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Sensors 2016, 16(2), 243;

One-Pot Hydrothermal Synthesis of Magnetite Prussian Blue Nano-Composites and Their Application to Fabricate Glucose Biosensor
School of Chemistry and Chemical Engineering, Southeast University, Nanjing 211189, China
Food Technology Department, Nyala Technological College, Nyala P. O. Box 155, Sudan
Author to whom correspondence should be addressed.
Academic Editors: Yu Lei, Ashutosh Tiwari and Hongyun Liu
Received: 7 December 2015 / Accepted: 15 February 2016 / Published: 18 February 2016


In this work, we presented a simple method to synthesize magnetite Prussian blue nano-composites (Fe3O4-PB) through one-pot hydrothermal process. Subsequently, the obtained nano-composites were used to fabricate a facile and effective glucose biosensor. The obtained nanoparticles were characterized using transmission electron microscopy, scanning electron microscopy, Fourier-transform infrared spectroscopy, UV-vis absorbance spectroscopy, cyclic voltammetry and chronoamperometry. The resultant Fe3O4-PB nanocomposites have magnetic properties which could easily controlled by an external magnetic field and the electro-catalysis of hydrogen peroxide. Thus, a glucose biosensor based on Fe3O4-PB was successfully fabricated. The biosensor showed super-electrochemical properties toward glucose detection exhibiting fast response time within 3 to 4 s, low detection limit of 0.5 µM and wide linear range from 5 µM to 1.2 mM with sensitivity of 32 µA∙mM−1∙cm−2 and good long-term stability.
magnetite Prussian blue nano-composites; one-pot synthesis; biosensor

1. Introduction

Since Clark and Lyons reported their first enzyme electrode for glucose determination in 1962, a tremendous attention has been given to develop electrochemical biosensors via immobilization of the enzymes on an electrode surface [1,2].
Among the electrochemical enzyme biosensors, the glucose biosensors have been developed as commercial clinical devices to monitor the glucose concentration of real time in human being blood. In the mechanism of glucose biosensor, the oxidation of glucose can be catalyzed by glucose oxidase (GOD) in the presence of oxygen to produce gluconic acid and hydrogen peroxide (H2O2) in which the generated H2O2 can be detected by electrochemical method. However, the detection of H2O2 at high potential suffers from the oxidation of interferes such as dopamine, uric acid, and ascorbic acid.
Prussian blue (PB) the simplest representative of MHCF family and its different analogues have been utilized worldwide for fabrication of chemical sensors/biosensor as transducers for the reduction of hydrogen peroxide at low applied potential [3,4]. For a glucose biosensor, the generated H2O2 can be detected by PB which exhibits high activity and selectivity [5]. Despite the attractive properties of PB, the PB films are unstable over long time under neutral or alkaline conditions, which greatly limits their applications in non-acidic solutions [6,7].
The advance in magnetic nanoparticles is their easy separation and purification by an external magnet [8]. Several methods have been used to synthesize magnetic nanoparticles, such as co-precipitation, hydrothermal synthesis, thermal decomposition and/or reduction, sol-gel reaction, electrochemical methods, flow injection synthesis and aerosol/vapor [9,10]. Among them, hydrothermal method has the ability to create crystalline phases which are not stable at the melting point. In addition, materials which have a high vapor pressure near their melting points can also be grown by hydrothermal method. Moreover, the hydrothermal method is also particularly suitable for the growth of high-quality nanoparticles while maintaining good control over their composition [11].
Many procedures of synthesis magnetic PB nanoparticles have been reported in the literature. Ge et al. prepared PB-Fe3O4 nanoparticles in two step procedure, first synthesized of Fe3O4 by co-precipitation of Fe2+ and Fe3+ ions in the presence of NaOH at 80 °C then the obtained Fe3O4 particles were suspended in K3Fe(CN)6 + FeCl3 + HCl solution under stirring to form PB-Fe3O4 [12]. Recently, Ge et al. synthesized Fe3O4@PB NPs by improving shell growing procedure by mixing aqueous dispersion of Fe3O4 with aqueous solution of K4Fe(CN)6 in acidic condition under mechanical stirring at room temperature. Subsequently, the aqueous solution of FeCl3 (pH 3) was added into above mixed to form Fe3O4@PB NPs [13]. Li et al. were also synthesized Fe3O4 NPs containing PB NPs in which Fe3O4 nanoparticles were prepared by co-precipitating of Fe2+ and Fe3+ ions then the obtained Fe3O4 particles were re-dispersed by sonication in K3Fe(CN)6 solution (pH 2) followed by addition of H2O2 as reducing agent and the mixture was stirred for 3 h to form Fe3O4/PB complex [2]. Zhang et al. presented a simple approach to synthesize γ-Fe2O3 modified PB at different levels. The γ-Fe2O3 NPs were first prepared then the obtained particles were diluted in deionized water (pH 2) and used as a seeds to prepare γ-Fe2O3-PB NPs. An aqueous solution of K4Fe(CN)6 with different volumes was added dropwise to the γ-Fe2O3 solution under stirring for 1 h [14].
In the past decades, the synthesis of magnetic-PB NPs has been developed not only for its fundamental scientific interest but also for many technological applications. They has been used in bio-sensing application such as glucose biosensor [2], targeted photothermal therapy of cancer under magnetic resonance imaging (MRI) [13], H2O2 sensor [12,15] and the removal of cesium from contaminated environment [8]. Recently, the strategies focus on developing these materials in the sensors fabrication because PB, a prototype of mixed valence transition metal hexacyanoferrate is an ancient dye with low cost, good catalytic activities and simple preparation. Moreover, the good characteristic of the reduced form of PB, Prussian White, to catalyze the reduction of H2O2 at low applied potential can minimize the effects of the most common electrochemical interfering species, which leads interest of research to develop sensors and biosensors based on PB nanocomposite materials. The magnetic nanoparticles have also exhibited substantial application in biomedicine as an enhancement agent especially for the magnetic resonance imaging. The most prominent and the decent characteristics of these nanoparticles are the ability to form stable colloidal suspensions in water without any organic or inorganic coating to prevent their aggregation and, at the same time, they are able to bind specific organic molecules leading to composite materials, which can be exploited for biotechnological applications. Furthermore, nanocomposite magnetic PB materials showed remarkable electrocatalytic properties and were used for the development of sensor and biosensor for hydrogen peroxide and glucose detection with high sensitivity, low detection limit, good reproducibility and stability.
Regardless the interesting properties of magnetic nanoparticles, the applications of pure magnetic nanoparticles are limited due to agglomeration of the fine particles for their large ratio of surface area to volume. The pure magnetic particles are also easily oxidized in air, therefore, losing the magnetic properties [9,12]. The modification of Fe3O4 particles with polymers, metals and semiconductor materials has been widely involved to overcome these problems.
The composite nanomaterials formed from magnetic Fe3O4 nanoparticles and PB would be promising to overcome such problems and be interesting to fabricate glucose biosensors for clinical applications in the human body due to the reliable biosafety [13].
In this work we synthesized magnetite PB nano-composites in one pot hydrothermal procedure. Subsequently, we introduced the magnetite PB nano-composites to fabricate electrochemical glucose biosensor via immobilization of GOD-BSA by cross-linking with glutaraldehyde vapor on Fe3O4-PB modified glassy carbon electrode (GCE) surface denoted as (GOD-BSA/Fe3O4-PB/GCE). The combination of Fe3O4-PB nanocomposite and enzyme significantly enhanced the performance such as stability and sensitivity in enzyme biosensor.

