.1×10−6 MGlucose: 5.4×
10−6 MGlutamate: 7.8×
10−6 M
[70]
H2O2 HRP TiO2 Entrapment Amperometric 7.5×10−6–1.23×10−4 M 2.5×10−6 M [71]
H2O2 HRP TiO2/Au/CNTs
Adsorption Amperometric 2.3×10−6–2.4×10−3 M 7.0×10−7 M [72]
H2O2 HRP TiO2/Au Adsorption Amperometric 4.1×10−5–6.3×10−4 M 5.9×10−6 M [73]
H2O2 HRP TiO2
nanodotsAdsorption Amperometric 1×10−6–7.8×10−4 M 8.5×10−7 M [74]
H2O2 HRP TiO2/PVA/CNTs
Entrapment Amperometric 5×10−7–2.7×10−6 M 1×10−8 M [75]
H2O2 HRP TiO2 Entrapment Amperometric 4.0×10−6–1.0×10−3 M 8.0×10−7 M [76]
H2O2 Mb and HRP TiO2 Electrostatic Amperometric 1×10−6–1.6×10−4 M 5×10−7 M [77]
H2O2 Hb TiO2/Au Covalent Amperometric 1.4×10−6–1.6×10−3 M 3.7×10−7 M [78]
Catechol Tyr TiO2 Adsorption Electrochemiluminescence 1.25×10−7–1.625×10−4 M 4.17×10−8 M [79]
Catechol Tyr TiO2 Adsorption Amperometric Up to 1.4×10−4 M 5×10−7 M [80]
Phenol Tyr TiO2/CNTs Crosslinking Amperometric 1×10−7–5×10−5 M 9.5×10−8 M [81]
Phenols Tyr TiO2 Entrapment Amperometric 7.5×10−8–6×10−6 M 1×10−8 M [82]
Glutamate GDH TiO2 Entrapment Fluorimetric 4×10−5–1×10−2 M 5.5×10−6 M [83]
Humanchorionicgonadotropin
HRP TiO2-Au/PB/CNTs
Covalent Amperometric 0.05 to 150 mIU·mL−1 0.023 mIU·mL−1 [84]
Lactic acid LDH TiO2 Entrapment Amperometric 1×10−6–2×10−5 M 4×10−7 M [85]
Nitrophenol HRP TiO2/Au Covalent Amperometric 3×10−7–1.2×10−4 M 9×10−8 M [86]
Organophosphate AChE TiO2/G Adsorption Amperometric 0.001–0.015 and 0.015–2ug·mL−1
0.3 ng·mL−1 [87]
2,4-Dichlorophe-nol
Lac TiO2 Crosslinking Thermometric 5×10−4–1×10−3 M 5×10−5 M [88]
AFP HRP TiO2/Au Covalent Amperometric − 29 pg·mL−1 [89]
Progastrinreleasingpeptide
GOx TiO2/Au Covalent Amperometric 10.0–500 pg·mL−1 3.0 pg·mL−1 [90]
Superoxide anion XOD CMC/G/TiO2 Crosslinking Amperometric 1.5×10−9–2×10−3 M 1.25×10−6 M [91]
Trichlorfon AChE PbO2/TiO2 Adsorption Amperometric 1×10−8–2×10−5 M 1×10−10 M [92]
Mb myoglobin; GDH glutamate dehydrogenase; Lac laccase
6 X. Shi et al.
stoichiometric structure were synthesized. The existence ofOH− groups at γ-Fe2O3 nanoparticles could act as chargebarriers preventing the aggregation of nanoparticles and en-abling a reversible binding with positive charged organicsubstances, such as Rhodamine B isothiocyanate. Afterimmobilized with GOx, the fluorimetric biosensor shows arate constant of 32.7 s–1 toward glucose oxidation. Shi [183]reported using circular strand-displacement amplificationchemiluminescence for point mutation detection at room tem-perature. Based on the circular strand-displacement amplifi-cation and HRP-catalyzed luminol–PIP–H2O2 reaction, thesensitivity was improved obviously. In addition, the magneticseparation was used to reduce the background signal in het-erozygous state and T4 DNA ligase to produce good selectiv-ity. Besides above-mentioned examples, some other opticalprobes based on enzyme and iron oxide nanoparticles werealso reported to measure different analytes, such as biogenicamines [178], enzyme inhibition assays [184], H2O2 andglucose [179].
