Insulin-stimulated glucose uptake and fasting blood glucose.

Changes in insulin-stimulated glucose metabolism were studied in young and aged subjects, subjects with impaired glucose tolerance, and patients with NIDDM by means of the glucose clamp technique. The diabetic group includes obese and non-obese patients treated without insulin and non-obese patients treated with insulin. The glucose disposal rate (GDR) was decreased in aged subjects (5.8 +/- 0.4 mg/kg/min) compared with young controls (7.4 +/- 0.3 mg/kg/min). In patients with IGT, it was further decreased to 3.6 +/- 0.5 mg/kg/min, which was comparable to the rate in NIDDM without insulin treatment (3.3 +/- 0.4 mg/kg/min). There were no differences in the GDR between obese (3.0 +/- 0.3 mg/kg/min) and non-obese (3.4 +/- 0.6 mg/kg/min) diabetic patients. In insulin-treated diabetic patients, GDR ranged widely, but the mean value was partially normalized (5.2 +/- 0.9 mg/kg/min). In the diabetic group, no correlation was observed between fasting blood glucose and GDR. These results suggest that in the course of developing NIDDM, a decrease in insulin-stimulated glucose uptake precedes a rise in fasting blood glucose. Thus, as previously reported for Caucasian NIDDM patients, resistance to insulin-stimulated glucose uptake may be one of the basic defects in Japanese patients with NIDDM. The degree of glycemia, however, is not directly related to the magnitude of the defect in insulin action.     

Novel FAD-dependent glucose dehydrogenase for a dioxygen-insensitive glucose biosensor

A novel FAD-dependent glucose dehydrogenase (FAD-GDH) was found and its enzymatic property for glucose sensing was characterized. FAD-GDH oxidized glucose in the presence of some artificial electron acceptors, except for O2, and exhibited thermostability, high substrate specificity and a large Michaelis constant for glucose. FAD-GDH was applied to an amperometric glucose sensor with Fe(CN)6(3-) as a soluble mediator. The use of a relatively high concentration of Fe(CN)6(3-) resulted in a good linearity between the current response and the glucose concentration, taking into account a large Michaelis constant for Fe(CN)6(3-). The glucose sensor was completely insensitive to O2 and responded linearly to glucose up to 30 mM. Compared to glucose, the response to other saccharides was negligible. The sensor can be stored at room temperature in a desiccator for at least one month without any change in the response or activity.     

Novel optical solid-state glucose sensor using immobilized glucose oxidase

Meso-tetra(4-carboxyphenyl)porphine (CTPP(4)) binds reversibly to immobilized glucose oxidase (GOD), resulting in an absorbance peak for the CTPP(4)-GOD complex at 427nm. The absorbance intensity of the 427nm peak is reduced upon exposure to glucose, which causes the dissociation of CTPP(4) from GOD. The change in absorbance at 427nm shows linear dependence on glucose concentration from 20 to 200mg/dL (1.1-11.1mM).     

Fermentation glucose assay using the Exactech blood glucose biosensor

Summary The Exactech blood glucose biosensor has been used successfully to measure glucose concentrations in fermentation broths. A highly sensitive linear calibration was obtained between the glucose concentration and the biosensor reading, which correlated well with a Reducing Sugar Assay.     

Interstitial fluid glucose time-lag correction for real-time continuous glucose monitoring

Time lag between subcutaneous interstitial fluid and plasma glucose decreases the accuracy of real-time continuous glucose monitors. However, inverse filters can be designed to correct time lag and attenuate noise enabling the blood–glucose profile to be reconstructed in real time from continuous measurements of the interstitial-fluid glucose. We designed and tested a Wiener filter using a set of 20 sensor-glucose tracings (～30 h each) with a 1-min sample interval. Delays of 10 ± 2 min (mean ± SD) were introduced into each signal with additive Gaussian white noise (SNR = 40 dB). Performance of the filter was compared to conventional causal and non-causal seventh-order finite-impulse response (FIR) filters. Time lags introduced an error of 5.3 ± 2.7%. The error increased in the presence of noise (to 5.7 ± 2.6%) and attempts to remove the noise with conventional low-pass filtering increased the error still further (to 7.0 ± 3.5%). In contrast, the Wiener filter decreased the error attributed to time delay by ～50% in the presence of noise (from 5.7% to 2.60 ± 1.26%) and by ～75% in the absence of noise (5.3% to 1.3 ± 1%). Introducing time-lag correction without increasing sensitivity to noise can increase CGM accuracy.     