2. Experimental

2.1. Chemicals and Reagents

Glucose oxidase (GOD, EC purified from Aspergillus Niger) was purchased from Sigma (Shanghai, China). Bovine serum albumin (BSA) was bought from Sangon Chemical Company (Shanghai, China). Glutaraldehyde (GA), potassium ferricyanide and potassium chloride were obtained from Shanghai Lingfeng Chemical Company (Shanghai, China). D-(+)-glucose, Iron (III) chloride hexahydrate, hydrogen peroxide and ethylene glycol were obtained from Sinopharm Chemical Company (Shanghai, China) and polyethylene glycol 4000 was obtained from Shantou Xilong Chemical Co., Ltd (Shantou, China).

2.2. Instruments

The magnetite PB particles were examined by transmission electron microscope (Gatan, Inc., Pleasanton, CA, USA) and scanning electron microscopy (SEM) and energy dispersive X-ray spectroscopy (EDAX) images were taken with scanning electron microscope (S-3000 N, Hitachi High-Technologies Corporation, Tokyo, Japan). Fourier-transform infrared (Nicolet 5700 FTIR spectrometer, Thermo elctron corporation, Madison, WI, USA ) and UV-Vis absorbance spectroscopy using UV-2450 spectrophotometer (Shimadzu Corporation, Kyoto, Japan) were performed to characterize the magnetite PB particles. Cyclic voltammetry and chronoamperometry were carried out on electrochemical workstation (CHI821C, Shanghai Chenhua Co., Ltd., Shanghai, China). The modified glassy carbon electrode (3.0 mm in diameter) was used as the working electrode, a saturated calomel electrode (SCE) as the reference electrode and a platinum wire as the auxiliary electrode.

