Monitoring of Glucose in Beer Brewing by a Carbon Nanotubes Based Nylon Nanofibrous Biosensor

Mason, Marco; Longo, Edoardo; Scampicchio, Matteo

doi:https://doi.org/10.1155/2016/5217023

Journal of Nanomaterials

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Research Article | Open Access

Volume 2016 | Article ID 5217023 | https://doi.org/10.1155/2016/5217023

Monitoring of Glucose in Beer Brewing by a Carbon Nanotubes Based Nylon Nanofibrous Biosensor

Marco Mason,¹Edoardo Longo,¹and Matteo Scampicchio¹

Academic Editor: William Yu

Received25 Mar 2016

Revised24 May 2016

Accepted25 May 2016

Published26 Jun 2016

Abstract

This work presents the design, preparation, and characterization of a novel glucose electrochemical biosensor based on the immobilization of glucose oxidase (GOX) into a nylon nanofibrous membrane (NFM) prepared by electrospinning and functionalized with multiwalled carbon nanotubes (CNT). A disc of such GOX/CNT/NFM membrane (40 μm in thickness) was used for coating the surface of a glassy carbon electrode. The resulting biosensor was characterized by cyclic voltammetry and chronoamperometry, with ferrocene methanol as mediator. The binding of GOX around the CNT/NFM greatly enhances the electron transfer, which results in a biosensor with a current five times higher than without CNT. The potential usefulness of the proposed biosensor was demonstrated with the analysis of glucose in commercial beverages and along the monitoring of the brewing process for making beer, from the mashing to the fermentation steps.

1. Introduction

Electrochemical biosensors represent a milestone in the field of analytical electrochemistry. High chemo- and stereoselectivity, low manufacturing costs, thermal and chemical stability, and simplicity of construction are some of the attractive features that drive the research on the development of new electrochemical biosensors [1, 2]. Among the different biosensors available, glucose biosensors have been one of the most successful examples due to the biomedical applications for diabetic patients [3, 4]. So far, researches have focused on the development of biosensors with enhanced signal transduction, larger linearity range, and higher sensitivity [3–11]. The approach used has always been based on the improvement of signal transduction between flavin adenine dinucleotide (FAD), the redox species involved in the GOX kinetic, and an opportune transducer [12]. Overall, the process is a two-electron mechanism in which the reduction of FAD to FADH₂ takes place at the expenses of glucose as the electrons donor [13]. Notably, in absence of oxygen only direct electrode oxidation of FADH₂ can occur. The direct electron transfer kinetics of the oxidation of FADH₂ by the electrode is hampered since FAD is buried 25 Å deep from the outer protein surface, preventing the direct electron transfer with the electrode [2, 5]. To circumvent this drawback, first-generation biosensors were based on the direct detection of the generated hydrogen peroxide (as FADH₂ is reoxidized at the expenses of oxygen). Although the direct measurement of peroxide formation is attractive because it is simple and fast, the amperometric measurement requires large overpotentials. When biological samples are analyzed, the resulting response current may suffer from the interferences of coexisting electroactive species.

Second-generation biosensors overcame such limitations by replacing the oxygen with a reversible redox mediator that is able to shuttle the electrons from the redox center of the enzyme to the electrode surface (Figure 1).

A suitable mediator for the GOX enzyme is required to have a higher redox potential than the flavin redox center, so that it acts as the electron acceptor. For its fast reversibility and diffusion into interface layers, ferrocene methanol has been widely employed as the redox mediator of choice ( versus Ag/AgCl = 0.216 V, cm·s⁻¹) [14].

Immobilization of the enzyme onto the electrode surface offers additional improvements. The advantage is that both enzyme and mediator can be brought close to the electrode surface, increasing the efficiency of the electron transfer between the enzyme and the electrode. Several methods of immobilization have been tested such as hydrogel encapsulation [4, 13–15], electropolymerization [16], or polymer film trapping [17–20]. Several improvements have also been devised in order to prevent unfavorable random orientations of the active site of the protein, such as templates or orienting functional groups [17, 20–25]. However, these approaches involve a certain effort to control the enzymes positioning to minimize the partial loss of catalytic efficiency due to active site wrong orientations.

