Development of Galactose Biosensor Based on Functionalized ZnO Nanorods with Galactose Oxidase

Khun, K.; Ibupoto, Z. H.; Nur, O.; Willander, M.

doi:https://doi.org/10.1155/2012/696247

Journal of Sensors

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Research Article | Open Access

Volume 2012 | Article ID 696247 | https://doi.org/10.1155/2012/696247

Development of Galactose Biosensor Based on Functionalized ZnO Nanorods with Galactose Oxidase

K. Khun,¹Z. H. Ibupoto,¹O. Nur,¹and M. Willander¹

Academic Editor: P. Siciliano

Received31 Dec 2011

Revised28 Apr 2012

Accepted13 May 2012

Published05 Jul 2012

Abstract

The fabrication of galactose biosensor based on functionalised ZnO nanorods is described. The galactose biosensor was developed by immobilizing galactose oxidase on ZnO nanorods in conjunction with glutaraldehyde as a cross-linker molecule. The IRAS study provided evidence for the interaction of galactose oxidase with the surface of ZnO nanorods. The electromotive force (EMF) response of the galactose biosensor was measured by potentiometric method. We observed that the proposed biosensor has a linear detection range over a concentration range from 10 mM to 200 mM with good sensitivity of mV/decade. In addition, the proposed biosensor has shown fast time response of less than 10 s and a good selectivity towards galactose in the presence of common interferents such as ascorbic acid, uric acid, glucose, and magnesium ions. The galactose biosensor based on galactose oxidase immobilized ZnO nanorods has a shelf life more than four weeks.

1. Introduction

Recently, zinc oxide (ZnO) has become one of the most important semiconductor materials used in the research due to its attractive properties such as a large band gap of 3.37 eV, high exciton binding energy of 60 meV, and optical gains 300 cm⁻¹ at room temperature [1–4]. ZnO nanomaterials exist in variety of one-dimensional (1D) nanostructures such as nanorods, nanotube, nanowalls, and nanowires, and all these nanostructures have potential applications in making devices such as light emitting diodes (LEDs), optical waveguides, nanolaser [5–9], gas sensor [10], chemical sensor [11], and biosensor [12]. Due to the high surface area to volume ratios, nontoxicity, chemical stability, and enhanced electrochemical response, these nanostructures possess a potential for sensor application [10–13]. Among the many nanostructures of ZnO, nanorods were largely used for sensing purposes because of their high surface area to volume ratios [14–19]. ZnO nanorods are -type semiconductor material and their electrical characteristics are well defined through the adsorption/desorption properties of chemical substance [20–25].

Galactose in the human body is metabolized after the lactose hydrolysis by different enzymes such as galactokinase, galactose-1-phosphate uridyl transferase, and beta galactoside and galactose-6-phosphate epimerase. The galactosemia is an inherited disorder analyzed from the inability of human body to utilize galactose because of the insignificant amount of one or more of these enzymes, which metabolize galactose and result in galactosemia in the human body. It is the higher level of galactose in the urine and blood which is responsible for the symptoms of galactosemia, galactosuria, and other metabolic disorders [26]. The classic galactosemia is a familiar type of galactosemia which is due to the absence of galactose-1-phosphate uridyl transferase (GALT) or its lower quantity. The GALT enzyme in the human body changes the galactose into the glucose that provides energy. The intensity of galactosemia is different for a person who is suffering from it, because every person has a different level of these enzymes; hence the needed therapy varies from one person to another. Persons with galactosemia should keep away from milk and dairy products, because those dietary foods have high level of galactose. The level of galactose-1-phosphate in the blood should be kept below 3-4 mg dl⁻¹. Fruits, vegetables, grains, breads, fats, and sugars do not have components containing galactose. Some vegetables and fruits have a few amount of bound galactose which is not consumed by the human body; therefore it can raise the galactose-1-phosphate level in the blood.

Non processing galactosemia raises galactose and galactose-1-phosphate in the blood stream and body tissues. Generally, the human body can have problems with feeding and growth because of the unrecognized galactosemia. Due to the unrecovered galactose, babies may suffer from some diseases such as cataracts, liver diseases and kidney problems [27–30]. However, increased level of galactose and galactose-1-phosphate can be dangerous to brain and finally leads to death. Because of the galactosemia, children may become disable in learning and girls may suffer from ovaries problems [31, 32]. The human body can be fed with soy formula, nutramigen or galactose-free formula such as zerolac, nusobee, and simyl-MCT and also different ways [33, 34]. Galactose in the food can be determined by different types of biosensors such as biostrips [35–39]. The quantity of galactose in the dairy samples is measured by biostrip method and the results of this method were compared with reported values of different dairy samples [40].

