Semiconductor nanoparticles, or quantum dots (QDs), have unique photophysical properties, such as size-controlled fluorescence, have high fluorescence quantum yields, and stability against photobleaching. These properties enable the use of QDs as optical labels for the multiplexed analysis of immunocomplexes or DNA hybridization processes. Semiconductor QDs are also used to probe biocatalytic transformations. The time-dependent replication or telomerization of nucleic acids, the oxidation of phenol derivatives by tyrosinase, or the hydrolytic cleavage of peptides by proteases are probed by using fluorescence resonance energy transfer or photoinduced electron transfer. The photoexcitation of QD-biomolecule hybrids associated with electrodes enables the photoelectrochemical transduction of biorecognition events or biocatalytic transformations. Examples are the generation of photocurrents by duplex DNA assemblies bridging CdS NPs to electrodes, and by the formation of photocurrents as a result of biocatalyzed transformations. Semiconductor nanoparticles are also used as labels for the electrochemical detection of DNA or proteins: Semiconductor NPs functionalized with nucleic acids or proteins bind to biorecognition complexes, and the subsequent dissolution of the NPs allows the voltammetric detection of the related ions, and the tracing of the recognition events.

Catalytic nucleic acids (DNAzymes or ribozymes) are selected by the systematic evolution of ligands by exponential enrichment process (SELEX). The catalytic functions of DNAzymes or ribozymes allow their use as amplifying labels for the development of optical or electronic sensors. The use of catalytic nucleic acids for amplified biosensing was accomplished by designing aptamer-DNAzyme conjugates that combine recognition units and amplifying readout units as in integrated biosensing materials. Alternatively, "DNA machines" that activate enzyme cascades and yield DNAzymes were tailored, and the systems led to the ultrasensitive detection of DNA. DNAzymes are also used as active components for constructing nanostructures such as aggregated nanoparticles and for the activation of logic gate operations that perform computing.

The selection of aptamers-nucleic acids that specifically bind low-molecular-weight substrates or proteins-by the SELEX (systematic evolution of ligands by exponential enrichment) procedure has attracted recent efforts directed to the development of new specific recognition units. In particular, extensive activities have been directed to the application of aptamers as versatile materials for the design of biosensors. The Minireview summarizes the recent accomplishments in developing electronic aptamer-based sensors (aptasensors), which include electrochemical, field-effect transistor, and microgravimetric quartz crystal microbalance sensors, and describes methods to develop amplified aptasensor devices and label-free aptasensors.

The H(2)O(2)-mediated enlargement of Au nanoparticles (NPs) and the growth mechanism are described. In addition to the deposition of gold on the NP faces, the formation of nanocrystalline clusters at the intersection of the faces is observed. The detachment of the latter nanoclusters provides additional seeds for the deposition of gold. The biocatalyzed generation of H(2)O(2) in the presence of O(2)/glucose and glucose oxidase enabled the development of an optical biosensor for glucose.

The neurotransmitters dopamine (1), L-DOPA (2), adrenaline (3), and noradrenaline (4) mediate the generation and growth of Au nanoparticles (Au-NPs). The plasmon absorbance of the Au-NPs allows the quantitative colorimetric detection of the neurotransmitters. Neurotransmitters 1, 2, and 4 are sensed with a detection limit of 2.5 x 10(-6) M, whereas the detection limit for analyzing 3 corresponds to 2 x 10(-5) M. The neurotransmitter-mediated growth of the Au-NPs is also used to probe the activity of tyrosinase. The later biocatalyst oxidizes tyrosine to L-DOPA that mediates the growth of the Au-NPs. The analysis of tyrosinase activity is important for detecting melanoma cells and Parkinson disease.

A label free, reagentless aptasensor for adenosine is developed on an ISFET device. The separation of an aptamer/nucleic acid duplex by adenosine leads to the aptamer/adenosine complex that alters the gate potential of the ISFET. The sensitivity limit of the device is 5 x 10-5 M. Also, the immobilization of the aptamer/nucleic acid duplex on an Au-electrode and the separation of the duplex by adenosine mono-phosphate (AMP) enable the electrochemical detection of adenosine by faradaic impedance spectroscopy. The separation of the aptamer/nucleic acid duplex by adenosine and the formation of the aptamer/adenosine complex results in a decrease in the interfacial electron-transfer resistance in the presence of [Fe(CN)6]3-/4- as redox active substrate.

Precipitation of an insoluble, insulating product on monolayer-functionalized electrodes enables the development of new electrochemical biosensors. Faradaic impedance spectroscopy and cyclic voltammetry are used to probe the electron-transfer resistance at the conductive support upon the accumulation of the insoluble product on the electrode surface. Similarly, microgravimetric quartz crystal microbalance, QCM, analyses were used to assay the formation of the precipitate on the electrode. A horseradish peroxidase, HRP, monolayer electrode is used to analyze H2O2 via the biocatalyzed oxidation of 4-chloro-1-naphthol (1) and the precipitation of the insoluble product (2). A bienzyme-layered electrode consisting of HRP and glucose oxidase, GOx, is used to sense glucose. Biocatalyzed oxidation of glucose by O2, in the presence of GOx, yields H2O2, and the generated hydrogen peroxide effects the formation of the insoluble product (2) in the presence of HRP. The insoluble product accumulated on the electrode, and the extent of the resulting electron-transfer resistance, correlated with the amounts of H2O2 or glucose, and appropriate calibration curves are extracted.

The preparation of integrated, electrically contacted, flavoenzyme and NAD(P) + -dependent enzyme-electrodes is described. The reconstitution of apo-glucose oxidase, apo-GOx, on a FAD cofactor linked to a pyrroloquinoline quinone (PQQ) phenylboronic acid monolayer yields an electrically contacted enzyme monolayer (surface coverage 2.1 × 10 -12 mol cm -2 ) exhibiting a turnover rate of 700 s -1 (at 22 ( 2 °C). The system is characterized by microgravimetric quartz-crystal microbalance analyses, Faradaic impedance spectroscopy, rotating disk electrode experiments, and cyclic voltammetry. The performance of the enzyme-electrode for glucose sensing is described. Similarly, the electrically contacted enzymeelectrodes of NAD(P) + -dependent enzymes malate dehydrogenase, MalD, and lactate dehydrogenase, LDH, are prepared by the cross-linking of affinity complexes generated between the enzymes and the NADP + and NAD + cofactors linked to a pyrroloquinoline quinone phenylboronic acid monolayer, respectively. The MalD enzyme-electrode (surface coverage 1.2 × 10 -12 mol cm -2 ) exhibits a turnover rate of 190 s -1 , whereas the LDH enzyme-electrode (surface coverage 7.0 × 10 -12 mol cm -2 ) reveals a turnover rate of 2.5 s -1 . Chronoamperometric experiments reveal that the NAD + cofactor is linked to the PQQ-phenylboronic acid by two different binding modes. The integration of the LDH with the two NAD + cofactor configurations yields enzyme assemblies differing by 1 order of magnitude in their bioelectrocatalytic activities.