Real-time glucose sensing by surface-enhanced Raman spectroscopy in bovine plasma facilitated by a mixed decanethiol/mercaptohexanol partition layer

A new, mixed decanethiol (DT)/mercaptohexanol (MH) partition layer with dramatically improved properties has been developed for glucose sensing by surface-enhanced Raman spectroscopy. This work represents significant progress toward our long-term goal of a minimally invasive, continuous, reusable glucose sensor. The DT/MH-functionalized surface has greater temporal stability, demonstrates rapid, reversible partitioning and departitioning, and is simpler to control compared to the tri(ethylene glycol) monolayer used previously. The data herein show that this DT/MH-functionalized surface is stable for at least 10 days in bovine plasma. Reversibility is demonstrated by exposing the sensor alternately to 0 and 100 mM aqueous glucose solutions (pH approximately 7). The difference spectra show that complete partitioning and departitioning occur. Furthermore, physiological levels of glucose in two complex media were quantified using multivariate analysis. In the first system, the sensor is exposed to a solution consisting of water with 1 mM lactate and 2.5 mM urea. The root-mean-squared error of prediction (RMSEP) is 92.17 mg/dL (5.12 mM) with 87% of the validation points falling within the A and B range of the Clarke error grid. In the second, more complex system, glucose is measured in the presence of bovine plasma. The RMSEP is 83.16 mg/dL (4.62 mM) with 85% of the validation points falling within the A and B range of the Clarke error grid. Finally, to evaluate the real-time response of the sensor, the 1/e time constant for glucose partitioning and departitioning in the bovine plasma environment was calculated. The time constant is 28 s for partitioning and 25 s for departitioning, indicating the rapid interaction between the SAM and glucose that is essential for continuous sensing.     

ENFET glucose biosensor produced with dendrimer encapsulated Pt nanoparticles

The biosensors based on ENFETs for direct glucose concentration analysis have been fabricated by introducing dendrimer encapsulated Pt nanoparticles and glucose oxidase (GOx) via a layer-by-layer self-assembly method. The free amine groups located on each poly(amidoamine) dendrimer molecule were exploited to immobilize enzyme through covalent attachment. Depending on metal nanoparticles within dendrimers and biocompatibility of dendrimers, the fabricated glucose sensitive ENFET shows obviously enhanced sensitivity and extended lifetime compared with the conventional ones. The fabricated sensor has a linear range of 0.25–2.0 mM, and a detection limit of ca. 0.15 mM. The influence of buffer concentration, ionic strength and pH was discussed. The biosensor also has good stability, which response could be used for detecting of glucose samples at intervals for at least 1 month when it stored in dry state at 4 °C.     

An electrochemical glucose sensor from an organically modified nanocomposite of viologen and TiO2

An organically modified TiO2 nanocomposite was explored for glucose detection. Bis-Butyl viologen (BBV) was mixed with TiO2 nanoparticles to generate highly dispersed nanocomposite solution, which provided organically modified nanocomposite film of TiO2 (BBV-TiO2). A transistor type sensor was fabricated using the BBV-TiO2 film and platinum gate electrode. The BBV-TiO2 nanocomposite sensor showed higher sensitivity to glucose sensing in low concentration region compared to that of TiO2 sensor. This result was ascribed to facilitated electron transport by the adsorbed viologen molecules on TiO2 nanoparticles, where viologen molecules act as an electron transfer mediator between enzyme and TiO2.     

Electrochemical study of reversible hydrogenase reaction of Desulfovibrio vulgaris cells with methyl viologen as an electron carrier.