There are many methods used for the firm binding of enzyme molecules with the biosensor electrodes and a very common method is the use of cross-linker molecule for the entrapment of enzyme molecules. Many synthetic polymers such as polyacrylamide, polyurethane, polyvinyl alcohol, polyvinylchloride, polyhydroxyethyl methacrylate, and polyvinyl formal (PVF) were frequently used to detect the galactose; due to their several advantages such as higher mechanical strength, chemical resistance and can also act as a complex buffer candidates. It has also been reported the amperometric galactose biosensor based on the galactose oxidase immobilized Langmuir-Blodgett (LB) film [41, 42].

In this work, a simple, sensitive and highly selective potentiometric galactose biosensor is developed by immobilizing galactose oxidase on ZnO nanorods grown on gold coated glass.

2. Experimental Detail

2.1. Material

Galactose oxidase (150UN), D-galactose, glutaraldehyde (GA) (crosslinking molecule), zinc nitrate hexahydrate [Zn (NO₃)₂·6H₂O], hexamethylenetetramine (HMT), D-glucose, and L-glucose-fructose were purchased from Sigma Aldrich Sweden. A phosphate buffer solution (PBS) with 10 mM concentration was prepared using 2.7 mM potassium chloride (KCl), 0.135 mM sodium chloride (NaCl), 1.5 mM potassium dihydrogen phosphate (KH₂PO₄), and 8 mM sodium dihydrogen phosphate (NaH₂PO₄) in deionized water. The pH of the buffer solution was adjusted by adding 100 mM hydrochloric acid (HCl) and 100 mM sodium hydroxide (NaOH). All these chemicals were also purchased from Sigma Aldrich Sweden. The chemicals used other than these were of analytical grade.

2.2. The Fabrication of Gold Coated Glass Substrate and Growth of ZnO Nanorods

The process of fabrication of gold coated glass substrates was as followed: firstly the glass substrates were washed with isopropanol in ultrasonic bath for 10 minutes, and then cleaned with deionized water and dried with nitrogen gas. After that the clean glass substrates were placed in the vacuum chamber of (Satis CR 725), for producing a 10 nm layer of titanium as an adhesive surface, and then followed by evaporation of a 100 nm thickness layer of gold. ZnO nanorods were grown on these substrates by the hydrothermal method, which is a low cost, a simple, and a low temperature growth method [19]. After the duration of growth, the nanostructures were characterised by the field emission scanning electron microscopy (FESEM) and it was seen that ZnO nanorods were highly dense and well aligned as shown in Figure 1(a).

(a)

(b)

2.3. Immobilization of ZnO Nanorods with Galactose Oxidase

We have immobilized five independent biosensor electrodes based on ZnO nanorods and immobilized with galactose oxidase in combination with GA as a cross-linking molecule for the galactose oxidase enzyme as shown in Figure 1(b). We prepared 2.5% GA solution in 0.1 mM PBS and also a galactose oxidase solution was prepared in PBS having a concentration of 150UN per 4 ml of PBS. We functionalised the ZnO nanorods electrodes within a mixture of galactose oxidase and GA for 4 minutes. We also investigated the effect of immobilization time on the response of the sensor electrode, but at 4 minutes the response of the sensor electrode was found higher due to almost complete physically adsorbed layer of galactose oxidase on the surface of ZnO nanorods.

2.4. IRAS Study of Galactose Oxidase Immobilized ZnO Nanorods

Figure 2(a) shows the FTIR spectra of ZnO nanorods. This study revealed that the peak at 549 cm⁻¹ the stretching modes correlated with ZnO nanorods [43]. The peaks at 3668 cm⁻¹ might be for the O-H hydroxyl stretching vibration of absorbed water molecules on the surface of the ZnO nanorods. The peak at 2380 cm⁻¹ was found to be for the CO₂ during the measurement. When the galactose oxidase was immobilized on ZnO nanorods, then the peaks 549, 699, 1163, 2533, and 3668 cm⁻¹ were shifted to 554, 652, 912, 2259, and 3247 cm⁻¹, respectively, as shown in Figure 2(b). This clearly shows the interaction between the galactose oxidase enzyme molecules with the surface of the ZnO nanorods. The appearance of extra peaks in the spectra might be due to possible impurity in the sample.

(a)

(b)

The electromotive force (EMF) response of the proposed biosensor based on the immobilized ZnO nanorods was measured by potentiometric method, which used the immobilized ZnO nanorods as a working electrode and silver-silver Ag/AgCl as reference electrode. For avoiding the reduction in the activity of the immobilized galactose oxidase, the biosensor electrodes were kept at 4°C when not in use.

