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An AFM determination of the effects on surface roughness caused by cleaning of fused silica and glass substrates in the process of optical biosensor preparation.

The covalent attachment of organic films and of biological molecules to fused silica and glass substrates is important for many applications. For applications such as biosensor development, it is desired that the immobilised molecules be assembled in a uniform layer on the surface so as to provide for reproducibility and speed of surface interactions. For optimal derivatisation the surface must be appropriately cleaned to remove contamination, to create surface attachment sites such as hydroxyl groups, and to control surface roughness. The irregularity of the surface can be significant in defining the integrity and density of immobilised films. Numerous cleaning methods exist for fused silica and glass substrates and these include gas plasmas, and combinations of acids, bases and organic solvents that are allowed to react at varying temperatures. For many years, we have used a well established method based on a combination of washing with basic peroxide followed by acidic peroxide to clean and hydroxylate the surface of fused silica and glass substrates before oligonucleotide immobilisation. Atomic force microscopy (AFM) has been used to evaluate the effect of cleaning on surface roughness for various fused silica and glass samples. The results indicate that surface roughness remains substantial after use of this common cleaning routine, and can provide a surface area that is more than 10% but less than 30% larger than anticipated from geometric considerations of a planar surface.

Biosensing Techniques↗

Missing mass effect in biosensor's QCM applications.

Nowadays, liquid applications of quartz crystal microbalance (QCM) opened a way for in situ studies of proteins, vesicles and cells adsorbed from the solution onto the QCM surface. The sensitivity of QCM to the viscoelasticity of the adsorbed biomaterial can be a reason of the experimentally observed deviation from a linear dependence of QCM resonant frequency on mass deposition (the so-called Sauerbrey relation) and can limit its application for biosensoring. Presented here rigorous theoretical analysis explains the deviation from ideal mass response of soft overlayers in the contact with liquid. The fundamental result of the theory is the analog of Sauerbrey relation for layered viscous/viscoelastic medium which can be exploited for the correct physical interpretation of QCM experimental data in biofluids, in particular for measurements of the 'true' surface mass of adsorbed biomolecular films. We predict a new physical effect 'missing mass' of the sample in liquid phase measurements and compare the results given by our theory with QCM measurements on supported membranes.

Adsorption↗

A comparison of imaging methods for use in an array biosensor.

An array biosensor has been developed which uses an actively-cooled, charge-coupled device (CCD) imager. In an effort to save money and space, a complementary metal-oxide semiconductor (CMOS) camera and photodiode were tested as replacements for the cooled CCD imager. Different concentrations of CY5 fluorescent dye in glycerol were imaged using the three different detection systems with the same imaging optics. Signal discrimination above noise was compared for each of the three systems.

Biosensing Techniques↗

Amperometric biosensors for detection of phenol using chemically modified electrodes containing immobilized bacteria.

Eight strains of Pseudomonas were studied for development of phenol sensor. The immobilization of cells was performed by absorbing them on the working part of mediator-modified screen-printed electrodes (SPEs). Only three Pseudomonas strains were able to transfer electrons resulting from specific oxidation of phenol to the electrode by means of mediators; ferrocene, duroquinone and dimethyferrocene were successfully used with the strains 394 (p20), 74-III and 83-IV (working names), respectively. The lower limits for detection of phenol were 1 micro M for the strain 74-III and 10 micro M for the strain 83-IV and 394 (p20). Calibrations were obtained as the dependencies of logarithm of current changes (log deltaI) on logarithm of concentration (logC), log delta I vs. logC. Among all substrates tested (phenol, catechol, hydroquinone, ethanol, methanol, propanol, isopropanol, isobutanol, isoamylalcohol, acetate, glucose, xylose, vanillin, 2,4,6-trichlorphenol, 2,3,6-trichlorphenol, 4-hydroxy-3-methoxybenzoic acid, coumarin, pentafluorophenol), bacterial sensor demonstrated a good selectivity with respect to phenol and lower responses to catechol and hydroquinone (10-times lower). The dependence of signals on operating conditions was studied. The biosensor should be used during the day of preparation. The operational stability was satisfactory to perform up to 10 consecutive measurements. Low cost and very simple manufacturing procedure allow for bacterial sensor to be applied as disposable devices.