Electrochemical method is the universal strategy in enzymebiosensor, such as potential [167] and capacitive [163] mea-surements. The most widely used electrochemical method isamperometry. For instance, amperometric Tyr biosensor basedon Fe3O4 nanoparticles-chitosan nanocomposite was devel-oped for the detection of phenolic compounds [140]. The largesurface area of Fe3O4 nanoparticles and the porous morphol-ogy of chitosan lead to a high loading of enzyme. Based on
enzyme amplification and magnetic enrichment and separa-tion, enzyme biosensors based on iron oxide have been widelyused in immunoassay. A three-layer composite composed ofFe3O4 magnetic core, prussian blue interlayer and gold shellwas used to fabricate an electrochemical immunosensor byfunctionalized with bienzyme of HRP and GOx (Fig. 7). Dueto the signal amplification from the nanobioconjugates, anelectrochemical immunosensing system was developed usingcarcinoembryonic antigen (CEA) and AFP as model. With theaddition of glucose, the immunosensor shows linear ranges of0.04–80.0 ng·mL−1for CEA and 0.074–142.0 ng·mL−1forAFP [137].
In order to improve the sensitivity of the enzymatic bio-sensors, some electron mediators or electron promoters wereintroduced into the biosensing system. For example, an am-perometric glucose biosensor was developed by entrappingGOx in chitosan composite doped with ferrocene monocar-boxylic acid-modified Fe3O4@SiO2 nanoparticles [120].With the aid of a permanent magnet, the magneticbionanoparticles were attached to the surface of CPE andacted as mediator to transfer electrons between the enzymeand the electrode. Eguílaz [145] developed a bienzymebiosensing system for the determination of cholesterol, inwhich Fe3O4 nanoparticles functionalized with glutaralde-hyde and poly(diallyldimethylammonium chloride) coatedMWCNTs were used as platforms for immobilization ofChOx and HRP. Using hydroquinone as a redox mediator,
Fig. 4 a SEM and TEM (insets) images of the calcined TiO2 micro-spheres prepared with different hydrothermal reaction times: (a) 1 h, (b)3 h, (c) 6 h , (d) 12 h , (e) 48 h, and (f) 96 h; b Cyclic voltammograms ofthe TiO2–48/Nafion/GC electrode (curve a), HRP/Nafion/GC electrode
(curve b), HRP/TiO2–1/Nafion/GC electrode (curve c), HRP/TiO2–6/Nafion/GC electrode (curve d) and HRP/TiO2–48/Nafion/GC electrode(curve e) in 0.1 M pH 7.5 PBS [ref. 93]
Enzymatic biosensors 7
Fig. 5 a Fabrication process of photoelectrochemical immunosensor andb corresponding electron-transfer mechanism c Photocurrent responsesand d corresponding calibration curve of ITO/TiO2/CS/anti-AFP/BSAelectrode in the presence of mixture containing 10 μL of AFP–CdTe–
GOx bioconjugates and 10 μL of different concentrations of AFP, whichwere measured in 0.1 M phosphate buffer solution (pH 7.4) containing60 mM glucose [ref. 94]
8 X. Shi et al.
the bienzyme biosensing system provided a sensitive andselective strategy for cholesterol measurement at a low detec-tion potential of −0.05 V.
Due to the supermagnetism of iron oxide nanoparticles, themagnetoswitchable biosensing system was developed. Tyrfunctionalizedmagnetic Fe3O4 nanoparticles were grafted ontoMWCNTs and the obtained MNP/Tyr/MWCNTs nanocom-positeswere utilized to design amagnetoswitchable biosensingsystem by magnetically loaded the nanocomposites on theworking electrode [141]. It allows an on-off bioelectrocatalyticswitching that controls redox reactions at the electrode surfacethrough the introduction, removal, and relocation of the exter-nal magnet (Fig. 8). In our research group, themagnetoswitchable bioelectrocatalytic systems were also de-veloped [185, 186]. A simple and versatile method for theintroduction of redox mediator (ferrocene) onto the surface ofmagnetic nanoparticles was developed based on “click” chem-istry. Due to the magnetism of magnetic nanoparticles and theelectrocatalytic activity of ferrocene unites, a recyclable,magneto-switchable bioelectrocatalytic system for glucose ox-idation in the presence of GOx was developed by simplealternate positioning of an external magnet.
