Modelling of the Potentiometric Response of ENFETs Based on Enzymatic Multilayer Membranes

Aouni, F.; Mlika, R.; Martelet, C.; Ouada, H. Ben; Jaffrézic‐Renault, Nicole

doi:10.1002/elan.200403079

Cited by 10 publications

(3 citation statements)

References 18 publications

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“…This allows the indirect determination of other reactants and products of the enzymatic reaction. EnFETs based on H + / OH − detection (enzymes immobilized on a pH-ISFET) were utilized for the biosensing of various analytes, such as glutamate [30] , glucose [31][32][33][34] , urea [35][36][37][38][39][40] , lactate [41] , penicillin [42,43] , and glykoalkaloids [44] . ISFETs are mostly used as pH-ISFETs in CBBs for cell microenvironment monitoring and sensing of the extracellular acidification rate (ECAR).…”

Section: Isfetmentioning

confidence: 99%

Label-free and Multi-parametric Monitoring of Cell-based Assays with Substrate-embedded Sensors

Oberleitner

2018

Springer Theses

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These cellular responses and the accompanying changes of physicochemical parameters are what is to be detected and transferred into a measurable electrical signal by the transducer units of the label-free biosensor devices (Fig. 1-1). There are various types of transducers, distinguishable by the underlying physicochemical phenomenon: electrochemical (including potentiometric, amperometric, and impedimetric), optical, thermometric, piezoelectric, and magnetic transduction. [8] Tab. 1-1 gives an LAPSLight-addressable potentiometric sensors (LAPSs) are multilayer field-effect devices similar to ISFETs [66] . A LAPS consists of a doped semiconductor covered with an insulator layer and a chemosensitive layer. The device is immersed in an electrolyte solution. The semiconductor is connected with a reference electrode in contact with the electrolyte (Fig. 1-2 B; reviewed in [10,17,[67][68][69][70] with respect to biological and cell-based applications). The insulator material of LAPSs is typically made up either of a single SiO 2 layer 1.1 Label-free Biosensors for Cell-based Assays 7 chip-based systems for the label-free and continuous monitoring of DO in cell-based assays, i.e. the oxygen consumption rate (OCR) of cells. [47,48,50,53,54,57,[60][61][62] The sensor chips with integrated amperometric oxygen sensors are typically build up as multi-parametric sensors and contain further physicochemical transducer structures like e.g. for cell morphology testing and ECAR monitoring. Besides the direct measurement of DO, the amperometric sensors are also capable of sensing indirectly any species that is consumed or produced in an oxidase-based enzymatic reaction (amperometric enzyme sensor) via the oxygen or hydrogen peroxide concentration. For this purpose, the amperometric pO 2 sensor is coated with a layer in which the respective enzyme is immobilized and which enables free diffusion of all reactants between the bulk solution and the sensor surface. This approach was first presented by Clark and Lyons as an amperometric sensor for glucose [85] and has also been applied as transduction method in cell-based assays for the label-free determination and monitoring of glucose and lactose [78,79] . A list of physiologically relevant analytes that have been successfully monitored by amperometric enzyme sensors is given in [86] . ECISElectrical impedance-based sensing of adherent cells, also termed as electric cell-substrate impedance sensing (ECIS), utilizes the property of cells to impede AC current flow when they are in close contact to the substrate, i.e. a small gold-film working electrode (Fig. 1-2 D). This technique was presented first by Giaever and Keese in 1984 [87] as "morphological biosensor for mammalian cells" [88] . The principle of ECIS, the method of impedance spectroscopy, and the analysis, physiological meaning, and modeling of impedance data are extensively addressed in the methods section 3.4 Electric Cell-Substrate Impedance Sensing (ECIS). Briefly summarized, ECIS enables the time-resolved, label-free, and ...

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Section: Isfetmentioning

confidence: 99%

Label-free and Multi-parametric Monitoring of Cell-based Assays with Substrate-embedded Sensors

Oberleitner

2018

Springer Theses

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“…A multitude of EnFETs differing in their sensor design or gate material, enzyme-membrane composition, or immobilization method have been reported for the detection of glucose, urea, penicillin, organophosphorus pesticides, creatinine, phenolic compounds, glycoalkaloids, and so on. [28][29][30][31][32][33][34][35][36][37][38][39][40][41][42][43][44] Some recently developed EnFETs are summarized in Table 1. For an exact measurement, a pH ISFET/EnFET differential arrangement is often employed (see e.g., Refs.…”

Section: Enzyme-modified Fets (Enfet)mentioning

confidence: 99%

Chemical and Biological Field‐Effect Sensors for Liquids—A Status Report

Poghossian

Schöning

2007

Handbook of Biosensors and Biochips

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Basic concepts, functional principles, and current trends in research and development of semiconductor‐based field‐effect chemical sensors and biosensors are described. The presented sensor devices summarize the following: ISFETs (ion‐sensitive field‐effect transistor), capacitive EIS (electrolyte‐insulator‐semiconductor) sensors and LAPS (light‐addressable potentiometric sensor) structures.

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“…The C(V) measurements were based on the at band potential shi (DV FB ). The variation of DV FB obeys Nernst's law [23][24][25] and the response of the sensor was dened as the slope of the curve DV FB as a function of the ammonium ionic potential (Àlog [NH 4 + ]). 26 From this representation we determined the detection limits, the sensitivity and the linear range of the biosensor.…”

mentioning

confidence: 99%

Urease capacitive biosensors using functionalized magnetic nanoparticles for atrazine pesticide detection in environmental samples

2013

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A new atrazine pesticide potentiometric biosensor was described using urease biomolecules immobilized onto the insulator-semiconductor electrode and different additional materials such as glutaraldehyde as a cross-linking agent, bovine serum albumin, coated nanoparticles (Fe 3 O 4 ), cationic poly(allylamine hydrochloride) and anionic poly(sodium 4-styrenesulfonate) polyelectrolytes. The effect of atrazine molecules on the activity of free and immobilized urease was studied using the ion selective electrodes (ISEs) and capacity-potential measurements C(V). The sensitivity of the modified bioelectrode to urea addition was evaluated by the capacitance method via the relationship between the evolution of the flat band potential DV FB and the urea concentration for values ranging from 23 to 0.04 mM. The detection of atrazine in solution was performed via its inhibiting action on the urease biosensor. An incubation time of 30 min was chosen to study the inhibition effect of atrazine for different concentrations on the urease biosensor. Under optimal experimental conditions, the enzymatic activity, the inhibition process and the analytical characteristics of the resulting ENFEC (Enzyme Field effect capacitive) system were investigated. As a result, the detection limit of atrazine via the inhibition of urease activity was about 0.13 mM with a dynamic concentration range from 10 À2 to 10 À7 M.

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Modelling of the Potentiometric Response of ENFETs Based on Enzymatic Multilayer Membranes

Cited by 10 publications

References 18 publications

Label-free and Multi-parametric Monitoring of Cell-based Assays with Substrate-embedded Sensors

Label-free and Multi-parametric Monitoring of Cell-based Assays with Substrate-embedded Sensors

Chemical and Biological Field‐Effect Sensors for Liquids—A Status Report

Urease capacitive biosensors using functionalized magnetic nanoparticles for atrazine pesticide detection in environmental samples

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