Biosensing Techniques↗

A hydrogen biosensor made of clay, poly(butylviologen), and hydrogenase sandwiched on a glass carbon electrode.

A hydrogen gas (H(2)) biosensor was developed in which hydrogenase (H(2)ase) was immobilized and sandwiched between two layers of a montmorillonite clay and poly(butylviologen) (PBV) mixture on a glass carbon electrode. The immobilized PBV efficiently enhanced the electron transfer among the electrode, H(2)ase, and methyl viologen in solution. Both PBV and methyl viologen acted as the electron carrier in the clay-PBV-H(2)ase modified electrode. The clay-PBV-H(2)ase electrode catalyzed the oxidation of H(2) to protons (H(+)) with the electrons being transferred by viologen groups to the electrode. The activation energy of this process was 38+/-2 kJ/mol at pH 7. The catalytic current of the clay-PBV-H(2)ase electrode increased linearly when exposed to increasing concentrations of H(2) gas. In contrast, this electrode showed no activity when exposed to three combustible compounds, namely, carbon monoxide, methane and methanol. The optimum pH range for the oxidation of H(2) by the clay-PBV-H(2)ase electrode was from 7 to 10. Electron transfer process in the clay-PBV-H(2)ase electrode is discussed.

Aluminum Silicates↗

Detection of the damage caused to DNA by niclosamide using an electrochemical DNA-biosensor.

Niclosamide is the only commercially available molluscicide recommended by the WHO for large-scale use in schistosomiasis control programs. The electrochemical reduction and oxidation mechanism of niclosamide was studied using cyclic, differential and square wave voltammetry, at a glassy carbon electrode. An indirect procedure for in situ quantification of niclosamide using batch injection analysis with electrochemical detection, possible to be used for in situ determinations in river streams and effluents, was developed. It enabled a detection limit of 8 x 10(-7) M. The investigation of the niclosamide-DNA interaction using an electrochemical DNA-biosensor showed for the first time clear evidence of interaction with DNA and suggested that niclosamide toxicity can be caused by this interaction, after reductive activation.

Animals↗

Oxygen-independent poly(dimethylsiloxane)-based carbon-paste glucose biosensors.

Several silicone oils have been assessed and compared as an internal source of oxygen in connection to their use as binders for carbon-paste glucose biosensors. All four poly(dimethylsiloxane) (PDMS) oils tested a dramatic increase in the oxygen capacity of carbon-paste enzyme electrodes to allow convenient biosensing under severe oxygen-deficit conditions. The resulting oxygen independence is better than that exerted by perfluorocarbon binders or that displayed by mediator-based bioelectrodes. The resistance to oxygen effects is indicated from the identical response (observed in the presence and absence of oxygen) up to 2 x 10(-2) M glucose and the slight (12%) sensitivity loss at 4 x 10(-2) M. The influence of the viscosity of the PDMS binder upon the internal oxygen supply is examined. The PDMS carbon-paste enzyme electrode displays a stable glucose response over prolonged (15 h) operation in an oxygen-free solution. On-line continuous testing indicates favorable dynamic properties with no carry-over effects over the physiological and pathophysiological range (3-12 mM glucose).

Biosensing Techniques↗

Reagentless biosensors based on co-entrapment of a soluble redox polymer and an enzyme within an electrochemically deposited polymer film.

A novel biosensor architecture, which is based on the combination of a manual and a non-manual deposition technique for sensor components on the electrode surface is reported. A water-soluble Os-poly(vinyl-imidazole) redox hydrogel is deposited on a graphite electrode by drop-coating (i.e. manually) followed by the electrochemically-induced deposition of an enzyme-containing non-conducting polymer film. The local polymer deposition is initiated by electrochemical generation of H(3)O(+) exclusively at the electrode surface causing a pH-shift to be established in the diffusion zone around the electrode (i.e. non-manually). This pH-shift leads to the protonation of a dissolved polyanionic polymer which in consequence changes significantly its solubility and is hence precipitating on the electrode surface. In the presence of a suitable enzyme, such as quinohemoprotein alcohol dehydrogenase (QH-ADH), the polymer precipitation leads to an entrapment of the redox enzyme within the polymer film. Simultaneously, the water-soluble Os-poly(vinyl-imidazole) redox hydrogel, which is slowly dissolving from the electrode surface after addition of the electrolyte, is co-entrapped within the precipitating polymer layer. This provides the pre-requisite for an efficient electron-transfer pathway from the redox enzyme via the polymer-bound redox centres to the electrode surface. The sensor preparation protocol has been optimised aiming on a high mediator concentration in the polymer film and an effective electron transfer.