In 2007, Gao [122] reported that Fe3O4 nanoparticles havean intrinsic peroxidase-like activity for the first time. Based onthe magnetism and peroxidase activity of Fe3O4 nanoparticles,they developed a novel capture-detection immunoassay forcardiac troponin I. After that, the enzyme mimetic activity ofiron oxide nanoparticles was used to design differentbiosensing systems. Wei [187] reported a colorimetric assaystrategy for glucose using Fe3O4 nanoparticles as peroxidasemimetics. Colorimetric method based on peroxidase activityof Fe3O4 nanoparticles was also used to detection thrombin[169], H2O2 [170], ethanol and methanol [171], galactose[172], organophosphorus pesticides and nerve agents [188],and so on. In addition, the peroxidase mimetic activity ofFe3O4 nanoparticles was also used in electrochemicalbiosensing system for H2O2 and glucose [121, 133, 134, 189].
Other metal oxide nanoparticle based enzymaticbiosensors
The above-mentioned MONPs are the most widely used ox-ides in enzyme-based biosensors. Relatively, the examples of
enzymatic biosensors based on other metal oxides are rare.However, the inherent advantages of metal oxide such as largesurface area, excellent biocompatibility, nontoxicity and cata-lytic ability, make it possible for enzyme immobilization andbiosensor development. For example, zirconia nanoparticlesand their nanocomposites have been reported to be used forenzyme immobilization, such as HRP [190–192], GOx [193,194], AChE [195], Hb and Bilirubin oxidase (BOD). Anelectrochemical quartz crystal microbalance (EQCM) immu-noassay was developed utilizing ZrO2 nanoparticles for selec-tive capture phosphorylated AChE (Phospho-AChE) due totheir strong affinity for phosphoric groups (Fig. 9) [196].HRP-labeled anti-AChE antibodies were employed to recog-nize the captured phosphorylated proteins. This immunoassaycould be used to measure Phospho-AChE in human plasmawith a detection limit of 0.020 nM.
Nickel oxide also is a promising material for enzymeimmobilization owing to its high biocompatibility and largesurface area. GOx, catalase and Tyr were reported to beimmobilized onto electrodeposited nickel oxide nanoparticlesand the direct electron transfer of enzyme was realized [197].In addition, the direct electron transfer of catalase on nano-sized NiO/MWCNTs composite film was also reported [198].Gupta’s research group [199] reported that uricase was phys-ically adsorpted on NiO thin film prepared by radio frequency(RF) sputtering technique. The biosensor exhibits efficientsensing performance towards uric acid due to the good elec-tron transport property and nanoporous morphology.Moreover, the RF sputtered NiO thin film was also used toimmobilize GOx for glucose biosensing due to its high holemobility [200]. Recently, ChOx, XOD, cytochrome c (Cyt c),Urease and alcohol dehydrogenase enzyme were reported tobe physisorbed on NiO nanoparticles or nanocomposite todevelop enzymatic biosensor [201–205].
Although MnO2 bulk material is a poor catalyst, MnO2
nanomaterials show high catalytic ability. Enzyme field-effecttransistors (ENFET) based on the catalytic or special reactionactivity of MnO2 nanoparticles were reported by immobiliza-tion of enzyme and MnO2 at the gate surface [206]. Forinstance, Luo [207] developed a glucose-sensitive ENFETbased on MnO2 nanoparticles. In this system, the ENFETworked with local pH change in biomembranes, whichresulted from the formation of gluconic acid by combingGOxwithMnO2. Amperometric glucose biosensors were also
Fig. 6 Schematic illustration ofthe formation of Fe3O4
nanocrystals. The middle andright panels are TEM images ofthe as-synthesized nanocrystalstaken at different reaction times.[ref. 107]
Enzymatic biosensors 9
