Biotransducer

Electrochemical biosensors contain a biorecognition element that selectively reacts with the target analyte and produces an electrical signal that is proportional to the analyte concentration. In general, there are several approaches that can be used to detect electrochemical changes during a biorecognition event and these can be classified as follows: amperometric, potentiometric, impedance, and conductometric.

Optical biotransducers, used in optical biosensors for signal transduction, use photons in order to collect information about analyte.[2] These are highly sensitive, highly specific, small in size and cost effective.

The detection mechanism of optical biotransducer depends upon the enzyme system that converts analyte into products which are either oxidized or reduced at the working electrode.[3]

Evanescent field detection principle is most commonly used in an optical biosensor system as the transduction principle . This principle is one of the most sensitive detection methods. It enables the detection of fluorophores exclusively in the close proximity of the optical fiber. [4]

Electronic biosensing offers significant advantages over optical, biochemical and biophysical methods, in terms of high sensitivity and new sensing mechanisms, high spatial resolution for localized detection, facile integration with standard wafer-scale semiconductor processing and label-free, real-time detection in a nondestructive manner [6].

Devices based on field-effect transistors (FETs) have attracted great attention because they can directly translate the interactions between target biological molecules and the FET surface into readable electrical signals. In a FET, current flows along the channel which is connected to the source and the drain. The channel conductance between the source and the drain is switched on and off by gate electrode that is capacitively coupled through a thin dielectric layer [6].

In FET-based biosensors, the channel is in direct contact with the environment, and this gives better control over the surface charge. This improves the sensitivity of surface FET-based biosensors as biological events occurring at the channel surface could result in the surface potential variation of the semiconductor channel and then modulate the channel conductance. In addition to ease of on-chip integration of device arrays and the cost-effective device fabrication, the surface ultrasensitivity of FET-based biosensors makes it an attractive alternative to existing biosensor technologies[6].

Gravimetric biosensors use the basic principle of a response to a change in mass. Most gravimetric biosensors use thin piezoelectric quartz crystals, either as resonating crystals (QCM), or as bulk/surface acoustic wave (SAW) devices. In the majority of these the mass response is inversely proportional to the crystal thickness. Thin polymer films are also used in which biomolecules can be added to the surface with known surface mass. Acoustic waves can be projected to the thin film to produce an oscillatory device, which then follows an equation that is nearly identical to the Sauerbrey equation used in the QCM method.[5] Biomolecules, such as proteins or antibodies can bind and its change in mass gives a measureable signal proportional to the presence of the target analyte in the sample.

Pyroelectric biosensors generate an electric current as a result of a temperature change. This differential induces a polarization in the substance, producing a dipole moment in the direction of the temperature gradient. The result is a net voltage across the material. This net voltage can be calculated by the following equation.[6]

${\displaystyle \Delta V=\omega PAr\Delta T\left(1+\omega ^{2}\tau _{E}^{2}\right)^{-1/2}}$

${\displaystyle \tau _{E}=rC}$

where V = Voltage, ω = angular frequency of the modulated incident, P = pyroelectric coefficient, L = film thickness, ε = film dielectric constant, A = area of film, r = resistance of the film, C = capacitance of the film, τE = electrical time constant of the detector output.