An electrode modified with immobilized whole cells of Desulfovibrio vulgaris (Hildenborough) produces an S-shaped voltammogram with both cathodic- and anodic-catalytic-limiting currents in a methyl viologen-containing buffer saturated with H2. Methyl viologen penetrates into the bacterial cells to serve as an electron carrier in the reversible reaction of hydrogenase in the cells and functions as an electron-transfer mediator between the bacterial cells and the electrode, thus producing the catalytic currents for the evolution and consumption of H2. An equation for the catalytic current that takes into account the reversible hydrogenase reaction explains well the shape of the voltammogram. The potential at null current on the voltammogram agrees with the potential determined by potentiometry with the same electrode, which is equal to the redox potential of the H+/H2 couple in the solution--the standard potential of a hydrogen electrode at the pH of the solution. When D. vulgaris cells are suspended in an argon-saturated buffer containing methyl viologen, the suspension produces a catalytic current at a bare glassy carbon electrode for the evolution of H2. Analysis of the current by a theory for a catalytic current for a unidirectional nonlinear enzyme catalysis allows us to determine the kinetic parameters of the reaction between methyl viologen and hydrogenase in intact D. vulgaris cells. Thus we obtain the apparent Michaelis constant for methyl viologen cation radical, K'MV.+ = 0.16 mM, and the apparent catalytic constant (that is, the turnover number per D. vulgaris cell), zkcat,H+ = 1.2 x 10(7) s-1, for the H2 evolution reaction at pH 5.5 and at 25 degrees C, z being the number of hydrogenases contained in a D. vulgaris cell. The bimolecular reaction rate constant, kcat,H+/K'MV.+, of the reaction between methyl viologen cation radical and oxidized hydrogenase in intact D. vulgaris cells is estimated as 4.2 x 10(7) M-1 s-1. Similarly, the bimolecular reaction rate constant, kcat,H2/K'MV2+, of the reaction between methyl viologen and reduced hydrogenase is estimated to be 1.2 x 10(7) M-1 s-1 at pH 9.5 and 25 degrees C. Both rate constants are large enough for the reactions to be diffusion-limited processes.     

A fluorescence affinity hollow fiber sensor for continuous transdermal glucose monitoring

A novel concept of a fluorescence affinity hollow fiber sensor for transdermal glucose monitoring is demonstrated. The glucose-sensing principle is based on the competitive reversible binding of a mobile fluorophore-labeled Concanavalin A (Con A) to immobile pendant glucose moites inside of intensely colored Sephadex beads. The highly porous beads (molecular weight cutoff of 200 kDa) were colored with two red dyes, Safranin O and Pararosanilin, selected to block the excitation and spectrum of the fluorophore Alexa488. The sensor consists of the dyed beads and Alexa488-Con A confined inside a sealed, small segment of a hollow fiber dialysis membrane (diameter 0.5 mm, length 0.5 cm, molecular weight cutoff 10 kDa). In the absence of glucose, the majority of Alexa488-Con A resides inside the colored beads bound to fixed glucose. Thus, excitation light at 490 nm impinging on the sensor is strongly absorbed by the dyes, resulting in a drastically reduced fluorescence emission at 520 nm from the Alexa488-Con A residing within the beads. However, when the hollow fiber sensor is exposed to glucose, glucose diffuses through the membrane into the sensor chamber and competitively displaces Alexa 488-Con A molecules from the glucose residues of the Sephadex beads. Thus, Alexa 488-Con A appears in the void space outside of the beads and is fully exposed to the excitation light, and a strong increase in fluorescence emission at 520 nm is measured. At a medium to high loading degree of Sephadex with Alexa488-Con A (10 mg mL(-1) bead suspension), the absolute fluorescence increase due to 20 mM glucose was very large. It exceeded the response of other sensor devices based on FRET by a factor of 50 (Meadows and Schultz Anal. Chim. Acta 1993, 280, 21-30; Russell et al. Anal. Chem. 1999, 71, 3126-3132). The new sensor featured a glucose detection range extending from 0.15 to 100 mM, exhibiting the strongest dynamic signal change from 0.2 to 30 mM. It showed a reasonably fast response time (4-5 min). The combination of all the beneficial sensor features makes this sensor extremely attractive for future in vivo implantation studies for glucose monitoring in subdermal tissue.     

Affinity-based turbidity sensor for glucose monitoring by optical coherence tomography: toward the development of an implantable sensor

