Immobilization for sensor applications

Table I. Example of Immobilization for Sensor Applications (cont)... 

Stabilization of activated oxidoreductases on time scales of months to years has historically been challenging, and the lack of success in this regard has limited the industrial implementation of redox enzymes to applications that do not require long lifetimes. However, as mentioned in the Introduction, some possibility of improved stability has arisen from immobilization of enzymes in hydrophilic cages formed by silica sol—gels and aerogels, primarily for sensor applications.The tradeoff of this approach is expected to be a lowering of current density because... 

The fractional power in the cladding increases with mode number and capillary length. Thus, for sensor application, excitation of higher-order leaky modes leads to direct illumination of the immobilized fluorophores on the surface. 

For example, Zhang and Cass have also immobilized alkaline phosphatase on a nanoporous nickel-titanium film for sensor applications. 

The initial hurdle to overcome in the biosensor application of a nucleic acid is that involving its stable attachment on a transducing element which commonly includes a metallic electrode. In the first part of this chapter, we wish to introduce our approach for DNA immobilization (Scheme 1). A detailed characterization of the immobilization chemistry is also presented. In the second part, we follow the development of work from our laboratory on chemical sensor applications of the DNA-modified electrode involving a biosensor for DNA-binding molecules and an electrochemical gene sensor. 

Chapter 20 includes an extensive review of the CL sensors for determination of analytes in air, vapors, or liquids using different immobilization modes, its application to different analytes, based on enzyme or nonenzyme reactions, as well as CL immunosensors and DNA sensors. 

Immobilizing the catalyst on the electrode surface is useful for both synthetic and sensors applications. Monomolecular coatings do not allow redox catalysis, but multilayered coatings do. The catalytic responses are then functions of three main factors in addition to transport of the reactant from the bulk of the solution to the film surface transport of electrons through the film, transport of the reactant in the reverse direction, and catalytic reaction. The interplay of these factors is described with the help of characteristic currents and kinetic zone diagrams. In several systems the mediator plays the role of an electron shuttle and of a catalyst. More interesting are the systems in which the two roles are assigned to two different molecules chosen to fulfill these two different functions, as illustrated by a typical experimental example. 

This type of sensor was adapted for biochemical applications by using an en2ymatic catalyst (an oxidase) immobilized on CPG and positioned prior to the detector, as shown in Fig. 3.34.C [242]. 

In 1985, Ruzicka and Hansen established the principles behind flow injection optosensing [13-15], which has subsequently been used for making reaction-rate measurements [16], pH measurements by means of immobilized indicators [17,18], enzyme assays [19], solid-phase analyte preconcentration by sorbent extraction [20] and even anion determinations by catalysed reduction of a solid phase [21] —all these applications are discussed in Chapters 3 and 4. Incorporation of a gas-diffusion membrane in this type of sensor results in substantially improved sensitivity (through preconcentration) and selectivity (through removal of non-volatile interferents). The first model sensor of this type was developed for the determination of ammonium [13] and later refined by Hansen et al. [22,23] for successful application to clinical samples. 

Stability, duration, sensitivity, interference, and availability of substrates to contact enzymes are the criteria for the success of an enzyme sensor. These criteria depend on sources of enzymes, immobilization techniques, and transducers used. Food matrices are much more complicated than the clinical samples, hence, these criteria become extremely important for the application of the enzyme sensor in food analysis. An extensive list of the response time, detection limits, and stability of biosensors was summarized by Wagner (59). 

X. Sun, P. He, S. Liu, L. Ye and Y. Fang, Immobilization of single-stranded deoxyribonucleic acid on gold electrode with self-assembled aminoethanethiol monolayer for DNA electrochemical sensor applications, Talanta, 47 (1998) 487-495. 

Lemmon, T.L., J.C. Westall, and J.D. Ingle, Jr. 1996. Development of redox sensors for environmental applications based on immobilized redox indicators. Anal. Chem. 68, 947-953. 

Demas and DeGraff reported the design of highly luminescent transition metal complexes for optical oxygen sensor applications [16]. Table 2 shows the photochemical and photophysical properties of sensing probes using luminescent transition metal complexes in immobilizing polymer films. 

In recent years the electrochemistry of the enzyme membrane has been a subject of great interest due to its significance in both theories and practical applications to biosensors (i-5). Since the enzyme electrode was first proposed and prepared by Clark et al. (6) and Updike et al. (7), enzyme-based biosensors have become a widely interested research field. Research efforts have been directed toward improved designs of the electrode and the necessary membrane materials required for the proper operation of sensors. Different methods have been developed for immobilizing the enzyme on the electrode surface, such as covalent and adsorptive couplings (8-12) of the enzymes to the electrode surface, entrapment of the enzymes in the carbon paste mixture (13 etc. The entrapment of the enzyme into a conducting polymer has become an attractive method (14-22) because of the conducting nature of the polymer matrix and of the easy preparation procedure of the enzyme electrode. The entrapment of enzymes in the polypyrrole film provides a simple way of enzyme immobilization for the construction of a biosensor. It is known that the PPy-... 

Nanoparticles consisting of noble metals have recently attracted much attention because such particles exhibit properties differing strongly from the properties of the bulk metal [1,2], Thus, such nanoparticles are interesting for their application as catalysts [3-5], sensors [6, 7], and in electronics. However, the metallic nanoparticles must be stabilized in solution to prevent aggregation. In principle, suitable carrier systems, such as microgels [8-11], dendrimers [12, 13], block copolymer micelles [14], and latex particles [15, 16], may be used as a nanoreactors in which the metal nanoparticles can be immobilized and used for the purpose at hand. 

The novel water-soluble dye 64 shows sufficient stability for potential application in molecular-based beacons for cancer detection using optical imaging <2005BCC735>. An optochemical ozone sensor with a quantitation limit of 0.03 ppm and accuracy exceeding 8% has been obtained by immobilization of the novel soluble indigo derivative 65 in permeable transparent polymeric films of polydimethylsiloxane-polycarbonate <2005MI1628>. 

For AW sensor applications, grains of porous powders must be immobilized by some form of thin-film physical support layer on the device surface. This requirement is nontrivial, as it is a complex problem to create a uniform, well-bound layer of tiny, porous particles that is effectively glued to a flat surface without plugging the pores with the glue used for attachment. One class of materials that has been studied as a means to immobilize high-surface-area ains... 

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