A way to further enhance the electrochemical response has been to incorporate conductive elements between the electrode surface and the flavin redox center to enhance the heterogeneous electron transfer process. Carbon nanotubes (SWCNT or MWCNT) have been tested within biosensors, allowing both faster heterogeneous electron transfer and rigid scaffold orientation locking, for more efficient biosensors [6, 25–28]. Some carbon nanostructures in particular show exceptional conductive properties. Moreover, polymer-CNT composites are easy to prepare and effectively displayed enhanced conductivity properties, along with better mechanical and thermal resistance [29–32]. Electrospinning (ES) has been recently applied as an intriguing way to prepare nanofibrous (NF) polymers with high surface-to-volume ratio. ES has gained attention in engineering and material science for its exceptional simplicity, low cost, and industrial applications [20, 33]. Several reviews have been presented on this topic describing details on how this technique can be performed in-house by any laboratory [33–36]. Recent works in particular pointed out the good performances of electrospun Nylon-6 nanofibrous electrospun membranes (NFM) decorated with GOX for biosensing of glucose also in presence of interferents, showing good selectivity also in relatively complex matrices [6].

Glucose biosensors have a number of well-developed applications, from the biomedical (i.e., glucose monitoring for diabetic patients) to the pharmaceutical field. Also in food technology there are several potential applications where the features of glucose biosensors could provide a benefit for the producers. Apart from the classical analysis of glucose in fruit beverages, a very intriguing application of glucose biosensors could be the monitoring of glucose evolution and/or consumption during the production of alcoholic beverages, such as wine or beer. In particular, during beer brewing, the use of glucose biosensor could be of special help because it would provide information on the extent of the mashing process, where polysaccharides are progressively hydrolyzed into fermentable sugars, or during fermentation, where sugars are transformed into alcohol and carbon dioxide [37]. Thus, the simple and rapid monitoring of glucose could be of practical importance for the brew maker. In Table 1 some published results from glucose monitoring during several beer brewing steps and beer samples are reported.

Apart from brewing studies, a wide investigation of immobilized GOX for glucose sensing has been done [2, 5, 38]. Accordingly, this work aims to investigate the application of Nylon-6 nanofibrous electrospun membranes (NFM), functionalized with multiwall carbon nanotubes (CNT) and loaded with glucose oxidase (GOX) for the analysis of glucose content in fruit beverages and for the monitoring of glucose evolution in the beer brewing process.

2. Materials and Methods

GOX (from Aspergillus Niger Type XS, lyophilized powder, 100000–250000 units/g), salts, formic acid, and Nylon-6 beads were purchased from Sigma-Aldrich and used as delivered. MWCNT were bought by Nano-Lab (Waltham, MA, US).

2.1. Carbon Nanotubes Preparation

MWCNT as delivered were treated in 6 M HNO₃ (60°C for 16 h) and 8 M HCl (80°C for 5 h) for activation. After pretreatment, MWCNT were recovered by centrifugation at 6000 rpm for 15 minutes, washed in ethanol, ultrasonicated for 2 hours, and dried at 40°C for 5 to 16 hours until no weight loss was observed.

2.2. Electrospinning

Electrospinning (ES) was performed with an in-house apparatus based on a Spellman® CZE 1000R potentiostat equipped with a syringe pump. All NFM were electrospun at a flux of 0.02 mL/min onto an aluminium foil that acted as a grounded collector, when a +25 kV potential was applied on the flux exit needle located at 13 cm distance. Humidity in the environment was kept below 40% throughout the procedure. The NMF were functionalized with MWCNT by in-solution dipping. The resulting composite was analyzed by SEM (Figure SI 4 in Supplementary Material available online at http://dx.doi.org/10.1155/2016/5217023). Comixing the polymer precursor solution with MWCNT was also undertaken but it did not yield a viable way in terms of NFM strength and membrane conductivity; therefore this approach is not discussed any further herein. Immobilization of the enzyme was achieved by means of glutaraldehyde as the cross-linker, in presence of bovine serum albumin. This approach was adapted from a published methodology [6].