2.3. One-Pot Synthesis of Magnetite PB Nanoparticles

All of the reagents in this experiment are analytical grade and used without further purification. Magnetite PB nanoparticles were synthesized via one-pot hydrothermal reduction of FeCl3·6H2O and K3Fe(CN)6 by the ethylene glycol (EG) in the presence of polyethylene glycol (PEG) as surfactant. Typically, FeCl3·6H2O 1.3 g (0.124 M) was dissolved in 40 mL of EG followed by addition of 1.0 g PEG under mechanical stirring. 0.67 g K3Fe(CN)6 (0.049 M) was added to the above solution and continued stirred vigorously for 1 h and then transferred into Teflon-lined stainless-steel autoclave. The autoclave was then heated and maintained at 190 °C for 12 h. Afterward the autoclave was allowed to cool overnight at room temperature. The precipitation was collected by magnetic separation, washed several times with distilled water and dried for 6 h in oven at 60 °C. The preparation and purification process has been illustrated in Scheme 1.

2.4. Preparation of Glucose Oxidase Biosensor on Magnetite PB Modified Glassy Carbon Electrode

The GCE was polished before each experiment with 1.0, 0.3, and 0.05 µm α-alumina powder, respectively, rinsed thoroughly with double distilled water. 1 mg/mL of synthesized magnetite PB nanocomposite was dispersed in double distilled water and then 6 µL of magnetite PB solution was dropped onto the cleaned GCE surface allowed to dry at room temperature followed by heating for 1 h at 100 °C denoted as (Fe3O4-PB/GCE). GOD (5 mg/mL) was prepared in PBS (pH 6.5); BSA (5 mg/mL) was also prepared in PBS (pH 6.5). Enzyme mixture was prepared by mixing (1:1 V/V) GOD and BSA then 5 µL of enzyme mixture was dropped onto the obtained Fe3O4-PB/GCE and allowed to dry at 4 °C in refrigerator then the electrode was introduced to glutaraldehyde (25%) vapor for cross-linking of enzyme mixture for 15 min. The final modified electrode is denoted as GOD-BSA/Fe3O4-PB/GCE. The biosensor preparation steps have been shown in Scheme 2.

3. Results and Discussion

3.1. Possible Formation Mechanism of Magnetite PB Nanocomposite

We prepared magnetite PB nanoparticles by one-pot hydrothermal route using ferric (III) chloride and potassium ferricyanide as precursors, ethylene glycol as solvent and reducing reagent and PEG as protective reagent to keep nanoparticles from agglomeration. During the hydrothermal process, EG can reduce some of Fe3+ ions to Fe2+ ions to form Fe(OH)3 and Fe(OH)2 by hydrolysis firstly. The hydroxides finally become Fe3O4 nanoparticles by thermal decomposition [16,17]. Concerning to the formation of magnetite PB, there are two possibilities: (1) The above-formed Fe2+ ions in the reaction medium could react with Fe(CN)63− to form PB nanoparticles, which precipitate onto Fe3O4 nanoparticles surface to form the final nanocomposites via the electrostatic attraction between Fe3O4 nanoparticles and PB nanoparticles [18]; (2) Fe(CN)63− might be reduced to Fe(CN)64−, which can react with Fe3+ ions adsorbed on the formed Fe3O4 nanoparticles surface to form the final products. After the hydrothermal reaction, the color of the product was dark blue and the formed particles could be separated by external magnet indicating the magnetic PB nanocomposites have been successfully prepared (Scheme 1).

3.2. Characterization

The morphologies of the magnetite PB nanocomposites were characterized by TEM. Figure 1 shows the TEM results of the typical synthesized magnetite PB nanocomposites. Numerous spherical and cubic nanoparticles combined compactly together were observed. The spherical and cubic nanoparticles belong to Fe3O4 and PB, respectively. Meanwhile, Fe3O4-PB nanocomposites thin film and GOD-BSA/Fe3O4-PB thin film modified electrodes were characterized by SEM. Figure 2 shows their SEM images. As seen in Figure 2A, the morphologies of Fe3O4-PB nanocomposites were consistent with the results from their TEM measurements. After the Fe3O4-PB modified electrode was coated with GOD and BSA mixture via cross-linking by glutaraldehyde, it is apparent to observe an enzyme membrane covered on Fe3O4-PB film (Figure 2B). To further verify the formation of magnetite PB nano-composites, EDAX was performed upon magnetite PB nanocomposites modified platinum sheet. As seen in Figure S1, (in the supplementary materials), elements content of the nanocomposites showed the existing of C, N, O and Fe, which are typical elements of Fe3O4 and PB.
As shown in Figure 3A, FTIR was also used to characterize Fe3O4 (Figure 3A, curve a) and magnetite PB nanoparticles (Figure 3A, curve b). In Figure 3A, curve a, the absorption band at 573 cm−1 is assigned to the absorption peak of Fe–O bonds [19]. The absorption peaks at around 3315 and 1600 cm−1 are related to O–H and H–O–H, respectively, which are attributed to the existence of interstitial water in the particles [12]. For the magnetite PB particles (Figure 3A, curve b), the absorption band at 2085 cm−1 are attributed to the CN group, the absorption band at 496 cm−1 belongs to the Fe–CN–Fe [8,12,20], and the absorption peak at 596 cm−1 refers to the Fe–O bond. Existence of peaks at 2085, 496, and 596 cm−1 confirmed the formation of magnetite PB nanoparticles through one pot hydrothermal synthesis. The Fe–O band shifted from Fe3O4 to magnetite PB to higher wavenumbers of 596 cm−1. This phenomenon is indicating the formation of the nanocomposite. One of the basic influences of the finite size of NPs is the breaking of a large number of bonds for surface atoms, resulting in the rearrangement of dissociative electrons on the particle surface. Hence, when particles are reduced to nanoscale dimensions, the absorption bands of FTIR spectra shift to higher wavenumbers [14].
UV-vis spectroscopy was further used to investigate the formation of the magnetite PB composite as shown in Figure 3B. For pure Fe3O4 nanoparticles (Figure 3B, curve a), no clear absorbance peaks could be observed due to its wide spectrum absorbance property. However, for the magnetite PB composite (Figure 3B, curve b), the mixed valence charge transfer band of the PB FeII–C–N–FeIII at around 740 nm was observed. Both results obtained from FTIR and UV-vis showed good agreement to the results reported in the literature [21,22].