Table 3 Electrochemical enzyme biosensors based on iron oxide nanoparticles
Analyte Enzyme Matrix ImmobilizationMethod
Analyticalmethod
Performances Reference
Analytical range Limit of detection
Glucose GOx Pt/ FexOy /MWCNTs
Adsorption Amperometric 6.0×10−6–6.2×10−3 M 2.0×10−6 M [108]
Glucose GOx Cobalt ferrite Electrostatic Amperometric − − [109]
Glucose GOx Fe3O4/SiO2 Covalent Amperometric 2.5×10−4–2.0×10−3 M [110]
Glucose GOx Fe3O4/SiO2/CNTs
Adsorption Amperometric 1×10−4–3×10−2 M 8×10−7 M [111]
Glucose GOx Au/Fe3O4 Covalent Amperometric 5×10−5–2×10−2 M − [112]
Glucose GOx γ-Fe2O3/C Adsorption Amperometric 2×10−4–1×10−2 M 8×10−5 M [113]
Glucose GOx Au/Fe3O4 Entrapment Amperometric 2.0×10−6–2.6×10−3 M 3.3×10−7 M [114]
Glucose GOx CoFe2O4/Au Adsorption Amperometric 0.01–0.1 M − [115]
Glucose GOx Fe3O4 Adsorption Amperometric 3.97×10−3 M [116]
Glucose GOx Fe3O4 Entrapment Amperometric 2×10−5–1.875×10−3 M 6.5×10−6 M [117]
Glucose GOx and HRP Fe3O4 Crosslinking Amperometric 1×10−3–8×10−3 M 1×10−5 M [118]
Glucose GOx Fe3O4/PB Covalent Amperometric 5.0×10−7–8.0×10−5 M 1.44×10−5 M [119]
Glucose GOx Fe3O4/SiO2 Entrapment Amperometric 1×10−5–4×10−3 M 3.2×10−3 M [120]
Glucose GOx Fe3O4 Crosslinking Amperometric 6×10−6–2.2×10−3 M 6×10−6 M [121]
Glucose GOx Fe3O4 Crosslinking Amperometric 5×10−4–1×10−2 M 2×10−4 M [122]
H2O2 HRP Fe3O4 Adsorption Amperometric 2.0×10−4–1.2×10−2 M 1.0×10−4 M [123]
H2O2 HRP NiFe2O4 Adsorption Amperometric 3×10−4–1.2×10−3 M − [124]
H2O2 HRP Fe3O4 Adsorption Amperometric 2×10−7–6.8×10−4 M 7.8×10−8 M [125]
H2O2 HRP Fe2O3 Adsorption Amperometric 4×10−7–3×10−4 M 5×10−8 M [126]
H2O2 HRP, Hb and Mb Fe3O4/Al2O3 Adsorption Amperometric Hb: 0.51×10−7–1.112×10−4 MMb: 4.3×10−7–1.158×10−4 MHRP: 8.5×10−7–1.015×10−4 M
Hb: 1.6×10−7 MMb: 1.4×10−7 MHRP: 2.8×10−7 M
[127]
H2O2 Mb Au/Fe3O4 Adsorption Amperometric 1.28×10−3–0.283 M 4×10−4 M [128]
H2O2 Mb Fe3O4 Crosslinking Amperometric 6.9×10−5–2.9×10−4 M and 2.9×10−4–3.0×10−3 M
2.1×10−5 M [129]
H2O2 Hb Fe3O4/SiO2 Covalent Amperometric 2.03×10–6–4.05×10–3 M 3.2×10−7 M [130]
H2O2 HRP Fe3O4/SiO2 Electrostatic Amperometric − 4.3×10−7 M [131]
H2O2 andglucose
HRP Fe3O4/GO Covalent Amperometric H2O2: 4×10−4–4×10−2 M
Glucose: 4×10−3–5.6×10−2 M− [132]
H2O2 peroxidase mimic Fe3O4 − Amperometric 2×10−4–2×10−3 M 1×10−5 M [133]
H2O2 peroxidase mimic Fe3O4 − Amperometric 4.18×10−6–8×10−4 M 1.4×10−6 M [134]
AFP HRP Au/Fe3O4 Covalent Amperometric 0.01–200 ng·mL−1 5 pg·mL−1 [135]
AFP α-AFP antibody Fe2O3 Covalent Amperometric 1–80 ng·mL−1 0.5 ng·mL−1 [136]
CEA and AFP GOx and HRP Au/PB/Fe3O4 Covalent Amperometric CEA: 0.04–80.0 ng·mL−1
AFP: 0.074–142.0 ng·mL−1CEA: 4 pg·mL−1
AFP: 0.014 to142.0 ng·mL−1
[137]
Catechol Lac Fe3O4/SiO2 Covalent Amperometric 7.5×10−7–2.75×10−4 M 7.5×10−7 M [138]
Catechol Lac Fe3O4 Covalent Amperometric 7.5× 10−7–4.4× 10−4 M − [139]
Catechol Tyr Fe3O4 Adsorption Amperometric 8.3×10−8–7.0×10−5 M 2.5×10−8 M [140]
Catechol Tyr Fe3O4/CNTs Covalent Amperometric 1×10−5–1.20×10−4 M 7.61×10−6 M [141]
Phenol Tyr MgFe2O4/SiO2
Covalent Amperometric 1×10−6–2.5×10−4 M 6.0×10−7 M [142]
Phenol Tyr Fe3O4 Crosslinking Amperometric 1.0×10−9–1.0× 10−5 M 1×10−9 M [143]
Phenol HRP Fe3O4 Covalent Amperometric − − [144]
Cholesterol HRP and ChOx Fe3O4 Crosslinking Amperometric 1×10−5–9.5×10−4 M 8.5×10−6 M [145]
Clozapine HRP SiO2/ Fe3O4-γ-Fe2O3
Covalent Amperometric 5×10−6–2.5×10−5 M − [146]
Creatine Creatinase Fe3O4 Adsorption Amperometric 2×10−7–3.8×10−6 M 2×10−7 M [147]
DNA HRP Fe3O4/Au Electrostatic Amperometric 5.0×10−11–5×10−7 M 7.1×10−12 M [148]
Dopaquinone Tyr γ-Fe2O3 Covalent Amperometric − − [149]
Escherichia coli HRP Au/Fe2O3 Adsorption Amperometric 1×103–5×105 cfu·mL−1 5 cfu·mL−1 [150]
Ethinylestradiol HRP Fe2O3 Covalent Amperometric 0.1–1,500 ng·L−1 – [151]