Alcohol Oxidoreductases↗

Microbial biosensor array with transport mutants of Escherichia coli K12 for the simultaneous determination of mono-and disaccharides.

An automated flow-injection system with an integrated biosensor array using bacterial cells for the selective and simultaneous determination various mono- and disaccharides is described. The selectivity of the individually addressable sensors of the array was achieved by the combination of the metabolic response, measured as the O(2) consumption, of bacterial mutants of Escherichia coli K12 lacking different transport systems for individual carbohydrates. Kappa-carrageenan was used as immobilization matrix for entrapment of the bacterial cells in front of 6 individually addressable working electrodes of a screen-printed sensor array. The local consumption of molecular oxygen caused by the metabolic activity of the immobilized cells was amperometrically determined at the underlying screen-printed gold electrodes at a working potential of -600 mV vs. Ag/AgCl. Addition of mono- or disaccharides for which functional transport systems exist in the used transport mutant strains of E. coli K12 leads to an enhanced metabolic activity of the immobilized bacterial cells and to a concomitant depletion of oxygen at the electrode. Parallel determination of fructose, glucose, and sucrose was performed demonstrating the high selectivity of the proposed analytical system.

Biofilms↗

Near real-time biosensor-based detection of 2,4-dinitrophenol.

A fluorescent biosensor assay has been developed for near real-time detection of 2,4-dinitrophenol (DNP). The assay was based on fluorescent detection principles that allow for the analysis of antibody/antigen interactions in solution using the KinExA immunoassay instrument. Our KinExA consisted of a capillary flow observation cell containing a microporous screen that maintains a compact capture antigen-coated bead bed. The bead bed was comprised of polymethylmethacrylate (PMMA) beads coated with dinitrophenol-human serum albumin (DNP-HSA) conjugate. Phosphate buffered saline (PBS) solutions, containing various concentrations of free DNP, were incubated for 30 min with mouse anti-DNP monoclonal antibody to equilibrium. Solutions containing the DNP-monoclonal antibody complex and possible excess free antibodies were then passed over DNP-HSA labeled beads. The free monoclonal anti-DNP antibody, if available, was then bound to the DNP-HSA fixed on the beads. The system was then flushed with excess PBS to remove unbound reactants in the bead bed. The beads were then subjected to brief contact with PBS solutions containing goat anti-mouse fluorescein isothiocyanate (FITC)-labeled secondary antibody, once again, followed by a short PBS flush. The fluorescence was recorded during the addition of the FITC labeled secondary antibody to the bead bed through the final PBS flushing with the KinExA. The amount of DNP detected could then be determined from the fluorescent slopes that were generated or by the remaining fluorescence that was retained on the beads after final PBS flushing of the system. This assay has been able to detect a minimum of 5 ng/ml of DNP in solution and can be adapted for other analytes of interest simply by changing the capture antigen and antibody pairs.

2,4-Dinitrophenol↗

Spatially resolved monitoring of cellular metabolic activity with a semiconductor-based biosensor.

Metabolic activity of cultured cells can be monitored by measuring changes in the pH of the surrounding medium caused by metabolic products such as protons, carbon dioxide or lactic acid. Although many systems designed for this purpose have been reported, almost all of them are based on bulk measurements, where the average metabolic activity of all cells in contact with the device is recorded. Here, we report on a novel biosensor, based on a modified light-addressable potentiometric sensor (LAPS) device, which enables the metabolic activity of cultured cells to be measured with spatial resolution. This is demonstrated here by detecting the differential sensitivity to a cholinergic receptor agonist of two different co-cultured cellular populations. By making simultaneous measurements of the metabolic activity of different cell types seeded on different segments of one sensor, this device not only provides a rapid means of assessing cellular specificity of pharmaceutical compounds but also has the potential of being used to non-invasively monitor humoral as well as synaptic communication between different cell populations in co-culture. The temporal and spatial resolution of the device were investigated and are discussed.

