Document Type : Research Paper
1 bPharmacology and Toxicology Department, Faculty of Pharmacy, Tabriz University of Medical Sciences, Tabriz, Iran
2 aResearch Center for Pharmaceutical Nanotechnology, bPharmacology and Toxicology Department, Faculty of Pharmacy, Tabriz University of Medical Sciences, Tabriz, Iran
3 Research Center for Pharmaceutical Nanotechnology,
The pH of biological samples may be considered as one of the main problems in the analytical experiments. The saliva has a pH in 6.0 to 7.0 ranges; the pH of the small intestine is acidic because of hydrochloric acid secretion in the stomach, and the large intestine has a pH of about 8.0. The pH of the body fluids, especially urine, can also be affected by different conditions and unwanted contaminations. For example, substances such as drugs, food elements and drinks influence the pH of urine and result in complications in the analytical determinations [1-6]. Therefore, in the sensor fabrication, the pH independency could be considered as a main point, and designing a pH independent biosensor would be a big progress in this field.
Novel aptamer-based sensors (aptasensors) have been introduced as a good candidate for this subject. Aptasensors are a kind of affinity based biosensors that use aptamers as recognition elements. Among optical, electrochemical, and other approaches, electrochemical based aptasensors attract a lot of interest as useful methods because of their low cost, accuracy, sensitivity and simplicity [7-12]. In the electrochemical approaches, the electro-active redox molecules have been used as the transducer part in several different ways, i.e. label free, biomolecule-attached, or surface-attached . Biomolecule-attached redox molecules are very common in biosensor designing and ferrocene is used as the most popular redox molecule in this field [14-18]. However, the instability of the ferrocenium ion in the strong nucleophilic reagents and chloride containing buffer solutions is one of the main problems related this molecule [14, 19, 20]. Therefore, the quinine derivatives were proposed as an alternative biomolecular-attached redox species . Since, the quinine derivatives show electro-activity in a wide range of pH [22, 23], these redox molecules may be able to solve the mentioned problems simultaneously: (1) using a sensor for a specific target in different pH ranges; (2) and in the chloride containing buffers without any intervention with the contents. Juglone, a 5-hydroxy derivative of 1,4- naphthoquinone, is a natural electro-active quinine that is used as a surface attached redox molecule in several studies by us and others [16, 24, 25]. In this study the potential usage of Juglone as an attached redox molecule in different concentration of chloride containing buffers has been investigated and the ability of the fabricated sensor in the different pH ranges was also tested.
2. Materials and methods
Codeine phosphate (99%) was provided from Temad Company, Tehran, Iran. 6-Mercaptohexanol (97%) was purchased from Sigma-Aldrich, Germany. N-hydroxysuccinimide (≥99%), 3-mercaptopropionic acid (≥98%) and 3-Mercaptopropionic acid (3-MPA) synthesis grade were purchased from Merck, Germany. N-(3-dimethylaminopropyl)- N'-ethylcarbodiimide hydrochloride (EDC) and 5-Hydroxy- 1,4-naphthoquinone (97%; Juglone) were supplied by Acros, Belgium, and were used without further purification. The specific RNA-aptamer sequence for codeine  (5'-SHC6-GGG ACA GGG CUA GCU UAG UGC UAU GUG AGA AAA GGG UGU GGG GGC7NH2- 3') was synthesized by Microsynth, Switzerland, with a C6 aliphatic thiol and a C7 primary aliphatic amin modifications in the 5' and 3' termini, respectively.
2.2. Buffer preparations
A range of buffers and aqueous solutions were prepared during the work. For preparing the phosphate buffer in different pH ranges, a mixture of monobasic dihydrogen phosphate (KH2PO4) and dibasic monohydrogen phosphate (K2HPO4) were used. A 1 M stock solutions of KH2PO4 and K2HPO4 were made separately by sterile deionized water (with 0.05 μs/cm electrical conductivity) at 25 ºC. Then, the appropriate volumes of these solutions were mixed and diluted to 1 liter by sterile deionized water to reach to a 0.1 M desire phosphate buffer. The ratio of the needed KH2PO4 and K2HPO4 solutions was calculated by the Henderson-Hasselbalch equation [27-29]. For accurate adjusting of the pH, 1 M HCl and 3 M NaOH solutions were used.
Figure 1. The aptasensor was tested against 10 μM codeine phosphate (Metrohm Autolab 302N potentiometer output) in the presence of different concentrations of NaCl. a: 0.0, b: 0.1 M, c: 0.2 M, d: 0.5 M, e: 1.0 M, and f: 2.0 M.
