Polyaniline-uricase biosensor prepared with template process

Polyaniline (PANI) uricase biosensor prepared with template process is reported first in this paper. The fabrication process is as follows. Firstly, a PANI–uricase electrode is obtained using one-step process. Secondly, the electrode is hydrolyzed in 6.0 mol/dm³ hydrochloric acid solution to remove the uricase that may be affected by aniline monomer from PANI film. Finally, active uricase is immobilized into the PANI film based on the principle of the doping and undoping of the conducting polymer and a PANI–uricase biosensor is obtained. Some factors that affect response current are studied, such as temperature, pH, potential and substrate concentration. The determination of biosensors indicates that the response current of the biosensor prepared by template process decreases only by about 18% for 60 days, but that prepared by two-step process decreases by approximately 39% for 40 h. The uricase in PANI–uricase biosensor prepared by template process mainly interacts with the nitrogen linked to the quinoid ring. The biosensor is characterized with FTIR, UV-Vis and SEM for the first time.     

Development of a sandwich format, amperometric screen-printed uric acid biosensor for urine analysis

A screen-printed carbon electrode (SPCE) incorporating the electrocatalyst cobalt phthalocyanine (CoPC), fabricated using a water-based ink formulation, has been investigated as the base transducer for a uric acid biosensor. A sandwich biosensor was fabricated by first depositing cellulose acetate (CA) onto this transducer (CoPC-SPCE), followed by uricase (UOX) and finally a polycarbonate (PC) membrane; this device is designated PC-UOX-CA-CoPC-SPCE. This biosensor was used in conjunction with chronoamperometry to optimize the conditions for the analysis of urine: temperature, 35°C; buffer, pH 9.2; ionic strength, 50 mM; uricase, 0.6 U; incubation time, 180 s. The proposed biosensor was applied to urine from a healthy subject. The precision determined on unspiked urine (n=6) was 5.82%. Urine was fortified with 0.225 mM UA, and the resulting precision and recovery were 4.21 and 97.3%, respectively. The linear working range of the biosensor was found to be 0.015 to 0.25 mM (the former represents the detection limit), and the sensitivity was calculated to be 2.10 μA/mM.     

Mercaptoethylpyrazine promoted electrochemistry of redox protein and amperometric biosensing of uric acid

Electrochemistry of microperoxidase-11 (MPx-11) anchored on the mixed self-assembled monolayer (SAM) of 2-(2-mercaptoethylpyrazine) (PET) and 4,4'-dithiodibutyric acid (DTB) on gold (Au) electrode and the biosensing of uric acid (UA) is described. MPx-11 has been covalently anchored on the mixed SAM of PET and DTB on Au electrode. MPx-11 on the mixed self-assembly exhibits reversible redox response characteristic of a surface confined species. The heterocyclic ring of PET promotes the electron transfer between the electrode and the redox protein. The apparent standard rate constant kapps obtained for the redox reaction of MPx-11 on the mixed monolayer is approximately 2.15 times higher than that on the single monolayer of DTB modified electrode. MPx-11 efficiently mediates the electrocatalytic reduction of H2O2. MPx-11 electrode is highly sensitive to H2O2 and it shows linear response for a wide concentration range. The electrocatalytic activity of the MPx-11 electrode is combined with the enzymatic activity of uricase (UOx) to fabricate uric acid biosensor. The bienzyme assembly is highly sensitive towards UA and it could detect UA as low as 2 microM at the potential of -0.1 V. The biosensor shows linear response with a sensitivity of 3.4+/-0.08 nA cm(-2) microM(-1). Ascorbate (AA) and paracetamol (PA) do not significantly interfere in the amperometric sensing of UA.     

Electrochemical detection of uric acid via uricase-immobilized graphene oxide

Measurement of the uric acid level in the body can be improved by biosensing with respect to the accuracy, sensitivity and time consumption. This study has reported the immobilization of uricase onto graphene oxide (GO) and its function for electrochemical detection of uric acid. Through chemical modification of GO using 1-ethyl-3-(dimethylaminopropyl) carbodiimide (EDC) and N-hydroxysulfosuccinimide (NHS) as cross-linking reagents, the enzyme activity of the immobilized uricase was much comparable to the free enzyme with 88% of the activity retained. The modified GO-uricase (GOU) was then subjected to electrocatalytic detection of uric acid (UA) via cyclic voltammetry (CV). For that reason, a glassy carbon electrode (GCE) was modified by adhering the GO along with the immobilized uricase to facilitate the redox reaction between the enzyme and the substrate. The modified GOU/GCE outperformed a bare electrode through the electrocatalytic activity with an amplified electrical signal for the detection of UA. The electrocatalytic response showed a linear dependence on the UA concentration ranging from 0.02 to 0.49 mM with a detection limit of 3.45 μM at 3σ/m. The resulting biosensor also exhibited a high selectivity towards UA in the presence of other interference as well as good reproducibility.     