2.3. Functionalization of NFM with MWCNT Coating

A weighed amount of NFM 3.8 mg (2 sides of 9.62 cm²) with a thickness of mm was dipped into a 50 mM Triton™ X-100 solution containing a pretreated and sonicated MWCNT dispersion with concentration of 0.5 mg·mL⁻¹. The mixture was ultrasonicated for 10 hours a day for one week (50 W, 40 kHz at 25°C); then the membrane was removed and dried at 50°C for 20 minutes, carefully plunged in milliQ water until surfactant rinsing and dried again at 50°C for 30 minutes. After reweighing the membrane coated with MWCNT, the final amount deposited on the membrane was 4.5% of initial weight. The final membrane presented a homogeneous black coating.

2.4. Scanning Electron Microscopy

NFM scanning electron micrographs were collected on a Phenom™ ProX SEM instrument (70–20000x digital zoom) with 30 nm max resolution. Samples were mounted on aluminium stubs and images were collected at 5 or 10 kV accelerating voltage. All samples were mounted on biadhesive tape and purged with a gentle air flow prior to measurement. Fibers diameter dispersion was evaluated with the provided Phenom Pro Suite using the Fibermetric tool. Average diameter distributions were evaluated by fitting with a Gaussian function.

2.5. Electrode Coating

A bare glassy carbon working electrode (BAS) was first polished with 0.3 and 0.05 μm alumina slurry, then rinsed with water, and sonicated in EtOH, till a mirror-like surface was obtained. A piece of Nylon-6 NFM prepared as described before was placed on top of the electrode surface and fixed with two O-rings (all membrane exceeding parts were carefully cut off).

2.6. Enzyme Immobilization

An enzyme solution was prepared in two steps: first, 40 mg of BSA and 11.4 mg of GOX were dissolved in 1 mL of Britton-Robinson pH 5. Then glutaraldehyde (5 μL, 2.5%) in water was added to 15 μL of this solution. The coating solution was freshly prepared before electrode coating. 5 μL was dropped twice to the center of the membrane and left drying for 10 minutes at room temperature. After the immobilization, the biosensor was placed in Britton-Robinson pH 5 and stored at 4°C.

2.7. Electrochemical Characterization

CV experiments were performed using an AUTOLAB 128N potentiostat. A 0.07 cm² glassy carbon working electrode, Ag/AgCl reference, and 1 cm² Pt counter electrode (BAS) were used in 0.4 M Britton-Robinson buffer at room temperature. Cyclic voltammetry was performed in the range from −0.2 V to +0.6 V. 100 μM Ferrocene methanol was used as mediator, with or without the presence of glucose. Chronoamperometric measurements were performed under stirring at an applied potential of +0.5 V with a 0.5 s per point acquisition time.

2.8. Determination of Glucose with the Dinitrosalicylic Acid (DNS) Reagent

The reagent was prepared by adding 5 g of DNS salt in 200 mL of distilled water containing 150 g of potassium sodium tartrate tetrahydrate and 8 g of sodium hydroxide. Care was taken by first mixing the tartrate and NaOH solutions and then adding the DNS salt. The solution was left overnight under stirring. The following day, a final volume of 500 mL was reached by adding distilled water [52]. An aliquot of standard or sample was diluted to 2 mL with deionized water and mixed with 2 mL of DNS reagent. Before UV-VIS measurement, the solution was heated in boiling water for 3 minutes. The determination was performed on an Agilent Cary 100 spectrophotometer provided with a Peltier thermostated 12-cell unit at 25°C. The spectra were collected between 500 and 650 nm (2 nm bandwidth, 1 point per sec integration time). The measurements of each standard or sample were repeated in triplicate. Sample concentrations were calculated by taking into account dilution factors.