10 X. Shi et al.
Table 3 (continued)
Analyte Enzyme Matrix ImmobilizationMethod
Analyticalmethod
Performances Reference
Analytical range Limit of detection
Fructosyl valine Fructosyl aminoacid oxidase
Fe3O4 Covalent Amperometric 0–2×10−3 M 1×10−4 M [152]
Hydroquinone Lac Fe3O4/SiO2 Covalent Amperometric 1×10−7–1.375×10−4 M 1.5×10−8 M [153]
Methyl parathion Hydrolase Au/Fe3O4 Electrostatic Amperometric 0.5–1,000 ng·mL−1 0.1 ng·mL−1 [154]
Mycobacteriumtuberculosis
Thermophilichelicase
Au/Fe2O3 − Amperometric 0.01–10 ng·μL−1 0.01 ng·μL−1 [155]
NADH LDH and NAD+ Fe3O4/CNTs Covalent Amperometric 5×10−5–5×10−4 M 5×10−6 M [156]
Ochratoxin A HRP γ-Fe2O3/Au Covalent Amperometric 0.78–8.74 ng·mL−1 0.07±0.01 ng·mL−1
[157]
Ochratoxin A HRP γ-Fe2O3 Covalent Amperometric 0.027–0.033 ng·mL−1 0.11±0.01 ng·mL−1
[158]
Organophos-phoruspesticides
AChE Fe3O4 – Amperometric – 4.0× 10−13 M [159]
Organophos-phorusesticides
AChE Au/Fe2O3 Covalent Amperometric 1.0×10−3–10 ng·mL−1 5.6×10−4 ng·mL−1 [160]
Sulfite SOD Fe3O4/GNPs Covalent Amperometric 5.0×10−7–1×10−3 M 1.5×10−7 M [161]
Xanthine XOD Fe3O4/CNTs Covalent Amperometric 2.5×10−7–3.5×10−6 M 6×10−8 M [162]
Urea Urease Fe3O4 Crosslinking Capacitive 1×10−5–3×10−4 M − [163]
Glucose GOx γ-Fe2O3 /PAH Crosslinking Conductometric − 3×10−6 M [164]
Ig G and interferon-γ
HRP γ-Fe2O3 Covalent Magnetoresistive 12 pg·mL−1 [165]
Glucose GOx Fe3O4 Covalent Potentiometric 1.0× 10−6–3.0× 10−2 M – [166]
Urea Urease PGMA/Fe3O4
Covalent Potentiometric 2.5×10−4–5.0×10−3 M 5×10−5 M [167]
SOD sulfite oxidase
Table 4 Optical enzyme biosensors based on iron oxide nanoparticles
Analyte Enzyme Matrix ImmobilizationMethod
Analytical method Performances Reference
Analytical range Limit ofdetection
Mycotoxinochratoxin A
Alkalinephosphatase
Fe2O3 Covalent Colorimetric − − [168]
Thrombin peroxidase mimic Fe3O4 − Colorimetric 1×10−9–1×10−7 M 1×10−9 M [169]
H2O2 peroxidase mimic Fe3O4 − Colorimetric 5×10−7–1.5×10−4 M 2.5×10−7 M [170]
Ethanol andmethanol
AOX Fe3O4 Entrapment Colorimetric 1×10−4–5×10−4 M 2.5×10−5 M [171]
Galactose GAO Fe3O4 Crosslinking Colorimetric 10–200 μg·mL−1 5 μg·mL−1 [172]
CA125 HRP Fe3O4 Covalent Electrochemiluminescence 0–10 mU·mL−1 8.0μU·mL−1 [173]
AFP α-AFP antibody Fe3O4 − Electrochemiluminescence 0.5 pg·mL−1–5.0 ng·mL−1 0.2 pg·mL−1 [174]
Glucose GOx γ-Fe2O3 Covalent Fluorescent 0–1.5×10−3 M 9×10−7 M [175]
Glucose GOx Fe3O4 Covalent Fluorimetric 1×10−3–2×10−2 M – [176]
Glucose GOx γ-Fe2O3/Rhodamine
Covalent Fluorimetric 1×10−8–1×10−6 M 1.5×10−9 M [177]
Biogenic amines DAO Fe3O4 Electrostatic Fluorimetric 2.5×10−5–3×10−5 M – [178]
H2O2 HRP Fe3O4 Crosslinking Fluorimetric 5.0×10−9–1×10−5 M 2.1×10−9 M [179]
Ochratoxin A Avidin Fe3O4 Covalent Luminescent 1×10−13–1×10−9 g·mL−1 1×10−13 g·mL−1 [180]
Thrombin Thrombin Fe3O4 Covalent Surface plasmon resonance 1× 10−11–1.5× 10−9 M 1.7× 10−11 M [181]
AFP α-AFP antibody Fe3O4 Covalent Surface plasmon resonance 1.0–200.0 ng·mL−1 0.65 ng·mL−1 [182]
AOX alcohol Oxidase; GAO galactose oxidase; DAO diamine oxidase
Enzymatic biosensors 11