Modification of nanocrystalline TiO2 coatings with molecularly imprinted TiO2 for uric acid recognition

Combining the surface modification and molecular imprinting technique, a novel piezoelectric sensing platform with excellent molecular recognition capability was established for the detection of uric acid (UA) based on the immobilization of TiO₂ nanoparticles onto quartz crystal microbalance (QCM) electrode and modification of molecularly imprinted TiO₂ (MIT) layer on TiO₂ nanoparticles. The performance of the fabricated biosensor was evaluated, and the results indicated that the biosensor exhibited high sensitivity in UA detection, with a linear range from 0.04 to 45 μM and a limit of detection of 0.01 μM. Moreover, the biosensor presented high selectivity towards UA in comparison with other interferents. The analytical application of the UA biosensor confirmed the feasibility of UA detection in urine sample.     

Construction of amperometric uric acid biosensor based on uricase immobilized on PBNPs/cMWCNT/PANI/Au composite

A chitosan-glutaraldehyde crosslinked uricase was immobilized onto Prussian blue nanoparticles (PBNPs) absorbed onto carboxylated multiwalled carbon nanotube (c-MWCNT) and polyaniline (PANI) layer, electrochemically deposited on the surface of Au electrode. The nanohybrid-uricase electrode was characterized by scanning electron microscopic (SEM), Fourier transform infrared spectroscopy (FTIR) and cyclic voltammetry. An amperometric uric acid biosensor was fabricated using uricase/c-MWCNT/PBNPs/Au electrode as working electrode, Ag/AgCl as standard and Pt wire as auxiliary electrode connected through a potentiostat. The biosensor showed optimum response within 4 s at pH 7.5 and 40 °C, when operated at 0.4 V vs. Ag/AgCl. The linear working range for uric acid was 0.005-0.8 mM, with a detection limit of 5 μM. The sensor was evaluated with 96% recovery of added uric acid in sera and 4.6 and 5.4% within and between batch of coefficient of variation respectively and a good correlation (r = 0.99) with standard enzymic colorimetric method. This sensor measured uric acid in real serum samples. The sensor lost only 37% of its initial activity after its 400 uses over a period of 7 months, when stored at 4 °C.     

Development and analytical application of an uric acid biosensor using an uricase-immobilized eggshell membrane

An uric acid biosensor fabricated from a uricase-immobilized eggshell membrane and an oxygen electrode was presented. The detection schemes involve the enzymatic reactions of the uricase leading to the depletion of dissolved oxygen level upon exposure to uric acid solution. The decrease in oxygen level was monitored and related to the uric acid concentration. The scanning electron micrographs show the microstructure of the eggshell membrane within which the uricase is successfully immobilized. The effects of enzyme loading, pH, temperature, and phosphate buffer concentration on the response of the biosensor were investigated in detail. The uric acid biosensor has a linear response range of 4.0-640 microM with a detection limit of 2.0 microM (S/N=3). The response time was less than 100 s. The biosensor exhibited good repeatable response to a 0.10mM uric acid solution with a relative standard deviation of 3.1% (n=7). The reproducibility of fabrication of the biosensors using four different membranes was good with a R.S.D. of 3.2%. The biosensor showed extremely good stability with a shelf-life of at least 3 months. Some common potential interferents in samples such as glucose, urea, ascorbic acid, lactic acid, glycine, DL-alpha-alanine, DL-cysteine, KCl, NaCl, CaCl2, MgSO4, and NH4Cl showed no interferences on the response of the uric acid biosensor. The biosensor was successfully applied to determine the uric acid level in some human serum and urine samples, and the results agreed well with those obtained by a commercial colorimetric assay kit.     

Electrochemical determination of uric acid at ordered mesoporous carbon functionalized with ferrocenecarboxylic acid-modified electrode

Ordered mesoporous carbon (OMC) functionalized with ferrocenecarboxylic acid (Fc) was used to modify the glassy carbon (GC) electrode. The characterization of OMC–Fc shows that, after anchoring ferrocene on the mesoporous, ordered mesostructure of the material (OMC–Fc) remains intact and Fc is electrochemically accessible. The obtained OMC–Fc-modified electrode was used to investigate the electrochemical behavior of uric acid (UA). UA oxidation is catalyzed by this electrode in aqueous buffer solution (pH 7.3) with a decrease of 200 mV in overpotential compared to GC electrode. The detection and determination of UA in the presence of ascorbic acid (AA), the main interferent, were achieved. The voltammetric signals due to UA and AA were well separated with a potential difference of 308 mV, a separation that can allow the simultaneous determination of UA and AA. With amperometric method, at a constant potential of 375 mV, the catalytic current of UA versus its concentration shows a good linearity in the range 60–390 μM (R = 0.998) with a detection limit of 1.8 μM (S/N = 3). These results are not influenced by the presence of AA in the sample solution. With good stability and reproducibility, the present OMC–Fc-modified electrode was applied in the determination of UA content in urine sample and satisfactory results were obtained.     