3.3. Electrochemical Behaviors of Fe3O4-PB and GOD-BSA/Fe3O4-PB/GCE

To investigate the electrochemical behaviors of the synthesized magnetite PB nanocomposites and its corresponding glucose oxidase biosensor, cyclic voltammetry and chronoamperometry were performed. As shown in Figure 4, two pairs of anodic and cathodic peaks were observed from cyclic voltammogram (CV) of Fe3O4-PB/GCE in 0.01 M PBS (pH 6.0) containing 0.1 M KCl at the scan rate of 100 m∙Vs−1. The two pair of peaks were attributed to the oxidation of PB to Prussian green (PG) and the reduction of PB to Prussian white (PW), respectively. Clearly, from the shape of CV, the synthesized nano-composites contain PB [23].This result is with good agreement to the above-mentioned other characterization.
The conventional PB modified electrodes suffer from the instability of the film in neutral and alkaline conditions due to the presence of hydroxide ions, which could break Fe–(CN)–Fe bonds. Therefore, we investigated the pH effect to magnetite PB modified electrode in PBS with the pH values ranging from 5 to 9. Figure S2 (supplementary materials) showed multi-CVs of Fe3O4-PB/GCE in different PBS at scan rate of 100 mV∙s−1. The modified electrodes exhibited good stabilities in pH 5 to 7. However, the current peaks showed a little decrease in pH 8 and 9 upon 20 potential scanning cycles on each pH value. The current peak is almost unchanged which reveals that no proton is involved in the electrochemical reaction of PB. As well-known, the unmodified PB film is highly unstable in neutral and alkaline solution, and it has significant loss of redox activity. The good stability of the Fe3O4-PB/GCE may be due to the presence of the magnetic ions on the magnetite PB nano-composites which block the attack of hydroxide ions towards PB. In conclusion, electrostatic interaction between Fe3O4 and PB may offer stabilization mechanism to prevent its dissolution.
The electro-catalysis of Fe3O4-PB/GCE to H2O2 was investigated by cyclic voltammetry. Figure 5 shows the CVs of the Fe3O4-PB/GCE upon different concentrations of H2O2 in 0.01 M PBS (pH 6.0) containing 0.1 M KCl. The potential scan range was between –0.3 and 0.6 V vs. SCE and the scan rate is 100 mV∙s−1. The reduction current peaks increased significantly in magnitude upon increasing concentrations of H2O2 and the oxidation peaks decreased correspondingly, which demonstrated the electrocatalytic reduction of H2O2.
As shown in Figure S3 (in the supplementary materials), the amperometric determination of H2O2 was performed by successive addition of H2O2 into 0.01 M PBS (pH 6.0) containing 0.1 M KCl under stirring at –0.1 V. The amperogram of the Fe3O4-PB/GCE displayed fast response and stable signal with injection of H2O2. The response time is only 4–5 s.
Compared with Fe3O4-PB/GCE, an obvious decrease of peak currents was observed in the GOD-BSA/Fe3O4-PB/GCE as shown in Figure S4 (in the supplementary materials). This was attributed to the block effect of enzyme membrane to the mass transportation, which is consistent with the SEM measurement (Figure 2).
Figure 6 showed the typical CVs of GOD-BSA/Fe3O4-PB/GCE for glucose detection. In the presence of 1 mM glucose, the cathodic peak current increased and the anodic peak current decreased indicating catalytic reduction reaction. The description for this reaction process is that glucose diffuses from the electrolyte solution to the enzyme film on the electrode surface then GOD catalyzes the oxidation of glucose resulting in the generation of H2O2 and gluconic acid in consumption of oxygen. Subsequently, the generated H2O2 is then catalytically reduced by Prussian white (the reduced form of PB) [24].