2.9. Beer Preparation and Glucose Analysis

The beer making process has been monitored throughout the brewing steps. The samples have been collected in the following steps. (1) Malt (500 g) was milled (mill rollers knurled stainless steel AISI 316) and then added to warm water (1.5 L, 52°C). (2) The temperature was kept at 52°C for 15 minutes. In this step, the proteases contained in the malt provide a source of free amino acids, which are being used later by the yeast during fermentation. (3) The temperature was raised to 62°C and kept for 10 minutes (maltose production). (4) This was followed by a further raise at 68°C that was kept for 30 minutes (saccharification). In steps (3) and (4) the α- and β-amylases break down starch molecules into fermentable sugars (i.e., glucose and maltose). (5) The temperature was further raised at 78°C and kept for 15 minutes to inactivate the enzymes. (6) Then, the wort was filtered and washed with water (about 500 mL). (7) The sweet wort was then boiled for 1 h, during which 2.8 g of hops was added (Hallertau Hersbrucker). After boiling, the hops were removed and the wort rapidly cooled down to room temperature thanks to a heat exchanger. Then 1 g of yeast (Danstar Nottingham British Ale) was added for starting the fermentation (fermentation day 0). The fermentation was monitored for additional 4 days (steps (8) and (11)). The evolution of glucose during the fermentation was monitored. Wort samples were filtered with a 0.2 μm CA membrane. 1 mL or 1.5 mL of the filtered solution was then added to the biosensor measurement cell prepared with 10 mL of 100 μM ferrocene methanol solution. The response current was read after at least 200 s of plateau equilibration.

3. Results and Discussion

3.1. Characterization of the GOX-NFM/MWCNT by Cyclic Voltammetry

The sensing mechanism for this second-generation GOX biosensor is schematically described in Figure 2.

Briefly, glucose is converted to gluconate (A) by reducing FAD into FADH₂ (FAD reduced form). FADH₂ is oxidized back (B) by the mediator (e.g., ferrocene methanol) which becomes reduced (C). FAD becomes this way available again to accept electrons from glucose. The reversible mediator is free in solution and can get closer to the anode. Therefore, it is oxidized at the coated electrode directly and through mediation of the carbon nanotubes (D). It becomes again available this way for reduction by FADH₂. The overall effect provided by carbon nanotubes in ET enhancement has been elucidated and consists in a better current transduction [53, 54]. To show the effect of added MWCNT on our biosensor, Figure 3 compares the effect of CNT on the resulting mediated detection of glucose by ferrocene methanol. In detail, when the electrode is coated with NFM and loaded with GOX, the resulting voltammogram reflects the typical response of a mediated biocatalytic reaction, where the reversible voltammetry of the mediator turns irreversible with the anodic current reaching a plateau at potential higher than +0.2 V versus Ag/AgCl. Upon reversing the direction of potential scan, no reduction peak is observed, as expected when the oxidized form of the mediator is rapidly consumed by the continuous oxidation of FADH₂ (Figure 3(a)). When the NFM was functionalized with CNT and the enzyme was free in the bulk solution, the result is similar but the background current is increased. The prominent background current is a consequence of the large, catalytically active surface area of the modified electrode. Apart from the higher capacitive current, the signal enhancement is negligible (Figure 3(b)). However, when the glassy carbon electrode is coated with NFM functionalized with CNT and loaded with glucose oxidase, a great enhancement on the current response is observed (Figure 3(c)). Since such higher current density is observed only when the enzyme is immobilized on the conductive surface of the NFM functionalized with CNT, we conclude that such enhancement is due to the electron shuttling of CNT from the active site of GOX toward the glassy carbon transducer [53].

Figure 3

Cyclic voltammetry of glucose at a glassy carbon electrode coated with (a) NFM with GOX immobilized; (b) NFM/CNT with GOX free in solution; (c) NFM/CNT with GOX immobilized. Experiment: 25.2 mM D-glucose, 100 μM ferrocene methanol, and Britton-Robinson buffer, 400 mM, pH 5. Detection was performed at 100 mV s⁻¹ scan rate. A full characterization of anodic peak current versus the scan rate and evaluated diffusion coefficients are reported in Supporting Information (Table SI 1 and Figure SI 1).

3.2. Analytical Performance of the Biosensor by Chronoamperometry

Chronoamperometry is a very sensitive technique for electrochemical biosensors characterization. In order to evaluate the analytical performance of the glassy carbon electrode coated with NFM/CNT/GOX, Figure 4 shows the chronoamperometric calibration of glucose in presence of 100 μM ferrocene methanol.