固定化尿酸酶丝素膜的性质及其尿酸传感器

应用电化学分析法对固定化酶丝素膜的性质进行了分析,结果表明这种酶经丝素膜固定后,活性得率高、性能稳定、能长期存放.用这种酶膜和氧电极等组成的流动注射分析式尿酸传感器对生物样品进行的百次重复分析结果表明,这种传感器的重现性良好,每小时能分析60个人血清样品.     

Glucose biosensor based on immobilization of glucose oxidase in poly(o-aminophenol) film on polypyrrole-Pt nanocomposite modified glassy carbon electrode

Novel Pt nanoclusters embedded polypyrrole nanowires (PPy-Pt) composite was electrosynthesized on a glassy carbon electrode, denoted as PPy-Pt/GCE. A glucose biosensor was further fabricated based on immobilization of glucose oxidase (GOD) in an electropolymerized non-conducting poly(o-aminophenol) (POAP) film that was deposited on the PPy-Pt/GCE. The morphologies of the PPy nanowires and PPy-Pt nanocomposite were characterized by field emission scanning electron microscope (FE-SEM). Effect of experimental conditions involving the cycle numbers for POAP deposition and Pt nanoclusters deposition, applied potential used in glucose determination, temperature and pH value of the detection solution were investigated for optimization. The biosensor exhibited an excellent current response to glucose over a wide linear range from 1.5 × 10⁻⁶ to 1.3 × 10⁻² M (r = 0.9982) with a detection limit of 4.5 × 10⁻⁷ M (s/n = 3). Based on the combination of permselectivity of the POAP and the PPy films, the sensor had good anti-interference ability to ascorbic acid (AA), uric acid (UA) and acetaminophen. The apparent Michaelis–Menten constant (K_m) and the maximum current density (I_m) were estimated to be 23.9 mM and 378 μA/cm², respectively. In addition, the biosensor had also good sensitivity, stability and reproducibility.     

The development of an amperometric microbial biosensor using Acetobacter pasteurianus for lactic acid

A microbial biosensor, using Acetobacter pasteurianus cells and an oxygen electrode, was developed for the determination of lactic acid. The bacterial cells were retained on a nylon membrane and attached to the surface of the oxygen electrode. In view of response time, stability and sensitivity, the biosensor performed best at 26°C and in pH 6 phthalate buffer containing magnesium sulfate. The activity of the retained cells was stable for approximately 170 h and was regenerable. The biosensor exhibited a hyperbolic response to both D- and L-lactic acid in the range of 10⁻⁴ M to 25 × 10⁻³ M. However, in the range 10⁻⁴ M to 15 × 10⁻⁴ M the response was linear. The microbial biosensor was applicable for detecting lactate concentration in yogurt and milk, since it was not sensitive to lactose, sucrose and glucose — three major components of such dairy products.     

Simultaneous determination of ascorbic acid, dopamine and uric acid using high-performance screen-printed graphene electrode

A disposable and sensitive screen-printed electrode using an ink containing graphene was developed. This electrode combined the advantages of graphene and the disposable characteristic of electrode, which possessed wide potential window, low background current and fast electron transfer kinetics. Compared with the electrodes made from other inks, screen-printed graphene electrode (SPGNE) showed excellent electrocatalytic activity for the oxidation of ascorbic acid (AA), dopamine (DA), and uric acid (UA). Three well-defined sharp and fully resolved anodic peaks were found at the developed electrode. Differential pulse voltammetry was used to simultaneous determination of AA, DA, and UA in their ternary mixture. In the co-existence system of these three species, the linear response ranges for the determination of AA, DA, and UA were 4.0-4500 μM, 0.5-2000 μM, and 0.8-2500 μM, respectively. The detection limits (S/N=3) were found to be 0.95 μM, 0.12 μM, and 0.20 μM for the determination of AA, DA, and UA, respectively. Furthermore, the SPGNE displayed high reproducibility and stability for these species determination. The feasibility of the developed electrode for real sample analysis was investigated. Results showed that the SPGNE could be used as a sensitive and selective sensor for simultaneous determination of AA, DA, and UA in biological samples, which may provide a promising alternative in routine sensing applications.     