constructed by modification with GOx as a biocomponent andnanostructured manganese oxide as a mediator [208–211].Yang reported the development of H2O2 biosensor by encap-sulation of HRP on methylene blue/layered manganese oxide[212] and polyquaternium-manganese oxide nanosheet nano-composite films [213]. Mohseni [214] studied thevoltammetric behavior of modified CPE with Cyt c andMn2O3 nanoparticles for H2O2 sensing. An amperometricbiosensor with amine oxidase and MnO2 for measuring bio-genic amines was developed and the enzymatically producedH2O2 was determined to quantify biogenic amines [215].
Nanostructured alumina is beneficial for high enzyme load-ing due to large surface area, porous morphology and hydro-philic property. Tyr [216], GOx [217, 218], AChE [219], HRP[220, 221] and galactosidase [222] were successfullyimmobilized on Al2O3. Very recently, Santos [223] developeda smart enzymatic sensor based on the PL of nanoporous anodicalumina (NAA) in the UV-visible range. The structure of NAAwas functionalized and activated for immobilizing trypsin in acontrolled manner (Fig. 10). Based on the change of PL spec-trum in each stage, it is possible to accurately detect andquantify the immobilized enzyme within the NAA structure.
Fig. 7 Schematic drawing (a) of the immunosensor fabrication process.(a) Dropping of chitosan-nanoAu hydrogel membrane; (b) immobilizingof anti-CEA; (c) the immunoreaction of CEA and anti-CEA; (d) incuba-tion of the solution containing multilabeled three-layer composite mag-netic conjugate resulting in an amplified signal-generating detection; (e)
separation of the immunocomplex using an external magnetic field per-mits the regeneration of the immunosensor. Calibration plots of thechanges of the current response via concentration of CEA (b) and AFP(c) with (a) and without (b) the addition of 1.25 mm glucose in pH 6.86PBS under optimal conditions. [ref. 137]
12 X. Shi et al.
Fig. 8 a Formation of the on-offmagnetic switching assay. Tyr-modified MNPs (size: 100 nm)are first mixed with multiwalledCNTs (MWCNTs). The resultingMNP–Tyr conjugate is washedwith phosphate-buffered saline(PBS) at pH 6.5 in the presence ofa magnetic field, and this givesrise to the MNP–Tyrbioconjugate, which is thenintroduced, along with MWCNT,onto the screen-printed electrode(SPE) to produce the SPE/MNP–Tyr–MWCNT switching system.b Current–time recordingsfor catechol obtained for theMNP–Tyr–MWCNT biosensor.[ref. 141]
Fig. 9 a Schematic illustration of the principle and process for ZrO2
adsorption-based EQCM immunoassays for Phospho-AChE, includingthe ME monolayer modification, ZrO2 film electro-deposition, Phospho-AChE capture, HRP-anti-AChE recognition, and HRP-catalytic precipi-tation of insoluble product towards amplified EQCM immunoassays. bCalibration curve plotted on a semi-log scale for detecting Phospho-
AChE in plasma samples, with a detection limit of 0.020 nM. The topinsert shows the comparison of final Δf responses of immunoassays forBSA (10 mg ml−1), AChE (0.1 nM) and Phospho-AChE (0.1 nM), andthe bottom insert manifests the real-time EQCMmonitoring for the directadsorptions of 0.5 nM a AChE and b Phospho-AChE onto the ZrO2-coated crystals [ref. 196]
Enzymatic biosensors 13
Besides the metal oxides mentioned above, CuO [224],Bi2O3 [225], CeO2 [226] nanoparticles were reported to beused for GOx immobilization and biosensor design. MgO[227], Ruthenium oxide [228] and Ni doped SnO2
nanoparticles [229] were also modified on electrode forHRP immobilization and H2O2 detection. Table 5 shows someother metal oxide nanoparticle-based enzyme biosensors.