We investigated the feasibility of constructing an implantable optical-based sensor for seminoninvasive continuous monitoring of analytes. In this novel sensor, analyte concentration-dependent changes induced in the degree of optical turbidity of the sensing element can be accurately monitored by optical coherence tomography (OCT), an interferometric technique. To demonstrate proof-of-concept, we engineered a sensor for monitoring glucose concentration that enabled us to quantitatively monitor the glucose-specific changes induced in bulk scattering (turbidity) of the sensor. The sensor consists of a glucose-permeable membrane housing that contains a suspension of macroporous hydrogel particles and concanavalin A (ConA), a glucose-specific lectin, that are designed to alter the optical scattering of the sensor as a function of glucose concentration. The mechanism of modulation of bulk turbidity in the sensor is based on glucose-specific affinity binding of ConA to pendant glucose residues of macroporous hydrogel particles. The affinity-based modulation of the scattering coefficient was significantly enhanced by optimizing particle size, particle size distribution, and ConA concentration. Successful operation of the sensor was demonstrated under in vitro condition where excellent reversibility and stability (160 days) of prototype sensors with good overall response over the physiological glucose concentration range (2.5-20 mM) and good accuracy (standard deviation 5%) were observed. Furthermore, to assess the feasibility of using the novel sensor as one that can be implanted under skin, the sensor was covered by a 0.4 mm thick tissue phantom where it was demonstrable that the response of the sensor to 10 mM glucose change could still be measured in the presence of a layer of tissue shielding the sensor aiming to simulate in vivo condition. In summary, we have demonstrated that it is feasible to develop an affinity-based turbidity sensor that can exhibit a highly specific optical response as a function of changes in local glucose concentration and such response can be accurately monitored by OCT suggesting that the novel sensor can potentially be engineered to be used as an implantable sensor for in vivo monitoring of analytes.     

Design and in vitro studies of a needle-type glucose sensor for subcutaneous monitoring.

A new miniaturized glucose oxidase based needle-type glucose microsensor has been developed for subcutaneous glucose monitoring. The sensor is equivalent in shape and size to a 26-guage needle (0.45-mm o.d.) and can be implanted with ease without any incision. The novel configuration greatly facilitates the deposition of enzyme and polymer films so that sensors with characteristics suitable for in vivo use (upper limit of linear range greater than 15 mM, response time less than 5 min, and sensitivity yielding a 5:1 signal-to-background ratio at normal basal glucose levels) can be prepared in high yield (greater than 60%). The sensor response is largely independent of oxygen tension in the normal physiological range. It also exhibits good selectivity against common interferences except for the exogenous drug acetaminophen.     

A novel non-enzymatic glucose sensor based on nickel (II) oxide electrospun nanofibers

A new enzymeless glucose sensor has been fabricated via electrospinning technology and subsequent calcination. The morphology and structure of the as-prepared nanofibers have been characterized by scanning electron microscopy (SEM), transmission electron microscopy (TEM), and X-ray diffraction (XRD). The electrocatalytic oxidation of glucose in alkaline medium at nickel oxide modified glassy carbon electrodes has been investigated. The modified electrodes offer excellent electrocatalytic activity toward the glucose oxidation at low positive potential (0.3 V). Glucose has been determined chronoamperometrically at the surface of NiO nanofibers modified electrode in 0.5 mM NaOH. Under the optimized condition, the calibration curve is linear in the concentration range of 2 x 10(-3) mM - 1 mM, and 1 mM - 9.5 mM. The detection limit (signal-to-noise 3) and response time are 3.394 x 10(-6) M and 2 s, respectively. The NiO electrospun nanofibers is easy to prepare and feasible in economy. The modified electrode is steady and can be used repeatedly, so it is reasonable to expect its broad use in non-enzymatic glucose sensor.     

Novel sucrose three-enzyme conductometric biosensor

For the first time a conductometric biosensor for sucrose determination has been developed using a complex three-enzyme (invertase, mutarotase, and glucose oxidase) containing membrane as a sensitive element immobilized on the conductometric interdigitated planar electrodes. The time of measurement of sucrose concentration in the solution was about 1–2 min. The dynamic range of biosensor depends on buffer capacity, being 2 μM–5 mM of sucrose in 5 mM phosphate buffer. The conductometric biosensor developed demonstrates high selectivity, operational stability and reproducibility. The dependence of sensor response on pH and ionic strength of tested solution has been studied in this work. Storage conditions have also been under investigation. The sensor appeared to be eligible towards application in practice.     

Oxygen optrode for use in a fiber-optic glucose biosensor

An optical fiber oxygen sensor, based on the dynamic quenching of the luminescence of tris(1,10-phenanthroline)-ruthenium(II) cation by molecular oxygen, is presented. The complex is adsorbed onto silica gel, incorporated in a silicone matrix possessing a high oxygen permeability, and placed at the tip of the optical fiber. Oxygen has been monitored continuously in the 0-750 Torr range, with the detection limit being as low as 0.7 Torr. The device has been applied to the development of a fast responding and highly sensitive fiber-optic glucose biosensor based on this highly sensitive oxygen transducer. The sensor relates oxygen consumption (as a result of enzymatic oxidation) to glucose concentration. The enzyme is immobilized on the surface of the oxygen optrode; carbon black is used as an optical isolation in order to prevent ambient light and sample fluorescence to interfere. Measurements have been performed in a flow-through cell in air-equilibrated glucose standard solutions of pH 7.0. The effects of enzyme immobilization procedures (including enzyme immobilization on carbon black) as to response times (around 6 min), analytical ranges (0.06-1 mM glucose), reproducibility in sensor construction, and long-term stability have been studied as well.     

