Microcantilever-based biosensors

Moulin, A. M.; O’Shea, S. J.; Welland, Mark E.

doi:10.1016/s0304-3991(99)00145-x

Cited by 222 publications

(118 citation statements)

References 15 publications

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“…The estimation of the magnitude of threshold stress, r0, is done in several ways. The experimental data at a single temperature are generally plotted as e_ 1 n s against r in double linear scales with known values of n [41] (n = 3 for creep controlled by viscous glide processes [32], n = 5 for creep controlled by high temperature climb of dislocations (lattice diffusion) [29,42], n = 7 for creep controlled by low temperature climb (core diffusion) [43] and n = 8 for lattice diffusion controlled creep with a constant structure [44]). If the creep rate of the composite obeys Eq.…”

Section: Evaluation Of Steady State Creep Mechanismmentioning

confidence: 99%

Impression creep behaviour of magnesium alloy-based hybrid composites in the longitudinal direction

Mondal

Kumar

2008

Composites Science and Technology

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Section: Evaluation Of Steady State Creep Mechanismmentioning

confidence: 99%

Impression creep behaviour of magnesium alloy-based hybrid composites in the longitudinal direction

Mondal

Kumar

2008

Composites Science and Technology

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“…Single microcantilevers are generally known to be susceptible to spurious deflections because of temperature changes, chemical interaction of a coated cantilever with the liquid environment, and slow rearrangement of molecules in the protein multilayer (10,12,26,27). As a result, a base-line drift can be observed during static-mode measurements.…”

Section: Resultsmentioning

confidence: 99%

A label-free immunosensor array using single-chain antibody fragments

Backmann

Zahnd

Huber

et al. 2005

Proc. Natl. Acad. Sci. U.S.A.

264

183

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We report a microcantilever-based immunosensor operated in static deflection mode with a performance comparable with surface plasmon resonance, using single-chain Fv (scFv) antibody fragments as receptor molecules. As a model system scFv fragments with specificity to two different antigens were applied. We introduced a cysteine residue at the C terminus of each scFv construct to allow covalent attachment to gold-coated sensor interfaces in directed orientation. Application of an array enabled simultaneous deflection measurements of sensing and reference cantilevers. The differential deflection signal revealed specific antigen binding and was proportional to the antigen concentration in solution. Using small, oriented scFv fragments as receptor molecules we increased the sensitivity of microcantilevers to Ϸ1 nM.cantilever arrays ͉ nanomechanics ͉ proteomics M icrocantilever-based sensors have attracted much interest as devices for fast and reliable detection of small amounts of molecules in air and solution. Over the last few years the application of the cantilever sensor concept was extended to the measurements of biocompounds in solution, resulting in a versatile biosensor (1, 2). Because of its label-free detection principle and small size, this kind of biosensor is advantageous for diagnostic applications, disease monitoring, and research in genomics or proteomics (3, 4). Multicantilever arrays would enable the detection of several analytes simultaneously.The main principle of the cantilever static mode is the transduction of the molecular interaction between analyte and receptors, immobilized as a layer on one surface of a cantilever, into a nanomechanical motion of the cantilever. Biomolecular interactions taking place on a solid-state interface produce a change in surface stress, because of changes in molecular configuration and intermolecular crowding (5). This process results in bending of the cantilever. Microcantilever-based biosensors operated in static mode have been successfully applied for the detection of various molecular interactions such as ssDNA-ssDNA (5-7) or protein-DNA (8, 9). Interactions between proteins were detected with cantilever-based immunosensors, where an antigen was recognized by its cognate antibody randomly immobilized on the sensor surface (10-12).The most critical step in preparation of any immunosensor is the immobilization of capture molecules on the support, a process where the orientation of the antigen-binding sites toward the analyte in solution plays a key role. Immunoglobulins can be either adsorbed on gold directly (10, 12) or attached covalently to the surface modified with hetero-bifunctional self-assembled monolayers of alkylthiols (11). However, these approaches produce a layer of randomly oriented antibody molecules on the cantilever surface, thereby generating conformational heterogeneity and inactive receptor molecules (13,14).As previously shown (13,(15)(16)(17)(18), the sensitivity of immunosensors can be improved by both maximizing the degree of functional ...

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“…When antibodies or small DNA fragments were immobilized on one side of a cantilever, the presence of complementary biological species produced cantilever deflections in a rather predictable manner (9,(15)(16)(17). On the basis of the deflection behavior of MCs modified with biological receptors, even very small mismatches in receptor-analyte complementarity could be detected.…”

Section: Applicationsmentioning

confidence: 91%

“…An increasing number of recent reports confirms the potential of MC sensors for environmental and biomedical applications, and the multifaceted functionality of MCs indicates their uniqueness as compared with more traditional sensor designs (7)(8)(9)(10)(11)(12)(13)(14)(15)(16)(17).…”

mentioning

confidence: 99%