“…This procedure was chosen in line with work reported by other researchers [15] after checking that 2 h was sufficient as reported by others [16]. Other authors [17] do not indicate the conditioning time before the first measurement.…”
A biosensor for the detection of insecticides based on an ion-sensitive field-effect transistor (ISFET) was developed. The resulting device combines the simplicity of potentiometric sensors and the use of associated electronic systems as powerful tools for the acquisition and the processing of data. The enzyme acetylcholinesterase (AChE) was entrapped in a membrane placed on the gate of the ISFET forming an enzyme field-effect transistor (EnFET). The biosensor is applied to the determination of pesticides in spiked real samples. Organophosphorous and carbamate insecticides were measured with a detection limit of 10(-8) mol L(-1). The measurement is based on the production of hydrogen ions due to the hydrolysis of acetylthiocholine by the enzyme. The resulting local pH change is picked up by the underlying pH-sensitive ISFET and transduced as potential variations. The preparation of the membrane is simple and reproducible. The analysis in spiked real samples was performed in tap water and showed detection limits comparable to those obtained by other researchers.
“…This procedure was chosen in line with work reported by other researchers [15] after checking that 2 h was sufficient as reported by others [16]. Other authors [17] do not indicate the conditioning time before the first measurement.…”
A biosensor for the detection of insecticides based on an ion-sensitive field-effect transistor (ISFET) was developed. The resulting device combines the simplicity of potentiometric sensors and the use of associated electronic systems as powerful tools for the acquisition and the processing of data. The enzyme acetylcholinesterase (AChE) was entrapped in a membrane placed on the gate of the ISFET forming an enzyme field-effect transistor (EnFET). The biosensor is applied to the determination of pesticides in spiked real samples. Organophosphorous and carbamate insecticides were measured with a detection limit of 10(-8) mol L(-1). The measurement is based on the production of hydrogen ions due to the hydrolysis of acetylthiocholine by the enzyme. The resulting local pH change is picked up by the underlying pH-sensitive ISFET and transduced as potential variations. The preparation of the membrane is simple and reproducible. The analysis in spiked real samples was performed in tap water and showed detection limits comparable to those obtained by other researchers.
“…Both have obtained premarket approval by the FDA. Based on previous work [53,54] we developed a glucose sensor for continuous monitoring in interstitial fluid (Fig. 5).…”
Section: Glucose Sensor For Continuous Monitoring In Interstitial Fluidmentioning
Based on electrical biochips made in Si-technology cost effective portable devices have been constructed for field applications and point of care diagnosis. These miniaturized amperometric biosensor devices enable the evaluation of biomolecular interactions by measuring the redox recycling of ELISA products, as well as the electrical monitoring of metabolites. The highly sensitive redox recycling is facilitated by interdigitated ultramicroelectrodes of high spatial resolution. The application of these electrical biochips as DNA microarrays for the molecular diagnosis of viral infections demonstrates the measurement procedure. Self-assembling of capture oligonucleotides via thiol-gold coupling has been used to construct the DNA interface on-chip. Another application for this electrical detection principle is continuous measuring with bead-based biosensors. Here, paramagnetic nanoparticles are used as carriers of the bioanalytical interface in ELISA format. A Si-micromachined glucose sensor for continuous monitoring in interstitial fluid ex vivo shows the flexibility of the electrical platform. Here the novel approach is a pore membrane in micrometer-dimensions acting as a diffusion barrier. The electrochemical detection takes place in a cavity containing glucose oxidase and a Pt-electrode surface. The common hydrogen peroxide detection, together with Si technology, enable precise differential measurements using a second cavity.
“…The PU component was responsible for the adhesion and uniformity of the immobilization layer [27,28]; while the PEO (a well-known polyelectrolyte) ensured homogonous distribution of enzyme and retained a high water content within the immobilization layer. The latter is crucial for enzyme kinetics and activity.…”
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