Amperometric glucose biosensor based on assisted ion transfer through gel-supported microinterfaces

A novel amperometric glucose sensor was developed based on the facilitated proton transfer across microinterfaces between two immiscible electrolyte solutions. The combination of a 1,3:2,4-dibenzylidene sorbitol/2-nitrophenyl octyl ether gel membrane and 3-(2-pyridyl)-5,6-diphenyl-1,2,4-triazine as the ionophore allows the transfer of protons from water to the gellified organic phase; the gel membrane is supported on arrays of microholes drilled on a polyester film. The protons are generated as the result of the dissociation of gluconic acid produced during the enzymatic degradation of glucose by glucose oxidase. The characteristics of the glucose sensor were investigated using several experimental conditions, namely, the concentration of ligand and enzyme. The electrochemical response is typical of an enzymatic electrode and displays a linear behavior in the range 0.2-3 mM glucose. The effect of the experimental parameters of the voltammetric technique was also optimized with the aim of improving sensor sensitivity.     

Preparation of porous titania sol-gel matrix for immobilization of horseradish peroxidase by a vapor deposition method

A new and facile vapor deposition method has been developed for the preparation of sol-gel matrix. This method was used to form a titania sol-gel thin film and to immobilize horseradish peroxidase (HRP) on a glassy carbon electrode surface for the production of an amperometric hydrogen peroxide biosensor. This process prevented the cracking of conventional sol-gel-derived glasses. The morphologies of both titania sol-gel and the enzyme membranes were characterized using scanning electron microscopy and proved to be chemically clean, porous, and homogeneous and to have a very narrow particle size distribution. The sol-gel-derived titania-modified electrode retained the enzyme bioactivity and provided for long-term stability of the enzyme in storage. In the presence of catechol as a mediator, the sensor exhibited a rapid electrocatalytic response (less than 5 s), a linear calibration range from 0.08 to 0.56 mM with a detection limit of 1.5 microM and a high sensitivity (61.5 microA mM(-1)) for monitoring of H2O2. Effects of pH and operating potential were also explored for optimum analytical performance by using the amperometric method. The apparent Michaelis-Menten constant of the encapsulated HRP was 1.89 +/- 0.21 mM.     

Microtubule sensors and sensor array based on polyaniline synthesized in the presence of poly(styrene sulfonate)

Microtubule sensors for glucose, urea, and triglyceride were fabricated based on poly(styrene sulfonate)-polyaniline (PSS-PANI) composites synthesized within the pores of track-etched polycarbonate membranes. The synthesis of a sufficiently thick and conducting PSS-PANI film at pH 5 provided the advantage of immobilizing enzymes during polymerization. This resulted in the improvement of sensor response for urea and triglyceride by a factor of approximately 10(2) with a significant increase in the linear region of response compared to polyaniline-based sensors, where the enzymes were immobilized by physical adsorption after the polymerization. The sensors based on urea and triglyceride were found to have a higher linear range of response, better sensitivity, improved multiple use capability, and faster response time compared to the potentiometric and amperometric sensors based on polyaniline. A microtubule sensor array for glucose, urea, and triglyceride based on PSS-PANI was fabricated by immobilization of three different sets of enzymes on three closely spaced devices and its response was found to be free from cross-interference when a sample containing a mixture of the above analytes was analyzed in a single measurement.     

Amperometric detection of histamine with a methylamine dehydrogenase polypyrrole-based sensor

Methylamine dehydrogenase (MADH) has been immobilized in a polpyrrole (PPy) film on an electrode surface and used as an amine sensor for the determination of primary amines. Its response to histamine has been characterized in detail. The PPy film containing MADH was formed electrochemically on a gold minielectrode (1-mm diameter) in the presence of ferricyanide. The film was then coated with Nafion. This enzyme electrode did not require any additional cofactors and was not sensitive to oxygen. It exhibited a maximum response current to histamine at applied potentials of 0.24-0.33 V and at pH 7.5-8.5. This MADH-PPy sensor exhibited a response time of less than 3 s. The immobilized MADH on the electrode exhibited Michaelis-Menten behavior similar to that of the free enzyme in solution with a Km value of 1.3 mM. This sensor could be used to reliably detect histamine over a concentration range from approximately 25 microM to 4 mM. This is the first example of a biosensor that uses an immobilized enzyme that possesses the tryptophan tryptophylquinone prosthetic group.     