3.4. Detection of Glucose

For the fabrication of GOD-BSA/Fe3O4-PB/GCE, the effect of cross-linking time in glutaraldehyde vapor was investigated from 5 min to 30 min. The optimal time is 15 min. A short time in the vapor leads the instability of the enzyme membrane due to the insufficient cross-linking. A long time in glutaraldehyde causes the decreasing of the bioactivity of GOD. For the detection of glucose, the applied potential of –0.15 V was chosen to perform the current-time response experiment due to the acceptable sensitivity and avoiding the interference of electroactive species shown in Figure S5. The sensitivity and the bioactivity of the biosensor greatly depend on the solution pH values. The current-time response of GOD-BSA/Fe3O4-PB/GCE in PBS with different pH values (from 4 to 9) with the injection of 0.4 mM glucose was investigated. The current peak response reached its maximum at pH 6.0, which is consistent with the optimal enzyme activity and the performance of Fe3O4-PB in acidic condition. Hence, the pH 6.0 is selected as the optimal value for this biosensor.
Under the optimal conditions, the current-time response of GOD-BSA/Fe3O4-PB/GCE upon successive addition of glucose (0.5 µM and 1500 µM) in 0.01 M PBS (pH6.0) containing 0.1 M KCl under stirring was shown in Figure 7. The electrocatalysis current reached 95% of its steady current within short time about 3–4 s after the injection of glucose indicating the biosensor has fast response. Meanwhile, the biosensor exhibited wide linear range to glucose concentration from 5 to 1200 µM with a sensitivity of 32 µA∙mM−1∙cm−2 and the limit of detection of 0.5 µM. The inset in Figure 7 displayed the corresponding calibration curve for glucose. The wide linear range of this biosensor may be due to the big loading of enzymes using the cross-linking method. The usage of BSA might not only provide sufficient amino groups for cross-linking via glutaraldehyde to stabilize GOD but also provide biocompatible surroundings to maintain the bioactivity of GOD. Table 1 shows the performance comparison of this work with other recently reported biosensors in the term of detection limit, linear range, sensitivity and response time.

3.5. Storage Stability of the Biosensor

In order to investigate the storage stability of the biosensor, cyclic voltammetry was used to detect constant concentration of glucose daily for two weeks. The biosensor showed acceptable stability with decreasing in current peaks about 5%–8% from its initial value. The long term stability of the biosensor attributed to the stability of the Fe3O4-PB nanocomposite film and the cross-linking enzyme membrane allowed large loading of the enzyme.

4. Conclusions

Electroactive Fe3O4-PB nano-composites have been synthesized in one-pot hydrothermal approach for the first time. Fe3O4-PB nano-composites modified GCE exhibited good performance in electro-catalysis of hydrogen peroxide, especially its stability. Furthermore, a highly sensitive glucose biosensor was developed via cross-linking of GOD-BSA onto Fe3O4-PB nano-composites modified GCE. The cross-linking between BSA and GOD guaranteed for more loading and good stability of GOD. The association of magnetite PB could improve the stability of PB film. Obviously, The Fe3O4-PB nano-composites film could be used as a promising platform for the development of biosensors related to hydrogen peroxide.

Supplementary Materials

The following are available online at, Figure S1: EDAX showing the elements content of the composite Fe3O4-Prussian blue. Figure S2: Multi-CVs of the Fe3O4-PB/GCE in 0.01 M Phosphate buffer solution (PBS) containing 0.1 M KCl at deferent pH values (A) 5.0, (B) 6.0, (C) 7.0, (D) 8.0, (E) 9.0. Figure S3: Current-time response of the Fe3O4-PB/GCE to the successive addition of H2O2 in 0.01 M PBS (pH 6.0) + 0.1 M KCl under stirring at −0.1 V. Insert: Plot of catalytic current vs. H2O2 concentration. Figure S4: Typical CVs obtained at Fe3O4-PB/GCE (A) and GOD-BSA/Fe3O4-PB/GCE (B) in 0.01 M PBS (pH 6.0) + 0.1 M KCl. Scan rate: 50 mV∙s−1. Figure S5: Typical Chronoaperometry (I-t) response of 0.025 µM glucose and (A) 0.1 µM AA and 0.1 µM UA (B) 0.2 µM AA and 0.2 µM UA at GOD-BSA/Fe3O4-PB/GCE. Applied Potential: −0.15 V.


This work was supported by the National Natural Science Foundation of China (Grant Nos. 21575022 and 21535003), the National High Technology Research and Development Program (“863” Program) of China (Grant No. 2015AA020502), the Open Research Fund of Key Laboratory of Energy Thermal Conversion and Control of Ministry of Education, Southeast University, and the Fundamental Research Funds for the Central Universities.

Author Contributions

Shou-Nian Ding conceived and designed the experiments; Ezzaldeen Younes Jomma performed the experiments; Both of them analyzed the data and completed the writing of the paper.