On-line control of glucose concentration using an automatic glucose analyzer

The fundamental characteristics of an automatic glucose analyzer which consists of sampling, sensor, and operation units were examined. The glucose sensor is a dual cathode type which has an immobilized glucose oxidase membrane coupled with an oxygen sensor. Using this glucose sensor combined with an automatic sampling device, on-off control of the glucose concentration in fed-batch cultures of Saccharomyces cerevisiae was carried out. When the glucose concentration to be controlled was set at 0.3 and 10 g/l, the concentration was well maintained within the range of 0.08−0.54 g/l in the former, and within 9.2–11.1 g/l in the latter. In the former experiment, 1.67 g/l of ethanol was produced at the end of cultivation (OD₅₇₀=34). On the other hand, 12.9 g/l of ethanol was accumulated at the end of cultivation (OD₅₇₀=43) in the latter experiment. Fed-batch cultures of Micrococcus ruteus were also carried out. The glucose concentration was set at 2.5 g/l. The microorganism grew up to OD₆₁₀=264 and the glucose concentration was maintained within 2.0 and 3.1 g/l.     

Holographic glucose sensors

A novel holographic sensor system capable of detecting dynamic changes in glucose concentration has been developed. The hologram is recorded within a bio-compatible hydrogel matrix containing phenylboronic acid derivatives. On binding glucose, the colour of the hologram red-shifts to longer wavelengths as the hydrogel expands and this colour change is used to quantify glucose concentration. However, phenylboronic acids are non-selective and bind a wide variety of cis-diols. In blood, glucose is the only sugar found free at high concentration, whilst other sugars are typically found as part of glycoproteins and macromolecular structures. Although glycoproteins have been shown to have no effect on the sensor, phenylboronic acids can bind lactate much more readily than glucose. We have designed two polymer hydrogel systems to increase the selectivity of the sensor for glucose over lactate. The first involved the use of high concentrations of 3-acrylamidophenylboronic acid (3-APB) whilst the second system utilised 2-acrylamido-5-fluorophenylboronic acid (5-F-2-MAPB). Both systems displayed an increased selectivity to glucose over lactate at physiological pH and ionic strength and could be deployed as selective holographic sensors for glucose detection in physiological fluids.     

High glucose concentrations inhibit glucose phosphorylation, but not glucose transport, in human endothelial cells.

Glucose uptake is autoregulated in a variety of cell types and it is thought that glucose transport is the major step that is subjected to control by sugar availability. Here, we examined the effect of high glucose concentrations on the rate of glucose uptake by human ECV-304 umbilical vein-derived endothelial cells. A rise in the glucose concentration in the medium led a dose-dependent decrease in the rate of 2-deoxyglucose uptake. The effect of high glucose was independent of protein synthesis and the time-course analysis indicated that it was relatively slow. The effect was not due to inhibition of glucose transport since neither the expression nor the subcellular distribution of the major glucose transporter GLUT1, nor the rate of 3-O-methylglucose uptake was affected. The total in vitro assayed hexokinase activity and the expression of hexokinase-I were similar in cells treated or not with high concentrations of glucose. In contrast, exposure of cells to a high glucose concentration caused a marked decrease in phosphorylated 2-deoxyglucose/free 2-deoxyglucose ratio. This suggests the existence of alterations in the rate of in vivo glucose phosphorylation in response to high glucose. In summary, we conclude that ECV304 human endothelial cells reduce glucose utilization in response to enhanced levels of glucose in the medium by inhibiting the rate of glucose phosphorylation, rather than by blocking glucose transport. This suggests a novel metabolic effect of high glucose on cellular glucose utilization.     