Conclusions and perspectives
Over the past decades, tremendous efforts have beenperformed on MONPs based biosensing system. The continu-ing breakthroughs in the synthesis and modifications ofMONPs have brought new properties and new applicationsin biosensors with improved performance. MONPs not onlyretain the bioactivity of the immobilized enzyme but alsoenhance the sensing characteristics such as sensitivity, selec-tivity and low detection limit of the enzymatic biosensingsystem.
Although great advances in enzymatic biosensors based onMONPs have been achieved, there are many challenges in thedevelopment of biosensing system for real sample analysis.Up to now, almost all researches on MONPs based enzymaticbiosensors are still in laboratory. As for practical applications,few enzymatic biosensors appear to be commercially feasibleexcept for some blood glucose and hand-held immunosensors[255]. To our best knowledge, no commercial enzymatic
biosensor based on MONPs has been reported until now.Therefore, to commercialize the enzymatic biosensors basedon MONPs, efforts should be made to break some key tech-nical barriers such as controlling the morphology of MONPson device, realizing efficient enzyme immobilization andkeeping enzyme long-life bioactivity as well as reducingmatrix interference and sensor fouling. Firstly, controllingthe morphologies ofMONPs for biosensor design is necessarybecause the morphology of the nanosized material is one ofthe most important factors to determine the properties forbiosensor applications. MONPs usually demonstrate size-dependent as well as shape- and structure-dependent optical,electronic, thermal, and structural properties. Many syntheticmethods have been developed for controllable preparationMONPs, however, for practical biosensor design, the proce-dure of controllable synthesis and then deposition thenanoparticles on device is not a good choice because of thetendency aggregation of nanoparticles. Thus, in-situ synthesis,for example, electrochemical deposition, CVD, template syn-thesis and so on, might be powerful tools to grow controlledMONPs on device directly. Secondly, how to realize efficientenzyme immobilization is a very critical question that shouldbe addressed for the commercialization of biosensors.Conventional strategies, including physical or chemical im-mobilization, have their shortage for controlling the orienta-tion of the enzyme in order to implement efficient enzymeimmobilization and retain the long-life bioactivity of enzyme.Recently, the coupled use of site-directed mutagenesis and
Fig. 10 a Schematic diagramshowing the different stages of thefabrication process of the NAAenzymatic sensor. (a) As-produced NAA. (b) APTES-functionalized NAA. (c) GTA-activated NAA. (d) Trypsin-immobilized NAA. (e) Magnifiedview of the resulting NAAenzymatic sensor. b Change inthe effective optical thicknessincrement as a result of thedifferent fabrication stages.ΔOTeff at each fabrication stageof sample Bio (1). c Contourgraph of ΔOTeff as a function ofthe anodization time (tan) andpore widening time (tpw) forsamples Bio(1–9) [ref. 223]
14 X. Shi et al.
immobilization has been proved a very useful strategy thatcontrolling the orientation of the enzyme and improving en-zyme features from activity to stability [256]. It should befurther studied to test whether site-directed mutagenesisand immobilization enzymes in MONPs could improveenzyme features or not. Thirdly, for practical applicationof MONPs based enzymatic biosensors, problems asso-ciated with matrix interference and sensor foulingshould be resolved. Biosensors might have well perfor-mance under controlled environments or laboratory sam-ples, however, in real sample analysis, the matrix inter-ference and sensor fouling are the detrimental factors
for commercialization. Especially, the large surface toarea for nanoparticles might lead to more serious sensorfouling. Thus, more effort should be made to solvethese problems.
Despite these numerous challenges, MONPs based enzy-matic biosensing system is considered to be one of the mostpromising tools for food safety detection, environmental pol-lution control, point-of-care testing and so on. With the ad-vancement of nanotechnology and biotechnology, more enzy-matic biosensing platforms based on MONPs will beestablished and new breakthroughs in practical applicationswill be realized.