Immobilization of uricase on protamine bound to glass beads and its application to determination of uric acid

Uricase was found to be stabilized by protamine from salmon testis. Protamine was then bound to controlled-pore glass beads aminohexyl CPG 500 using glutaraldehyde. Microbial uricase was readily immobilized on the protamine bound to glass beads. The immobilized uricase proved to be stable even at 70 degrees C, whereas free uricase was inactivated at 45 degrees C and showed activity over a broader pH range than free uricase. Automated analysis of uric acid was facilitated using the immobilized uricase. The standard curve for uric acid was linear in the range of 2 to 10 micrograms/sample and passed through the origin. This automated procedure was also applicable to the determination of uric acid in human serum. Protamine bound to glass beads is expected to be useful for the simple immobilization and stabilization of enzymes.     

Development of a screen-printed amperometric biosensor for the determination of L-lactate dehydrogenase level.

We attempted to develop a screen-printed biosensor for the amperometric determination of L-lactate dehydrogenase (LDH) level on the basis of NAD(+)/NADH-dependent dehydrogenase reaction. The printing ink for the working electrode consisted of L-lactate, NAD(+), composite polymer of hydroxyethyl cellulose with ethylene glycol, 3,4-dihydroxybenzaldehyde (3,4-DHB) as an electron transferring mediator, and graphite as the conducting material. The 3,4-DHB was electropolymerized on the carboneous working electrode by potential cycling between -200 and +300 mV vs. Ag/AgCl reference electrode. Through the electrocatalytic reaction with immobilized 3,4-DHB, the NADH generated by the LDH reaction could be efficiently oxidized at lower potential than the unmodified carbon electrode. The analytical performance of the electrode was characterized in terms of linear sensing range and detection limit for LDH. The response from the developed biosensor was linear up to 500 U/l of LDH, and the detection limit of 50 U/l was observed at the signal-to-noise ratio of 3.     

Highly sensitive and selective uric acid biosensor based on RF sputtered NiO thin film

Present study highlights the importance of RF sputtered NiO thin film deposited on platinum coated glass substrate (NiO/Pt/Ti/glass) as a potential matrix for the realization of highly sensitive and selective uric acid biosensor. Uricase has been immobilized successfully onto the surface of NiO matrix by physical adsorption technique. The prepared bioelectrode (uricase/NiO/Pt/Ti/glass) is utilized for sensing uric acid using the cyclic voltammetry and UV visible spectroscopy techniques. The bioelectrode is found to exhibit highly efficient sensing response characteristics with high sensitivity of 1278.48 μA/mM; good linearity of 0.05-1.0 mM, and very low Michaelis-Menten constant (k(m)) of 0.17 mM indicating high affinity of uricase towards the analyte. The enhanced response is due to the development of NiO matrix with good electron transport property and nanoporous morphology for effective loading of enzyme with preferred orientation.     

Application of a quartz crystal nanobalance to the molecularly imprinted recognition of phenylalanine in solution

A quartz crystal nanobalance (QCN) biosensor was developed for the selective determination of phenylalanine (Phe) in aqueous solutions. A Phe imprinted copolymer was synthesized using polyacrylonitrile and acrylic acid [poly(AN-co-AA)]. The copolymer was then coated on quartz crystal electrode to form complementary structures for the template recognition of Phe. The composite electrode was then used to determine Phe levels in solution. Determinations were based on frequency shifts of molecularly imprinted polymer (MIP) modified quartz crystal electrode caused by Phe adsorption. The frequency shifts were linearly dependent on Phe concentration over the range 50∼500 mgL⁻¹. The results obtained show that the imprinted poly(AN-co-AA) modified biosensor had higher sensitivity (0.5839 Hz/mgL⁻¹) than a non-molecularly imprinted copolymer (0.2724 Hz/mgL⁻¹). Furthermore, good reproducibility, R.S.D. = 1.84% (n = 7) was observed, and the detection limit was 45 mgL⁻¹. The selectivity of the imprinted poly(AN-co-AA) modified biosensor was examined using a number of analytes similar to Phe, i.e., dopamine (DA), ascorbic acid (AscA), vanillylmandelic acid (VMA), uric acid (UA), tryptophan (Trp), and tyrosine (Tyr), and the results obtained showed a size dependent selective effect.     