Although the GOX enzyme amount was the same both with loaded CNT and without, the effect of the biosensor design on the resulting signal intensity was huge. With respect to both the system with no immobilized enzyme and the one with no MWCNT loaded, NY CNT + imm GOX displayed a much higher response to glucose additions. Notably, all points correspond to 10 μL additions. As we discussed before, the addition of nanotubes (SWCNT or MWCNT) enhances the efficiency of the biosensor by increasing the electron transfer. This is consistent with our data. In fact, also with free GOX (purple curve) nanotubes induce a higher response. This effect can be seen by the higher plateau currents at the highest concentrations. On the contrary, the only immobilization of the enzyme has a little effect on the overall current even if it can extend the linearity range against glucose addition [6]. Under optimized conditions, the glassy carbon electrode coated with NFM/CNT/GOX showed a linearity range from 1 to 3 mM (). In such range the sensitivity was 1.2 μA·mM⁻¹ (RSD% = 2%) with a limit of quantitation of 20 μM (). Although the linear range was smaller than the one reported with a similar biosensor [6], the sensitivity was four times higher. Such higher sensitivity is a direct consequence of the loading of CNT on the surface of the nanofibers.

3.3. Kinetic Behavior of GOX-NFM/MWCNT and Effect of pH, Interferents, and Ageing

The kinetics of the enzyme before and after its immobilization on the NFM/CNT was studied by chronoamperometry for increasing concentration of glucose (0–12 mM) and at several pH values. As an example, Figure 5 shows the resulting current versus concentration plots at pH 5. The experimental points were initially fitted with a classical Michaelis-Menten model. Unfortunately, only when the enzyme was free in solution, the resulting current response obeyed this model. Conversely, when GOX was immobilized on the NFM, the current response showed a sigmoidal trend. The trend is fitted instead very well with the Hill equation, a generalized Michaelis-Menten model.

Figure 5

Chronoamperometric current responses of the biosensor with the GOX free or immobilized on the NFM/CNT, for increasing concentration of glucose. In the case of the GOX free in solution (NY CNT + free GOX), experimental points were fitted with Michaelis-Menten equation: , where )10⁻⁶ and . In the case of GOX immobilized on the NFM/CNT, the points were fitted with a Hill type equation: , where START = (−)10⁻⁷, END = ()10⁻⁵, = , and . In both cases, was 0.998. For the Michaelis-Menten fitting of NY CNT + imm GOX = mM, = μA (fitting was bad; therefore it is not shown).

The effect of pH on immobilized GOX kinetics was investigated between 5 and 7. For the free GOX, the optimum has been found between these values, and for immobilized GOX the values have been found below 6 and above 7, depending on the preparation [1, 51, 55]. In our case the optimum was found between 5 and 6 and the minimum value at 6.5. The Michaelis-Menten model did not fit the whole dataset properly. In fact, the current response for glucose concentrations below 1 mM deviates from linearity. Therefore, the Hill equation was alternatively applied to evaluate the asymptotes of the curves, namely, the values ( of Hill model): μA, μA, μA, μA, and μA at pH values 5, 5.5, 6, 6.5, and 7, respectively (data collected at the same ageing time on the same system equilibrated at the pH required). The reason for analyzing is that corresponds to one-half of the concentration required for the enzyme to reach the conversion speed limit (the asymptote or ). Therefore, (the actual experimental limit) can account qualitatively for the efficiency of the enzyme. This trend is not trivial to discuss. More investigations will be required to elucidate the lack of a precise trend in efficiency moving away from pH 6. We carried out the analyses at pH 5 instead of pH 6 because of the wider linear range. For the linear fitting of the 1–4 mM range at pH 5 was 0.98 and at pH 6 was 0.94. At pH 6, was near 0.98 only in the 1-2 mM range. Just for a comparison with other published results, we calculated the apparent Michaelis-Menten constant at pH 5 that was mM. This constant accounts for the enzyme efficiency and the found value is in good agreement with others reported in literature [9]. However, the immobilization strategy and the biosensor design can affect the enzyme efficiency so that much higher values are possible (e.g., 44 mM) [56]. Since the MM model did not fit the data and a generalized model (i.e., Hill equation) was used instead, we hypothesized the presence of a barrier-to-diffusion stage that the substrate has to overcome at lower concentrations. When the concentration of glucose is low, the substrate diffusion toward the “pseudo” pores of NFM is very limited. Only when glucose is higher than 1 mM, the transduction efficiency of the enzyme becomes linearly related to its concentration.