Conflicts of interest

The authors declare no conflict of interest.


  1. Wang, C.; Chen, S.; Xiang, Y.; Li, W.; Zhong, X.; Che, X.; Li, J. Glucose biosensor based on the highly efficient immobilization of glucose oxidase on Prussian blue-gold nanocomposite films. J. Mol. Catal. B Enzym. 2011, 69, 1–7. [Google Scholar] [CrossRef]
  2. Li, J.; Wei, X.; Yuan, Y. Synthesis of magnetic nanoparticles composed by Prussian blue and glucose oxidase for preparing highly sensitive and selective glucose biosensor. Sens. Actuators B Chem. 2009, 139, 400–406. [Google Scholar] [CrossRef]
  3. Fu, G.; Liu, W.; Feng, S.; Yue, X. Prussian blue nanoparticles operate as a new generation of photothermal ablation agents for cancer therapy. Chem. Commun. 2012, 48, 11567–11569. [Google Scholar] [CrossRef] [PubMed]
  4. Pandey, P.C.; Pandey, A.K. Tetrahydrofuran hydroperoxide mediated synthesis of Prussian blue nanoparticles: A study of their electrocatalytic activity and intrinsic peroxidase-like behavior. Electrochim. Acta 2014, 125, 465–472. [Google Scholar] [CrossRef]
  5. Wu, J.; Yin, F. Sensitive enzymatic glucose biosensor fabricated by electrospinning composite nanofibers and electrodepositing Prussian blue film. J. Electroanal. Chem. 2013, 694, 1–5. [Google Scholar] [CrossRef]
  6. Du, J.; Wang, Y.; Zhou, X.; Xue, Z.; Liu, X.; Sun, K.; Lu, X. Improved sensing in physiological buffers by controlling the nanostructure of Prussian blue film. J. Phys. Chem. C 2010, 114, 14786–14793. [Google Scholar] [CrossRef]
  7. Salazar, P.; Martín, M.; O’Neill, R.D.; Roche, R.; González-Mora, J.L. Improvement and characterization of surfactant-modified Prussian blue screen-printed carbon electrodes for selective H2O2 detection at low applied potentials. J. Electroanal. Chem. 2012, 674, 48–56. [Google Scholar] [CrossRef]
  8. Thammawong, C.; Opaprakasit, P.; Tangboriboonrat, P.; Sreearunothai, P. Prussian blue-coated magnetic nanoparticles for removal of cesium from contaminated environment. J. Nanopart. Res. 2013, 15, 1–10. [Google Scholar] [CrossRef]
  9. Lu, A.H.; Salabas, E.L.; Schuth, F. Magnetic nanoparticles: Synthesis, protection, functionalization, and application. Angew. Chem. 2007, 46, 1222–1244. [Google Scholar] [CrossRef] [PubMed]
  10. Laurent, S.; Forge, D.; Port, M.; Roch, A.; Robic, C.; Vander Elst, L.; Muller, R.N. Magnetic iron oxide nanoparticles: Synthesis, stabilization, vectorization, physicochemical characterizations, and biological applications. Chem. Rev. 2008, 108, 2064–2110. [Google Scholar] [CrossRef] [PubMed]
  11. Wu, W.; Wu, Z.; Yu, T.; Jiang, C.; Kim, W.-S. Recent progress on magnetic iron oxide nanoparticles: Synthesis, surface functional strategies and biomedical applications. Sci. Technol. Adv. Mater. 2015, 16. [Google Scholar] [CrossRef]
  12. Zhao, G.; Feng, J.; Zhang, Q.; Li, S.; Chen, H.-Y. Synthesis and characterization of Prussian blue modified magnetite nanoparticles and its application to the electrocatalytic reduction of H2O2. Chem. Mater. 2005, 17, 3154–3159. [Google Scholar] [CrossRef]
  13. Fu, G.; Liu, W.; Li, Y.; Jin, Y.; Jiang, L.; Liang, X.; Feng, S.; Dai, Z. Magnetic Prussian blue nanoparticles for targeted photothermal therapy under magnetic resonance imaging guidance. Bioconjugate Chem. 2014, 25, 1655–1663. [Google Scholar] [CrossRef] [PubMed]
  14. Zhang, X.; Gong, S.; Zhang, Y.; Yang, T.; Wang, C.; Gu, N. Prussian blue modified iron oxide magnetic nanoparticles and their high peroxidase-like activity. J. Mater. Chem. 2010, 20, 5110–5116. [Google Scholar] [CrossRef]
  15. Massimiliano, M.; Davide, B.; Gabriella, S.; Katerin, P.; Giorgio, Z.; Jiri, T.; Josef, K.; Radek, Z.; Fabio, V. Core-shell hybrid nanomaterial based on Prussian blue and surface active maghemite nanoparticles as stable electrocatalyst. Biosens. Bioelectron. 2014, 52, 159–165. [Google Scholar]