Animals↗

In vivo CH3(CH2)11SAu SAM electrodes in the beating heart: in situ analytical studies relevant to pacemakers and interstitial biosensors.

To study in vivo modification of the SAM equivalent circuit when a highly ordered SAM is used as a bioelectrode, dodecanethiolate SAM-Au intramuscular electrodes were studied in living rat heart in a challenging in situ perfused rat model by impedance spectroscopy, cyclic voltammetry, and neutron activation analysis (NAA). The SAM layer experienced disintegration in vivo biological system, as NAA detected the presence of Au atoms that had leached into the surrounding living tissue. Therefore, the underlying Au surface became exposed during biological implant. Study by impedance spectroscopy, however, revealed perfect capacitive behavior for the SAM, similar to in vitro behavior. Electrodes showed a pure capacitive Nyquist plot with 86.1-89.4 degrees near-vertical line segments as the equivalent circuit locus, as for a parallel plate capacitor. Impedance magnitude varied linearly with 1/omega excluding diffusionally limited ionic charge transport. There was no diffusional conductive element Z(W infinity ) or spatially confined Warburg impedance Z(D). The effect of in vivo exposure of a highly ordered SAM is a 'sealing over' effect of new defects by the binding of proteinaceous or lipid species in the biological milieu, a fact of significance for SAM electrodes used either as pacemaker electrodes or as a platform for in vivo biosensors.

Animals↗

Lipid membrane immobilized horseradish peroxidase biosensor for amperometric determination of hydrogen peroxide.

Stable films of didodecyldimethylammonium bromide (DDAB, a synthetic lipid) and horseradish peroxidase (HRP) were made by casting the mixture of the aqueous vesicle of DDAB and HRP onto the glassy carbon (GC) electrode. The direct electron transfer between electrode and HRP immobilized in lipid film has been demonstrated. The lipid films were used to supply a biological environment resembling biomembrane on the surface of the electrode. A pair of redox peaks attributed to the direct redox reaction of HRP were observed in the phosphate buffer solution (pH 5.5). The cathodic peak current increased dramatically while anodic peak decreased by addition of small amount H(2)O(2). The pH effect on amperometric response to H(2)O(2) was studied. The biosensor also exhibited fast response (5 s), good stability and reproducibility.

Biosensing Techniques↗

Optical biosensor for urea with improved response time.

An optical biosensor for urea measurements was developed. The operation of the sensor is based on the well-known urease enzyme-catalyzed hydrolysis of urea. The ammonium ions liberated in the reaction are detected with an ion selective optode membrane containing nonactin as ion selective ionophore and ETH 5294 chromoionophore in a thin (1 microm) plasticized poly(vinylchloride) film. The basic sensing element was home made of a microscope glass slide, a HeNe laser light source, photodiode light detector and light in coupling, de-coupling elements. The transducer membrane and the enzyme containing reaction layer were sandwich-cast with spin coating onto the surface of the sensing slide. The attenuation of the laser light propagating inside the glass wave-guide was used as signal for urea measurements. With this arrangement membranes provided good sensitivity (0.05 absorption unit when going from 0.1 to 1 mM urea) and short (16-20 s) response time. Taking advantage on the improved response time, flow injection urea measurements were made in the 0.01-2 mM concentration range. Thirty sample/hour analysis-rate, good peak-to-peak reproducibility (RSD=0.02) and recovery (95-104%) was achieved with buffer diluted urea solutions. Applications for the analysis of real samples are planned to do in the future.

Biosensing Techniques↗

Detection of pesticides using an amperometric biosensor based on ferophthalocyanine chemically modified carbon paste electrode and immobilized bienzymatic system.