Such biased response, low signal intensity for low concentration of the substrate and high sensitivity for concentrations higher than about 1 mM, was invariant for the amount of substrate added. Figure 6 shows the current response of the electrode coated with NFM/CNT/GOX for different initial (up to 1.5 mM) single spikes of 0.5 M glucose. The resulting calibration plot was the same when the spikes were done every 20 or 10 μL of 0.5 M glucose, and the plateau currents (above 20 μL) show a good agreement with the linear trend (see Figure SI 2 where the same data in the whole linear range are shown).

The biased response observed for lower concentration of glucose was not ascribable to the loss of enzyme morphology. Although the immobilization process is known to cause shrinkage of the protein and possible modifications of the active site shape and dimension, the proposed biosensor did not show any loss of specificity. Figure 7 shows the current response of the electrode coated with NFM/CNT/GOX after the addition of (1) glucose, followed by sequential addition of other sugars, such as (2) sucrose, (3) maltose, and (4) fructose (followed by a second addition of glucose).

Figure 7

Chronoamperometry analysis of possible interferents. The numbers indicate addition points where there are (1) 50 μL 0.5 M glucose addition (2.5 mM final concentration), (2) 101.5 μL 0.5 M saccharose (5 mM final concentration), (3) 101.5 μL 0.5 mM fructose (5 mM final concentration), (4) 101.5 μL 0.5 mM maltose (5 mM final concentration), and (5) 50 μL 0.5 M glucose addition (5 mM final concentration). Measurements were taken at day 45 in 100 μM Ferrocene methanol in BR buffer pH 5.0.

The resulting signal of these interferents is limited to a negligible current decrease, which is consistent with the dilution factor consequent to the addition of a volume of solvent. After a further addition of glucose (point 5), the signal rose again consistently as the first spike, demonstrating that the presence of other sugars does not affect the current response to glucose. The maintenance of the initial specificity of GOX toward common sugars gives proof that the enzyme has not changed morphology during the immobilization procedure. We took into account other possible interferents, namely, phenolic acids and ascorbic acid. Both can theoretically contribute to the signal by direct oxidation at the anode at potential below 0.5 V. We measured a contribution of 2.8 μA mM⁻¹ gallic acid spiked in the experimental conditions (immobilized GOX, 100 μM ferrocene methanol, and Britton-Robinson buffer pH 5). However, the reported concentrations of this class of antioxidants in beer are some order of magnitude smaller [57]. For ascorbic acid instead, the response of spiked amounts in the set conditions was slightly higher (3 μA mM⁻¹); we found few references on its presence in beer. For example, in commercial beers the ascorbic acid concentrations allowed are <10 mg kg⁻¹ (58 μM) [58]. Moreover, each aliquot of beer sample was diluted in the measurement cell by a 1 : 100 dilution factor. As a further precaution during beer samples analyses we left the sample to equilibrate at room temperature before and after filtration, to equilibrate oxygen content that acts as oxidizing agent for ascorbic acid.

The stability of the biosensor over time was monitored by repeating the glucose calibration, in the same condition, within 30 days from the first test. The results are reported in Figure 8.

The loss of efficiency of the biosensor has been monitored over one month and the results of the first 26-day period are reported as overall loss of plateau END currents (analogue to MM , evaluated by Hill model fitting). Over one month it has been the 19%. Notably, the change is almost completely concentrated in the first 15 days and was almost negligible for the next 11 days (day 15 to day 26).