Platinum nanoparticle modified polyaniline-functionalized boron nitride nanotubes for amperometric glucose enzyme biosensor

A novel amperometric biosensor based on the BNNTs-Pani-Pt hybrids with Pt nanoparticle homogeneously decorated on polyaniline (Pani)-wrapped boron nitride nanotubes (BNNTs), was developed. It is shown that π interactions take place between BNNTs and polyaniline (Pani) located at N atoms from BNNTs and C atoms from Pani, resulting in the water solubility for the Pani wrapped BNNTs hybrids. The developed glucose biosensor displayed high sensitivity and stability, good reproducibility, anti-interference ability, especially excellent acid stability and heat resistance. The resulted BNNTs-Pani-Pt hybrid amperometric glucose biosensor exhibited a fast response time (within 3 s) and a linear calibration range from 0.01 to 5.5 mM with a high sensitivity and low detection limit of 19.02 mA M(-1) cm(-2) and 0.18 μM glucose (S/N = 3). Surprisedly, the relative activity of the GC/BNNTs-Pani-Pt-GOD electrode keeps almost no change in a range from pH 3 to 7. Futhermore, the BNNTs-Pani-Pt hybrid biosensor maintains a high GOD enzymatic activity even at a relatively high temperature of 60 °C. This might be attributed to the effect of electrostatic field and hydrophobia of BNNTs. The unique acid stability and heat resistance of this sensor indicate great promising application in numerous industrial and biotechnological operations involving harsh conditions.     

Au@BSA prepared under alkaline conditions as an electrochemical non-enzymatic glucose sensor interface

Au@BSA was prepared at pH 8, pH 9, pH 10, pH 11, pH 11.4, and pH 12 as the working electrode of the non-enzymatic glucose sensor by biological template method. The six kinds of gold-cluster film working electrodes sintered by Au@BSA show golden color, especially the golden films corresponding to pH 8 and pH 12 are obvious. The gold-cluster films at pH 8, pH 9, pH 10, and pH 11 showed mono-layer gold nanoparticles, while the gold-cluster film at pH 11.4 showed porous structure. The gold-cluster film prepared at pH 12 presents a multi-layer 3D structure composed of a large number of gold nanoparticles. The linear detection range of the non-enzymatic glucose sensor prepared at pH 8 is the widest among the six sensors, and its sensitivity is also better than the other four sensors except the sensor prepared at pH 12. The sensor with the gold-cluster film-modified working electrode prepared at pH 12 show the highest sensitivity (330.002 μA mM^?1 cm^?2), because multi-layer 3D structure can bring more electric catalytic active site for this sensor. The electrochemical impedance spectroscopy showed that the specific surface area of the sensor prepared at pH 12 was much larger than that of the other five sensors. We provide a pH cycling method for once shaping preparation that can be extended to other metal films or metal-oxide films electrochemical interfaces. The Au@BSA non-enzymatic glucose sensor prepared in this paper is stable and can resist the toxicity of excessive chloride ions without losing activity.

     

3,3',5,5'-tetramethyl-N-(9-anthrylmethyl)benzidine: a dual-signaling fluorescent reagent for optical sensing of aliphatic aldehydes

A new optical chemical sensor for continuous monitoring of aliphatic aldehydes has been proposed based on the reversible chemical reaction between a new sensing reagent, 3,3',5,5'-tetramethyl-N-(9-anthrylmethyl)benzidine (TMAB), and the analytes. TMAB, containing two receptors and two fluorescent reporters, can perform dual fluorescence responses corresponding to the reactions of hydrogen ion and carbonyl compound. When immobilized in a plasticized poly(vinyl chloride) membrane, TMAB extracts aliphatic aldehydes from aqueous solution into the bulk membrane phase and reacts with the analyte by forming a Schiff base. Since the extraction equilibrium and chemical reaction are accompanied by fluorescence increase of the sensing membrane, the chemical recognition process could be directly translated into an optical signal. At pH 3.20, the sensor exhibits a dynamic detection range from 0.017 to 4.2 mM n-butyraldehyde with a limit of detection of 0.003 mM. The forward response time (t95) of the sensor is 3-5 min, and the reverse response time is 5-7 min. The responses of the sensor toward different kinds of aldehydes and ketones depend on the lipophilicity and the reactivity of the analytes. Since the fluorescence enhancement of the sensing membrane at 296 nm/410 nm is only related to the formation of Schiff base, the measurement of aldehydes is independent of pH.     