A new highly sensitive amperometric method for the detection of organophosphorus compounds has been developed. The method is based on a ferophthalocyanine chemically modified carbon paste electrode coupled with acetylcholinesterase and choline oxidase co-immobilized onto the surface of a dialysis membrane. The activity of cholinesterase is non-competitively inhibited in the presence of pesticides. The highest sensitivity to inhibitors was found for a membrane containing low enzyme loading and this was subsequently used for the construction of an amperometric biosensor for pesticides. Analyses were done using acetylcholine as substrate; choline produced by hydrolysis in the enzymatic layer was oxidized by choline-oxidase and subsequently H(2)O(2) produced was electrochemically detected at +0.35 V vs. Ag/AgCl. The decrease of substrate steady-state current caused by the addition of pesticide was used for evaluation. With this approach, up to 10(-10) M of paraoxon and carbofuran can be detected.

Acetylcholinesterase↗

Enzyme inhibition-based biosensors and biosensing systems: questionable analytical devices.

An overview of methods based on enzyme inhibition is presented. Both biosensors and biosensing systems (implemented in continuous and discontinuous approaches) are considered. The aim of the overview is to alert users on the use of these devices which, despite they can involve selective biocatalysts, the inhibition effect is not selective. Tables and examples illustrate this assertion.

Biosensing Techniques↗

Rapid identification of viable Escherichia coli subspecies with an electrochemical screen-printed biosensor array.

Rapid identification of Escherichia coli strains is an important diagnostic goal in applied medicine as well as the environmental and food sciences. This paper reports an electrochemical, screen-printed biosensor array, where selective recognition is accomplished using lectins that recognize and bind to cell-surface lipopolysaccharides and coulometric transduction exploits non-native external oxidants to monitor respiratory cycle activity in lectin-bound cells. Ten different lectins were separately immobilized onto porous membranes that feature activated surfaces (ImmunodyneABC). Modified membranes were exposed to untreated E. coli cultures for 30 min, rinsed, and layered over the individual screen-printed carbon electrodes of the sensor array. The membranes were were incubated 5 min in a reagent solution that contained the oxidants menadione and ferricyanide as well as the respiratory substrates succinate and formate. Electrochemical oxidation of ferrocyanide for 2 min provided chronocoulometric data related to the quantities of bound cells. These screen-printed sensor arrays were used in conjunction with factor analysis for the rapid identification of four E. coli subspecies (E. coli B, E. coli Neotype, E. coli JM105 and E. coli HB101). Systematic examination of lectin-binding patterns showed that these four E. coli subspecies are readily distinguished using only five essential lectins.

Agglutination Tests↗

Application of atomic force microscopy and grating coupler for the characterization of biosensor surfaces.

Atomic force microscopy (AFM) and an optical grating coupler system were used to improve the understanding of the biosensing layer on a Ta(2)O(5)-light-guiding surface. Exemplary, we investigated the immobilization of the protein avidin, the subsequent binding of biotinylated oligonucleotides and hybridization of a complementary 12-mer. The AFM measurements revealed the height of approximately 1.6 nm for a single avidin molecule, while the thickness of the avidin layer on the biosensor surface seemed to be 2.8-3.0 nm. This result lead to the conclusion that the protein was not forming a simple monolayer. However, the thickness of the avidin layer could not be determined directly, but only after shifting of protein by the tip of the AFM leading to grooves of 1 micro m(2) and approximately 3 nm depth. As the height of oxide particles forming the waveguide surface was also in the range of 1.5 nm, the depth of these grooves could also be a result of the deposition of proteins on top of the oxide particles. This was consistent with the increased roughness of the surface after protein binding. Thus, investigations with the grating coupler were used to determine quantitatively the amount of immobilized avidin. On a biotinylated surface the amount of immobilized avidin lead to the assumption of a complete monolayer, whereas simple adsorption proved to be less efficient. A binding ratio of 1:1.3 for avidin and a biotinylated oligonucleotide was achieved. Up to 83% of the bound single strand were accessible for a subsequent hybridization reaction with a 12-mer. These results supported the model of avidin being deposited mainly on top of the oxide particles leading to the picture of a 'rough' complete protein monolayer, which was postulated from the AFM investigations.

Avidin↗