Nanogold-plasmon-resonance-based glucose sensing

Noble metal nanoparticles are well known for their strong interactions with light through the resonant excitations of the collective oscillations of the conduction electrons on the particles, the so-called surface plasmon resonances. The close proximity of two nanoparticles is known to result in a red-shifted resonance wavelength peak, due to near-field coupling. We have subsequently employed this phenomenon and developed a new approach to glucose sensing, which is based on the aggregation and disassociation of 20-nm gold particles and the changes in plasmon absorption induced by the presence of glucose. High-molecular-weight dextran-coated nanoparticles are aggregated with concanavalin A (Con A), which results in a significant shift and broadening of the gold plasmon absorption. The addition of glucose competitively binds to Con A, reducing gold nanoparticle aggregation and therefore the plasmon absorption when monitored at a near-red arbitrary wavelength. We have optimized our plasmonic-type glucose nanosensors with regard to particle stability, pH effects, the dynamic range for glucose sensing, and the observation wavelength to be compatible with clinical glucose requirements and measurements. In addition, by modifying the amount of dextran or Con A used in nanoparticle fabrication, we can to some extent tune the glucose response range, which means that a single sensing platform could potentially be used to monitor microM --> mM glucose levels in many physiological fluids, such as tears, blood, and urine, where the glucose concentrations are significantly different.     

Fluorescence-based glucose sensors

There is an urgent need to develop technology for continuous in vivo glucose monitoring in subjects with diabetes mellitus. Problems with existing devices based on electrochemistry have encouraged alternative approaches to glucose sensing in recent years, and those based on fluorescence intensity and lifetime have special advantages, including sensitivity and the potential for non-invasive measurement when near-infrared light is used. Several receptors have been employed to detect glucose in fluorescence sensors, and these include the lectin concanavalin A (Con A), enzymes such as glucose oxidase, glucose dehydrogenase and hexokinase/glucokinase, bacterial glucose-binding protein, and boronic acid derivatives (which bind the diols of sugars). Techniques include measuring changes in fluorescence resonance energy transfer (FRET) between a fluorescent donor and an acceptor either within a protein which undergoes glucose-induced changes in conformation or because of competitive displacement; measurement of glucose-induced changes in intrinsic fluorescence of enzymes (e.g. due to tryptophan residues in hexokinase) or extrinsic fluorophores (e.g. using environmentally sensitive fluorophores to signal protein conformation). Non-invasive glucose monitoring can be accomplished by measurement of cell autofluorescence due to NAD(P)H, and fluorescent markers of mitochondrial metabolism can signal changes in extracellular glucose concentration. Here we review the principles of operation, context and current status of the various approaches to fluorescence-based glucose sensing.     

Calibration in dogs of a subcutaneous miniaturized glucose sensor using a glucose meter for blood glucose determination.

The feasibility of calibrating a glucose sensor by using a wearable glucose meter for blood glucose determination and moderate variations of blood glucose concentration was assessed. Six miniaturized glucose sensors were implanted in the subcutaneous tissue of conscious dogs, and the parameters used for the in vivo calibration of the sensor (sensitivity coefficient and extrapolated current in the absence of glucose) were determined from values of blood glucose and sensor response obtained during glucose infusion. (1) Venous plasma glucose level and venous total blood glucose level were measured simultaneously on the same sample, using a Beckman analyser and a Glucometer II, respectively. The regression between plasma glucose (x) and whole blood glucose (y) was y = 1.12x-0.08 mM (n = 114 values, r = 0.96, p = 0.0001). The error grid analysis indicated that the use of a Glucometer II for blood glucose determination was appropriate in dogs. (2) The in vivo sensitivity coefficients were 0.57 +/- 0.11 nA mM-1 when determined from plasma glucose, and 0.51 +/- 0.07 nA mM-1 when determined from whole blood glucose (t = 1.53, p = 0.18, n.s.). The background currents were 0.88 +/- 0.57 nA when determined from plasma glucose, and 0.63 +/- 0.77 nA when determined from whole blood glucose (t = 0.82, p = 0.45, n.s.). (3) The regression equation of the estimation of the subcutaneous glucose level obtained from the two methods was y = 1.04x + 0.56 mM (n = 171 values, r = 0.98, p = 0.0001).(ABSTRACT TRUNCATED AT 250 WORDS)     

Preparation of various glucose esters via lipase-catalyzed hydrolysis of glucose pentaacetate

beta-D(+)-Glucose pentaacetate was hydrolyzed both chemically and enzymatically. In contrast to the alkaline hydrolysis, esterase-catalyzed deacetylations afforded significant accumulation of intermediate glucose esters at different degrees of substrate conversion. Aspergillus niger lipase, the most suitable of the four enzymes tested, was used for preparative hydrolysis of glucose pentaacetate. As a result, gram quantities of pure glucose-2,3,4,6-tetraacetate, glucose triacetate (a mixture of two positional isomers, 2,4,6- and 3,4,6-), and glucose-4,6-diacetate were prepared.