The invention relates to blood glucose sensing methods and devices.
Glucose sensors are of great interest for the medical application of blood glucose sensing. Their optimization (in terms of response time, lifetime, sensitivity and selectivity) is highly necessary to improve the treatment of Diabetes Mellitus, a chronic disease affecting millions of 37 people around the world.
Most studies on this subject have involved the use of enzymes. Although enzymatic detection usually shows good selectivity and high sensitivity, the enzyme is easily denatured during its immobilization process.
Non-enzymatic glucose sensors have been studied to develop an effective enzyme-free sensor; in particular the direct electrochemical oxidation of glucose in alkaline medium was investigated at Cu, Ni, Fe, Pt and Au electrodes. Of these electrodes, platinum was the most promising, but it proved to be extremely non-selective and susceptible to poisoning by various components of blood and other physiological media over extended use.
A different approach to the subject involves performing a cyclic-voltammetric study of glucose oxidation at a gold electrode. Using this approach, the occurrence of a positive current peak was observed during the cathodic sweep, and highlighted a highly linear dependence between current value maxima and glucose concentration. The application of the method in blood glucose sensing, however, has been hindered by the presence of inhibitors; chlorides, amino acids, and human albumin were observed to inhibit the reaction. Among them, chlorides are the most problematic because of their high concentration in the blood, (about 0.1 M) and the difficulty inherent in trying to separate them from glucose.
The present invention advances the art by providing new technology for blood glucose sensing to overcome at least some of these problems.
The present invention provides a method and device for electrochemically sensing glucose from a sample containing chlorides. A first working electrode (e.g. silver) is used for removing chlorides from the sample. A second working electrode (e.g. gold) is used for absorbing glucose from the sample. A current collector electrode (e.g. platinum) is used for establishing current flow between the first and second working electrodes, while during the removal of chlorides the pH of the sample increases towards basic pH. In one example, the pH increases to about 11.5 or at least 11.5. A sensing device is used for sensing oxidative current peaks caused by the absorption of the glucose. In general, the first and second working electrodes and the current collector electrode are made from non-toxic materials to the human body.
To overcome at least some of the problem of chlorides in blood samples, the mechanism of glucose oxidation at gold electrodes was investigated. The glucose molecule is first electrochemically adsorbed at the surface of the electrode by dehydrogenation (peak I in
Chloride ions inhibit the formation of the “sensing peak” in two ways:
In the present invention, a further solution to this problem is provided which involves a three electrodes setup, and a four-steps pulsed electrochemical detection technique (see
In one example, D(+)-Glucose anhydrous, sodium chloride, potassium phosphate dibasic, potassium phosphate monobasic and silver gauze (80 mesh 0.115 mm diameter wire, 99.9% 2×2 cm) were used (e.g. from Sigma Aldrich). Gold pin electrode (Surface Area 0.0314 cm2) and platinum counter electrode were also used (e.g. from Amel Electrochemistry). The electrochemical characterization was carried out using a BioLogic VMP3 potentiostat-galvanostat multichannel equipped with EIS board, the experimental setup of the device and method has a total of four electrodes (see
Before each experiment, the gold pin electrode surface has been activated and stabilized in 0.1 M KOH by CV scans at 100 mV s-1 between −0.7 and 0.8 V vs. RE until stable voltammograms have been observed. All the measurements have been performed at room temperature under nitrogen atmosphere.
In these conditions (
After proving the efficiency of the pulsed technique at pH 11.5, the next step was to test it at pH 7.4, (blood pH), while keeping all other parameters constant.
In
Despite this, the pulsed technique has been tested in these conditions (
The following step was to test the method in the presence of 100 mM potassium chloride at pH 7.4 buffered with 50 mM K2HPO4/144 KH2PO4, thus partially recreating the physiological conditions of human blood. In this case, in both CV and the pulsed technique, instead of the oxidative peak in the cathodic scan, a reduction process is observed. In the presence of chlorides, it is known that gold is oxidized to AuCl-4, a reaction that takes place at a lower potential than Au(OH)3 formation. In the cathodic scan the gold tetrachloroaurate, previously generated in the anodic scan, is reduced.
However, upon analyzing the Pourbaix diagram of gold in the presence of chlorides, it is evident that at pH values higher than 9, gold hydroxide is the most stable phase, even in the presence of up to a 2 M chloride concentration. Therefore, it is not necessary to remove all the chlorides from the solution to perform the sensing step, but it is enough to locally increase the pH to over 9. On the basis of these considerations, a four-step, three electrode (silver gauze, gold pin and platinum counter electrode) measurement has been performed. The optimized operating conditions are reported in
The first step is a chronopotentiometry step, (I=10 mA) in which a silver gauze working electrode is oxidized to silver chloride, while water is reduced at the platinum counter electrode. In the overall reaction, for every chloride ion removed, a hydroxide ion is generated; therefore to shift the solution pH from 7.4 to 11.5 it is necessary to remove only 10% of the chlorides present in the solution. Thus the charge flow needs to be controlled, and it depends on th volume of solution employed (in the exemplary case we used 15 ml of solution and the charge was limited to 5 mC).
The second step corresponds to the first step of the pulsed technique described supra, in which a the gold pin electrode surface is oxidized to gold hydroxide (0.7 V vs. RE, 40 s) and subsequently reduced (0.3 V vs. RE, 15 s) in the third step: once the gold surface is regenerated, glucose can be re-adsorbed and an oxidative peak is generated. In this case, both the peaks observed in the CV, (
In the present invention, we identified a device and method for electrochemically sensing glucose in the presence of chlorides. These electrochemical devices and methods grant higher accuracies and sensitivities than enzymatic methods. All the materials employed (silver, platinum and gold) are fully compatible with in vivo sensing applications.
The examples reported have been tested in 15 ml of solution, which necessitates long time steps. The invention is not limited to the implementation of a miniaturized device which reduces each step time signitifantly.
This application claims priority from U.S. Provisional Patent Application 61/374,510 filed Aug. 17, 2010, which is incorporated herein by reference.
Number | Date | Country | |
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61374510 | Aug 2010 | US |