Amperometric uric acid biosensors fabricated of various types of uricase enzymes

Preparation process of an enzyme-based bipotentiostatic amperometric uric acid sensor has been investigated. The suitability of three different Uricase (EC 1.7.3.3) enzymes (from porcine liver, Candida Utilis, Bacillus Fastidiosus) is described in this paper. The sensor fabricated of Uricase from Candida Utilis showed a linear response to uric acid in the 0-0.9 mM concentration range and the response current range was 0-3.3 /spl mu/A. The sensor fabricated of Uricase from Bacillus Fastidiosus has been saturated at 0.72 mM and the response was not linear above 0.24 mM. The response current range was 0-0.9 /spl mu/A. The sensor fabricated of Uricase from porcine liver has not given detectable electrical signal due to its very low specific activity. The substrate was prepared by screen printing on sintered alumina ceramic sheets using pastes of Au or Pd-Pt as working (W) and counter (C) and Pt-Ag as a reference (R) electrode. Galvanostatic electrocopolymerization of dodecyl sulfate doped poly-N-methyl-pyrrole (pNMPy) layer was used for enzyme immobilization. The layout of the sensor consists of four electrode surfaces (W/sub 1/, W/sub 2/, R, and C). By the bipotentiostatic technique, the two working electrodes (with and without the enzyme) are identically prepared and polarized, while the currents in the two circuits are measured simultaneously; thus, the current of the W/sub 2/-C circuit (I/sub 2/) can be substracted as a nonspecific background noise. The nonspecific oxidation of uric acid on the poly-N-methyl-pyrrole layer at 0.2 V has been demonstrated in oxygen bubbled buffer solution.     

A glucose biosensor based on surface-enhanced Raman scattering: improved partition layer, temporal stability, reversibility, and resistance to serum protein interference

This work updates the recent progress made toward fabricating a real-time, quantitative, and biocompatible glucose sensor based on surface-enhanced Raman scattering (SERS). The sensor design relies on an alkanethiolate tri(ethylene glycol) monolayer that acts as a partition layer, preconcentrating glucose near a SERS-active surface. Chemometric analysis of the captured SERS spectra demonstrates that glucose is quantitatively detected in the physiological concentration range (0-450 mg/dL, 0-25 mM). In fact, 94% of the predicted glucose concentrations fall within regions A and B of the Clarke error grid, making acceptable predictions in a clinically relevant range. The data presented herein also demonstrate that the glucose sensor provides stable SERS spectra for at least 3 days, making the SERS substrate a candidate for implantable sensing. Glucose sensor reversibility and reusability is evaluated as the sensor is alternately exposed to glucose and saline solutions; after each cycle, difference spectra reveal that the partitioning process is largely reversible. Finally, the SERS glucose sensor successfully partitions glucose even when challenged with bovine serum albumin, a serum protein mimic.     

Extended-range glucose sensor employing engineered glucose dehydrogenases

An enzyme glucose sensor with an expanded dynamic range was constructed using a novel strategy. This strategy was based on a new concept of utilizing protein-engineered enzymes with a different Michaelis constant, which allows for the expanded dynamic range. We used the engineered Escherichia coli pyrroloquinoline quinone glucose dehydrogenase (PQQGDH) of which His775 was substituted for Asp which showed an increased Km value (25-fold). We first constructed the composite colorimetric analytical system employing the wild-type PQQGDH and His775Asp and evaluated its dynamic range. The composite colorimetric analytical system was constructed and showed a wide dynamic range of 0.5-30 mM with less than +/-5% error. The composite colorimetric analytical system, an extended-range colorimetric analytical system, enabled the determination of the concentration of glucose over a 30-fold range that could not have been achieved using the single colorimetric analytical system. Furthermore, we have demonstrated the composite amperometric glucose sensor employing the combination of His775Asn and His775Asp. The extended-range glucose sensor acquired not only the expanded dynamic range (3-70 mM) that covered both dynamic ranges of the single enzyme sensors but also the narrower substrate specificity of glucose due to the inherited property of engineered enzymes.