  16. Liu, S.; Xing, R.; Lu, F.; Rana, R.K.; Zhu, J.-J. One-pot template-free fabrication of hollow magnetite nanospheres and their application as potential drug carriers. J. Phys. Chem. C 2009, 113, 21042–21047. [Google Scholar] [CrossRef]
  17. Cheng, W.; Tang, K.; Qi, Y.; Sheng, J.; Liu, Z. One-step synthesis of superparamagnetic monodisperse porous Fe3O4 hollow and core-shell spheres. J. Mater. Chem. 2010, 20, 1799–1805. [Google Scholar] [CrossRef]
  18. Arun, T.; Prakash, K.; Kuppusamy, R.; Joseyphus, R.J. Magnetic properties of Prussian blue modified Fe3O4 nanocubes. J. Phys. Chem. Solids 2013, 74, 1761–1768. [Google Scholar] [CrossRef]
  19. Daou, T.J.; Grenèche, J.M.; Pourroy, G.; Buathong, S.; Derory, A.; Ulhaq-Bouillet, C.; Donnio, B.; Guillon, D.; Begin-Colin, S. Coupling agent effect on magnetic properties of functionalized magnetite-based nanoparticles. Chem. Mater. 2008, 20, 5869–5875. [Google Scholar] [CrossRef]
  20. Hu, M.; Furukawa, S.; Ohtani, R.; Sukegawa, H.; Nemoto, Y.; Reboul, J.; Kitagawa, S.; Yamauchi, Y. Synthesis of Prussian blue nanoparticles with a hollow interior by controlled chemical etching. Angew. Chem. 2012, 51, 984–988. [Google Scholar] [CrossRef] [PubMed]
  21. Li, J.; Yuan, Y. Synthesis of magnetic Prussian blue nanoparticles and the fabrication of chemically modified electrode. Acta Chim. Sin. 2006, 64, 261–265. [Google Scholar]
  22. Darder, M.; González-Alfaro, Y.; Aranda, P.; Ruiz-Hitzky, E. Silicate-based multifunctional nanostructured materials with magnetite and Prussian blue: Application to cesium uptake. RSC Adv. 2014, 4, 35415–35421. [Google Scholar] [CrossRef]
  23. Jiang, C.; Lin, X. Electrochemical synthesis of Fe3O4-PB nanoparticles with core-shell structure and its electrocatalytic reduction toward H2O2. J. Solid State Electrochem. 2008, 13, 1273–1278. [Google Scholar]
  24. Xue, M.-H.; Xu, Q.; Zhou, M.; Zhu, J.-J. In situ immobilization of glucose oxidase in chitosan-gold nanoparticle hybrid film on Prussian blue modified electrode for high-sensitivity glucose detection. Electrochem. Commun. 2006, 8, 1468–1474. [Google Scholar] [CrossRef]
  25. Albanese, D.; Sannini, A.; Malvano, F.; Pilloton, R.; Di Matteo, M. Optimisation of glucose biosensors based on sol-gel entrapment and Prussian blue-modified screen-printed electrodes for real food analysis. Food Anal. Methods 2013, 7, 1002–1008. [Google Scholar] [CrossRef]
  26. Palod, P.A.; Singh, V. Improvement in glucose biosensing response of electrochemically grown polypyrrole nanotubes by incorporating crosslinked glucose oxidase. Mater. Sci. Eng. C 2015, 55, 420–430. [Google Scholar] [CrossRef] [PubMed]
  27. Zhang, Y.; Liu, Y.; Chu, Z.; Shi, L.; Jin, W. Amperometric glucose biosensor based on direct assembly of Prussian blue film with ionic liquid-chitosan matrix assisted enzyme immobilization. Sens. Actuators B Chem. 2013, 176, 978–984. [Google Scholar] [CrossRef]
  28. Lin, Y.; Hu, L.; Yin, L.; Guo, L. Electrochemical glucose biosensor with improved performance based on the use of glucose oxidase and Prussian blue incorporated into a thin film of self-polymerized dopamine. Sens. Actuatos B Chem. 2015, 210, 513–518. [Google Scholar] [CrossRef]
  29. Li, L.; Sheng, Q.; Zheng, J.; Zhang, H. Facile and controllable preparation of glucose biosensor based on Prussian blue nanoparticles hybrid composites. Bioelectrochemistry 2008, 74, 170–175. [Google Scholar] [CrossRef] [PubMed]
  30. Lad, U.; Kale, G.M.; Bryaskova, R. Glucose oxidase encapsulated polyvinyl alcohol-silica hybrid films for an electrochemical glucose sensing electrode. Anal. Chem. 2013, 85, 6349–6355. [Google Scholar] [CrossRef] [PubMed]
  31. Ding, S.-N.; Dan, S.; Xue, H.; Zhu, D.; Cosnier, S. Glucose biosensor immobilized in alginatelayered double hydroxides hybrid membrane and its biosensing application. Anal. Sci. 2009, 25, 1421–1425. [Google Scholar] [CrossRef] [PubMed]
Scheme 1. Synthesis and purification process of the magnetite Prussian blue (PB) nano-composites.