Table 5 Other MONPs for enzyme immobilization and the performance of enzymatic biosensors
Analyte Enzyme MONPs matrix ImmobilizationMethod
Analyticalmethod
Performances References
Analytical range Limit ofdetection
H2O2 HRP ZrO2/Silica Entrapment Amperometric 7.8×10−7–3.2×10−3 M 3.2×10−7 M [230]
H2O2 Hb ZrO2/Collagen Entrapment Amperometric 8×10−7–1.32×10−4 M 1.2×10−7 M [231]
H2O2 Catalase NiO − Amperometric 1×10−6–1×10−3 M 0.96(± 0.05)mM
[232]
H2O2 HRP RuO2 Crosslinking Amperometric 5.09×10−3–1.5×10−2 M – [228]
H2O2 HRP SnO2/Ni Physical adsorption Amperometric 1.0×10−7–3.0×10−4 M 4.3×10−8 M [229]
H2O2 Mb ZrO2/CNTs Electrochemicaldeposition
Amperometric 2×10−6–1×10−3 M 6×10−7 M [233]
H2O2 HRP ZrO2/Collagen Entrapment Amperometric 1×10−6–7.3×10−5 M 2.5×10−7 M [234]
H2O2 ChOx MnO2 − Amperometric 1.0×10−5–2.1×10−3 M − [235]
H2O2 Catalase Al2O3/MB Entrapment Amperometric 1×10−5–1×10−4 M − [236]
H2O2 HRP Al2O3 Entrapment Amperometric 1.76×10−3–5.5×10−2 M 1.1×10−4 M [237]
H2O2 HRP tt-MgO Physical adsorption Amperometric 1×10−6–4.5×10−4 M 3×10−7 M [227]
H2O2 HRP Bi2O3/CNTs Electrostatic Amperometric 8.34×10−3–2.888×10−2 M − [238]
Glucose GOx NiO − Amperometric 3×10−5–5×10−3 M. 2.4×10−5 M [239]
Glucose GOx MnO2 Physical adsorption FET 2.5×10−5–1.9×10−3 M 3.5×10−9 M [207]
Glucose GOx MnO2 Entrapment Amperometric 9×10−7–2.73×10−3 M 1.8×10−7 M [240]
Glucose GOx Al2O3 Entrapment Amperometric 4×10−8–2.19×10−3 M 1×10−5 M [241]
Glucose GOx Al2O3 Crosslinking Amperometric 2.5×10−4–8×10−3 M − [242]
Glucose GOx CeO2 Physical adsorption Amperometric 2×10−3–2.6×10−2 M 1×10−4 M [243]
Lactate LOD MnO2 Electrostatic FET 1×10−5–3.6×10−3 M 8×10−6 M [244]
Lactate LOD MnO2 Physical adsorption Amperometric 2×10−4–5×10−3 M – [245]
Bilirubin BOD ZrO2/Silica Covalent Amperometric 2×10−8–2.5×10−4 M 1×10−10 M [246]
Cholesterol ChOx NiFe2O4/CuO/FeO
Electrostatic Amperometric 50–5,000 mg·L−1 313 mg·L−1 [247]
Cholesterol ChOx NiO Electrostatic Amperometric 10–400 mg·dL−1 43.4 mg·dL−1 [201]
Cyt c Cyt coxidase
NiO/CNTs Physical adsorption Amperometric 5×10−12–5×10−7 M 5×10−12 M [248]
Ethanol ADH NiO Physical adsorption Amperometric 1.6×10−3–3.8×10−2 M – [249]
Phenoliccompounds
Laccase MnO2/CNTs/PANI
Covalent Amperometric 1×10−7–1×10−5 M and 1× 10−5–5×10−4 M
4×10−8 M [250]
Phenols Tyr Al2O3 Entrapment Amperometric 5×10−7–3×10−5 M 3×10−7 M. [251]
SRB HRP MnO2 Covalent Amperometric 1.8×105–1.8×108 CFU·mL−1 − [252]
Urea Urease NiO Physical adsorption Amperometric 8.3×10−4–1.665×10−2 M – [204]
Urea Urease Al2O3 Entrapment Amperometric 5×10−7–3×10−3 M 2×10−7 M [253]
Uric acid Uricase CuO/Pt Physical adsorption Amperometric 5×10−5–1×10−3 M − [254]
ADH alcohol dehydrogenase
Enzymatic biosensors 15
Acknowledgments This work was supported by the National NaturalScience Foundation of China (No. 21175046), New Century ExcellentTalents in University (No. NCET-09-0357) and Open Foundation ofShanghai Key Laboratory of Green Chemistry and Chemical Process.
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