3.4. Biosensing of Glucose in Commercial Beverage and Beer Production Monitoring

The proposed biosensor was firstly tested on a commercial beverage and then to monitor a brewing process. In both cases, an aliquot of the selected beverage or wort (at each preparation stage) was added to 10 mL of Britton-Robinson buffer solution (0.4 M, pH 5), where ferrocene methanol (100 μM) had been dissolved. For the commercial energy drink (Energade Orange flavor), the results where comparable with those obtained by the dinitrosalicylic acid (DNS, calibration reported in SI) assay. DNS test (see calibration curve employed in the Supporting Information, Figure SI 3) indicated a glucose concentration value of g·100 mL⁻¹ which is in perfect agreement with the result obtained with the biosensor of g·100 mL⁻¹. Notably, the measurements were performed in three replicates both for DNS and with the biosensor. The latter gave a much higher precision in terms of percentage error, namely, 33% for DNS and 2.3% for the biosensor. Then we applied the prepared biosensor to the analysis of the brewing process.

Figure 9 shows the current response obtained with the NFM/CNT/GOX biosensor during the beer brewing process. At the early steps of mashing (from (1) to (5)), the concentration of glucose sharply increased, reaching a plateau value at about 0.3 g·100 mL⁻¹. In step (6), the wort was washed to recover the leftover sugars (500 mL). The data were corrected to account for this dilution. During the fermentation the concentration of glucose dropped significantly, until the fourth day of fermentation, when the yeast has consumed almost all the glucose present in the wort.

Figure 9

Chronoamperometric analysis performed on filtered (0.2 μm filter) wort samples taken at different process times. 1000 or 1500 μL was added to 10 mL 400 mM Britton-Robinson buffer pH 5. Dilution factors were taken into account for concentration calculation. Measurements were repeated in triplicate. Summary of analyzed steps: (1) addition of the malt in water (52°C); (2) protease rest (52°C for 15 min); (3) maltose production (62°C for 10 min); (4) saccharification (68°C for 30 min); (5) deactivation of the enzymes (78°C for 15 min); (6) filtration of the wort and washing with water (about 500 mL); (7) addition of the hops and boiling (for 1 h) followed by removing the hops and cooling down to room temperature at which the yeast was added; (8) fermentation: day 1; (9) fermentation: day 2; (10) fermentation: day 3; (11) fermentation: day 4.

4. Conclusions

GOX-NFM/MWCNT showed a good reproducibility over more than one month of utilization. This system is endowed with qualities such as a very low cost of production, storage resistance, and fast response time in the linear range (10–20 s). Moreover, it displays complementarity with other more classical analytical methods such as DNS and Brix. Together, they allow investigating the evolution of glucose with respect to other sugars. Still, both DNS and Brix are not sufficient to account for the evolution of specific sugar in matrices as complex as beer. Conversely, the biosensor shows a complete insensitivity toward other mono- and oligosaccharides even at concentration equal to or higher than glucose. The sensitivity of the biosensor in the linear range was evaluated to be 12 μA·mM⁻¹ with an evaluated limit of quantitation of 20 μM. Moreover, the kinetics of the immobilized GOX was evaluated with respect to free GOX. Michaelis-Menten model failed to actually fit the data; therefore the more general Hill equation was employed. Notably, the same effect was not observed with free GOX, where MM could be successfully applied. As future developments, the enzyme life and the enzymatic performances could be extended by preventing detachment from the nylon NMF. This research has demonstrated the suitability of the proposed biosensor for the monitoring of very complex fluids such as those deriving from the brewing process. Accordingly, the findings of this study may pave the way to a number of important applications for future practice. For instance, the proposed biosensor will be useful in the quantification of glucose in fruit juice [59], in fermentation process of fruit must [60], or even in the development of electronic tongue method for the objective evaluation of sweetness in beverages [61]. The possible applicability of the biosensor seems limited only by the presence of other redox species, such as ascorbic acid, that, when present at high concentrations, may interfere with the mediated biosensing mechanism. However, even in such unfavorable circumstance, the detection of glucose is still possible, provided that the sample is thoroughly aerated before the analysis, as ascorbic acid reacts quickly and irreversibly with oxygen.

Competing Interests

The authors declare no competing interests related to the publication of this paper.

Supplementary Materials

Figure SI 4 shows examples of the SEM micrographs of the coated and uncoated electrospun nanofibers obtained. An evaluation of the respective diameter dispersion is also provided. In the higher-right picture it is also possible to appreciate the MWCNT coated on the Nylon 6 fibers.

Supplementary Material

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Copyright © 2016 Marco Mason et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

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