Scheme 1. Synthesis and purification process of the magnetite Prussian blue (PB) nano-composites.
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Scheme 2. Steps to fabricate the biosensor.
Scheme 2. Steps to fabricate the biosensor.
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Figure 1. TEM image of the magnetite PB nano-composites.
Figure 1. TEM image of the magnetite PB nano-composites.
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Figure 2. SEM images of (A) Fe3O4-PB film and (B) Glucose oxidase (GOD)-bovine serum albumin (BSA)/Fe3O4-PB film.
Figure 2. SEM images of (A) Fe3O4-PB film and (B) Glucose oxidase (GOD)-bovine serum albumin (BSA)/Fe3O4-PB film.
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Figure 3. (A) FTIR spectra of pure Fe3O4 nanoparticles (curve a) and magnetite PB nano-composites (curve b); (B) UV-vis absorption spectra of Fe3O4 nanoparticles (curve a) and magnetite PB nano-composites (curve b).
Figure 3. (A) FTIR spectra of pure Fe3O4 nanoparticles (curve a) and magnetite PB nano-composites (curve b); (B) UV-vis absorption spectra of Fe3O4 nanoparticles (curve a) and magnetite PB nano-composites (curve b).
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Figure 4. Cyclic voltammogram (CV) of the magnetite PB nano-composites modified glassy carbon electrode (GCE) in 0.1 M PBS (pH 6.0) with the scan rate of 100 mV∙s−1.
Figure 4. Cyclic voltammogram (CV) of the magnetite PB nano-composites modified glassy carbon electrode (GCE) in 0.1 M PBS (pH 6.0) with the scan rate of 100 mV∙s−1.
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Figure 5. CVs of magnetite PB nano-composites modified GCE in the absence (a) and presence of 1 mM (b), 2 mM (c), and 4 mM H2O2 (d) in 0.1 M PBS (pH 6.0) with the scan rate of 100 mV∙s−1.
Figure 5. CVs of magnetite PB nano-composites modified GCE in the absence (a) and presence of 1 mM (b), 2 mM (c), and 4 mM H2O2 (d) in 0.1 M PBS (pH 6.0) with the scan rate of 100 mV∙s−1.
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Figure 6. CVs obtained at the GOD–BSA/Fe3O4-PB/GCE in 0.01 M PBS (pH 6.0) containing 0.1 M KCl in the absence (a) and presence (b) of 1 mM glucose with the scan rate of 50 mV s−1.
Figure 6. CVs obtained at the GOD–BSA/Fe3O4-PB/GCE in 0.01 M PBS (pH 6.0) containing 0.1 M KCl in the absence (a) and presence (b) of 1 mM glucose with the scan rate of 50 mV s−1.
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Figure 7. Current-time response of the biosensor upon successive addition of different concentrations of glucose from 5 µM to 1500 µM in 0.01 M PBS (pH 6.0) containing 0.1 M KCl under stirring. The applied potential was −0.15 V. Inset: the catalytic response vs. glucose concentration.
Figure 7. Current-time response of the biosensor upon successive addition of different concentrations of glucose from 5 µM to 1500 µM in 0.01 M PBS (pH 6.0) containing 0.1 M KCl under stirring. The applied potential was −0.15 V. Inset: the catalytic response vs. glucose concentration.
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Table 1. Comparison of electrocatalytic activities of this work with the previous reported.
Table 1. Comparison of electrocatalytic activities of this work with the previous reported.
Working ElectrodeLOD (µM)Linear RangeSensitivityResponse Time (s)Reference
PB/GOD/TEOS-PVA/NAFION205–1000 µM2.06 µA∙mM−1∙cm−2No data[25]
Anodisc™/Pt/PPy/GOx nanotube arrays500.2–13 mM72.1 mA∙M−1∙cm−213[26]
Fe3O4/PB/GOD0.10.5–80 µMNo data10[2]
GOx/Chi-IL/PB/Pt50.01–4.2 mM37.8 µA∙mM−1∙cm−23[27]
GOx–PDA/PB/GCE46.20.2–3.4 mM1.59 nA∙µM−115[28]
PBNPs-PANI/MWNTs/GCE0.66.7–1900 µM6.28 µAmM−15[29]
PVA-Au-pphTEOS-GOD7001–8 mM49 µA∙mM−1∙cm−26[30]
Alg/LDHs/GOD/Pt40.016–2 mM68.9 mA∙M−1∙cm−210[31]
GOD-BSA/GA/Fe3O4-PB/GCE0.55–1200 µM32 µA∙mM−1∙cm−24This work
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