Amperometric determination of choline released from rat submandibular gland acinar cells using a choline oxidase biosensor

A choline (CHO) biosensor based on the determination of H(2)O(2) generated at the electrode surface by the enzyme choline oxidase (CHOx) was developed. The biosensor consisted of CHOx retained onto a horseradish peroxidase (HRP) immobilized solid carbon paste electrode (sCPE). The HRPsCPE contained the molecule phenothiazine as redox mediator and CHOx was physically retained on the electrode surface using a dialysis membrane. Several parameters have been studied such as, mediator amount, influence of applied potential, etc. The CHO measurements were performed in 0.1 M phosphate buffer, pH 7.4. Amperometric detection of CHO was realized at an applied potential of 0.0 mV vs Ag/AgCl. The response is linear over the concentration range 5.0x10(-7)-7.0x10(-5) M, with a detection limit of 1.0x10(-7) M. This biosensor was used to detect choline released from phosphatidylcholine (PC) by phospholipase D (PLD) in isolated rat salivary gland cells stimulated by a purinergic agonist (ATP).     

An amperometric uric acid biosensor based on multiwalled carbon nanotube-gold nanoparticle composite

An amperometric uric acid biosensor was fabricated by immobilizing uricase (EC 1.7.3.3) onto gold nanoparticle (AuNP)/multiwalled carbon nanotube (MWCNT) layer deposited on Au electrode via carbodiimide linkage. Determination of uric acid was performed by oxidation of enzymically generated H₂O₂ at 0.4 V. The sensor showed optimal response within 7 s at 40 °C in 50 mM Tris–HCl buffer (pH 7.5). The linear working range of the biosensor was 0.01–0.8 mM. The limit of detection (LOD) was 0.01 mM. The sensor measured uric acid levels in serum of healthy individuals and persons suffering from gout. The analytical recoveries of the added uric acid, 10 and 20 mg L^–1, were 98.0% and 96.5%, respectively. Within- and between-batch coefficients of variation were less than 5.6% and less than 4.7%, respectively. A good correlation (r = 0.998) was obtained between serum uric acid values by the standard enzymic colorimetric method and the current method. A number of serum substances had practically no interference. The sensor was used in more than 200 assays and had a storage life of 120 days at 4 °C.     

Development of disposable lipid biosensor for the determination of total cholesterol

A prototype chronoamperometric biosensor for the determination of total cholesterol was developed that consists of a homemade potentiostat and disposable strips immobilized with Fe(3)O(4), cholesterol oxidase (ChOx), and cholesterol esterase (ChE). The principle of sensing cholesterol is based on the detection of reduction signal of hydrogen peroxide generated in two enzymatic reactions. The co-immobilization of ChE and ChOx allows the sensor to detect both concentrations of esterified and free cholesterol. The effects of biosensor on catalyst, enzymes, applied potential, and buffer pH was investigated, and the operation conditions were optimized. The detection of cholesterol can be accomplished in one step, a 10 microL of sample was dropped onto the area of sensing strip and the reduction signal was obtained at an applied potential of -200 mV (vs. Ag/Ag(+)). The pre-reaction time was set at 15s before applying potential on the strip and the sampling time was 5s. The sensing device displays a linear response over the range of 100-400mg/dL (R(2)=0.999) for cholesteryl oleate. The coefficient variation was determined as 5.06% (N=20) for 100mg/dL cholesteryl oleate and the detection limit is 19.4 mg/dL (S/N=3). The probable interferences in bio-matrix were selected to test the selectivity and no significant response was observed in the biosensor.     

Capillary-driven multiparametric microfluidic chips for one-step immunoassays

A new zinc oxide nanoparticles/chitosan/carboxylated multiwall carbonnanotube/polyaniline (ZnO-NPs/CHIT/c-MWCNT/PANI) composite film has been synthesized on platinum (Pt) electrode using electrochemical techniques. Three enzymes, creatinine amidohydrolase (CA), creatine amidinohydrolase (CI) and sarcosine oxidase (SO) were immobilized on ZnO-NPs/CHIT/c-MWCNT/PANI/Pt electrode to construct the creatinine biosensor. The enzyme electrode was characterized by scanning electron microscopy (SEM), Fourier transform infrared (FTIR) spectroscopy and electrochemical impedance spectroscopy (EIS). The enzyme electrode detects creatinine level as low as 0.5 μM at a signal to noise ratio of 3 within 10s at pH 7.5 and 30°C. The fabricated creatinine biosensor showed linear working range of 10-650 μM creatinine with a sensitivity of 0.030 μA μM(-1)cm(-2). The biosensor shows only 15% loss of its initial response over a period of 120 days when stored at 4°C. The fabricated biosensor was successfully employed for determination of creatinine in human blood serum.