3. Results and Discussions

3.1. The Characterisation of EMF Response of Functionalized ZnO Nanorods Selective Electrode

The EMF response of the potentiometric galactose biosensor based on galactose oxidase immobilized ZnO nanorods is shown in Figure 3. During the experiment we observed that the EMF response is the function of the galactose concentration and also on the rate of oxidation of galactose in the presence of galactose oxidase on the surface of ZnO nanorods. Which increases the concentration of unstable galactohexodialdose; H₂O₂ and further it decompose into the gluconic acid in the testing solution of galactose. It is the gluconic acid which increases the amount of H₃O⁺ ions into analyte solution. So in result the EMF response of the sensor electrode was increasing with the increase of the concentration of the electrolytic solution. It also has been reported that when there are the number of charges around the working electrode, then potential is observed [44]. The EMF response of enzyme based biosensors also depends on the catalytic efficiency of enzyme in specific conditions, higher is the catalytic efficiency of enzyme, greater is the EMF response of biosensor electrode. We tested the working biosensor electrode into different galactose concentrations from 1 mM to 200 mM; it had shown the linearity from 10 mM to 200 mM. The biosensor detected 1 mM concentration of galactose, but it was out of the linear range, and biosensor followed the Nernst’s equation as shown in Figure 3. The sensitivity and detection limit of the biosensor electrode was found to be about 89.10 ± 1.23 mV/decade and 1 mM, respectively.

3.2. Effect of pH and Temperature on the Operation of Biosensor

The purpose of this study was to demonstrate the effect of pH and temperature on the EMF of the present galactose sensor electrode. It has been investigated that the pH and temperature has pronounced effect on the performance of the biosensors. The effect of pH was studied for the pH range of 4 to 12. We observed that the biosensor showed the same response for a pH 6 and 7, but above pH 7 the EMF response was decreasing due to the fact that the galactose oxidase has optimum pH around 7 and higher pH might be decreasing the activity of immobilized enzyme on the ZnO nanorods [45]. However, the biosensor has shown increasing response for pH values below 5, because of the higher concentration of the hydronium ions, but we carried out all experiments at pH 7 in order to avoid the dissolution of ZnO nanorods in acidic medium as shown in Figure 4. It can be inferred from Figure 4 that the EMF response decreases for pH above 8 and increases for pH below 6.

The EMF response of the biosensor is also affected by the change in solution temperature. During this study, we measured temperature range from 20°C to 75°C. The biosensor has shown maximum response at 40°C and above this temperature the EMF response was decreasing as shown in Figure 5. This is because at high temperature, the enzyme molecules might be denatured, whereas at 40°C the galactose oxidase has maximum activity. We did all experiments at room temperature due to ease in the handling of the experimental setup and to avoid from the possible evaporation of analyte solution [46].

3.3. Study of Common Interfering Substances on the EMF Response and Response Time of Galactose

Selectivity of a biosensor is a key parameter for the evaluation of performance in the presence of common interferents. In this work, we examined the effect of common interferents such as ascorbic acid, glucose, magnesium ions Mg²⁺, and uric acid on the response of the proposed galactose biosensor-based immobilized ZnO nanorods using the separation solution method. The calculated selective coefficient values are summarised in Table 1. From the published similar biosensor results have been observed that uric acid and ascorbic acid were causing interference [47], but in this study it was noticed that the proposed galactose biosensor has shown no response to uric acid and a negligible response to ascorbic acid. We further studied the response time of the present galactose biosensor using electrical instrument (Keithley 2400) for the measurement of response time. The biosensor had shown a fast response time of less than 10 seconds as shown in Figure 6. We also studied the effect of galactose concentration on the time response of the biosensor and it was observed that the biosensor shown the inverse time response relation with the galactose concentrations.

3.4. Study of Life Time of Biosensor

During the investigation of stability and life time of the present biosensor, we found that the biosensor has a life time more than four weeks. When the galactose biosensor was tested for four successive weeks and it was observed that the detection limit was higher and sensitivity was almost same. This change in the detection limit could be because of the detachment of the enzyme molecules from the GA.

3.5. Comparison of the Proposed Galactose Sensor With Published Galactose Sensors

Table 2 shows comparative study of the results of the present galactose biosensor with other reported galactose biosensors. The proposed galactose sensor based on the functionalised ZnO nanorods exhibits low limit of detection, fast time response, acceptable storage stability, high sensitivity with good linearity and also no response to common interferents. All these results reveal that the galactose sensor based on ZnO nanorods as a transducer, has enhanced performance on the activity of the galactose sensor by providing high surface to the enzyme molecules.

4. Conclusion

In this paper, we have constructed for the potentiometric galactose biosensor based on the immobilized ZnO nanorods with galactose oxidase in combination of the crosslinking molecule for the enzyme, using physical surface assimilation method for immobilization. The galactose biosensor had successfully demonstrated high stability, good linearity, better sensitivity, fast response time, and excellent selectivity towards galactose in the presence of common interferents. These all obtained results of the proposed biosensor indicate that this biosensor can be used for the monitoring of galactose in milk, food, and blood samples as well as for the clinical purpose.

Acknowledgments

The authors are thankful to International Science Programme (ISP), Uppsala University, Sweden and Royal University of Phnom Penh (RUPP), Cambodia, who supported this paper.

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Copyright © 2012 K. Khun 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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