2.3. Instrumentation and procedures
Electrochemical measurements were performed by a Metrohm Autolab 302N Potentiostats-Galvanostats (The Netherlands). An Ag/AgCl/KCl 3 M reference electrode, a2 mm diameter gold disk working electrode (purchased from Azar Electrode Co., Iran) and a platinum wire auxiliary electrode were used as customary electrodes in electrochem- ical experiments. The NOVA software (version 1.5, Eco Chemie BV, The Netherlands) was used for controlling the electrochemical procedures. All the electro- chemical experiments were performed at room temperature and in the 50 ml of 0.1 M phosphate buffer solution (PBS). The pH of all buffers and aqueous solutions were controlled by a Metrohm Autolab 827 pH lab pH meter (The Netherlands).
2.4. Preparing the electrode for electrochem- ical experiments
The impurities were removed by physical and electrochemical polishing of the working electrode for efficient immobilization of aptamer on the surface of the electrode [14,16, 30, 31]. Then, A 50 µl volume of 5 µM modified RNA-aptamer was placed on the surface of polished electrode to form a monolayer of 5'-thiolated aptamer on the gold surface by self-assembling procedure for 18 h . In the next step, the electrode was rinsed by the phosphate buffer (pH 7.0) several times to remove residues from the surface and make ready for the redox attachment. The preparation of the redox molecule, N-hydroxysuccinimide ester of β[(5-hydroxy–1,4-naphthoquinonyl) thio]propionic acid (Jug-PE), was performed by the previously reported procedure . Then, the molecule was attached to the 3'-amin- modified terminus of the aptamer followed by treating with 2 mM 1-mercaptohexanol for two h [14, 15, 25]. In this stage, the electrode was ready and immediately used in experiments.
3.1. Effect of ionic strength on the aptasensor's response
The effect of the ionic strength of the buffers on the cyclic voltammetry (CV) scan of Juglone was studied by taking and comparing the cyclic voltammetry scans in the potential range of +0.4 to +0.9 V and the scan rate of 0.15 V/s in the 0.1 M PBS containing 10 µM codeine phosphate in the presence of NaCl concentrations of 0.0, 0.1,0.2, 0.5, 1, and 2 M (Figure 1). The maximum faradic currents of working electrode obtained were 5.75 µA, 8.56 µA, 11.5 µA, 19.5 µA,39.7 µA, and 87.2 µA, respectively (Figure 2). The obtained data show a significant relation between the ionic strength of the buffer and the faradic current of working electrode.
Figure 2. The aptasensor response to the different concentrations of NaCl. The maximum faradic currents of working electrode were obtained 5.75 μA, 8.56 μA, 11.5 μA, 19.5 μA, 39.7 μA, and 87.2 μA in the presence of 0.0, 0.1 M, 0.2 M, 0.5 M, 1.0 M, and 2.0 M NaCl respectively. The data show almost a linear relation between the NaCl concentration and faradic current of working electrode.
3.2. Effect of different concentrations of codeine phosphate on the response of aptasensor
The fabricated aptasensor was treated by the different concentrations of codeine phosphate (CP) to investigate the behavior of the sensor in the presence of its target. First, a background cyclic voltammetry scan was taken in 0.1 M PBS containing 2 M NaCl in the potential range of +0.4 to +0.9 V and the scan rate of 0.15 V/s. Then, the main scans were taken in the same condition in the presence of 10 nM, 50 nM, 100 nM, 500 nM, and 1000 nM of CP. The obtained data represent significant changes in the maximum faradic current of working electrode by increasing the CP concentration. In the presence of 10 nM of CP, an 11.4 μA faradic current was observed on the working electrode's voltammogram. Similarly, the 19.5 μA, 34.9 μA, 48.7 μA, and 75.5 μA faradic currents were observed, respectively, by adding 50 nM, 100 nM, 500 nM, and 1000 nM of CP to the medium (Figure 3). Based on the obtained data, it can be shown that the aptasensor shows a linear response to increasing concentrations of its specific target.
3.3. Effect of pH on the sensor's response
The ability of the aptasensor for CP detection in a wider range of pH was investigated by taking cyclic voltammetry scans in the presence of a high concentration of CP (10 μM). The background CV scan was taken in 0.1 M PBS containing 2 M NaCl and the main scan was performed in the same condition in the presence of CP. The electrochemical experiments were performed in the 5.5, 6.0, 6.5, 7.0, 7.5, 8.0, 8.5, and 9.0 pH ranges. The CV of the working electrode did not show the expected reduction and oxidationpeaks of aptamer-attached Juglone in the 5.5 and 6.0 pH ranges. The reduction and oxidation peaks of Juglone were appeared in pH 6.5, and a 35.42 μA faradic current of working electrode was observed. In pH 7.0, the sharpest oxidation and reduction peaks were observed and the maximum faradic current of working electrode reaches to 87.19 μA. By increasing the pH to 7.5, 8.0, 8.5, and 9.0, the maximum currents of working electrode produced were 77.61 μA, 73.79 μA, 35.98 μA, and 7.66 μA, respectively (Figure 4). The obtained data showed that the faradic current of the working electrode (i.e. sensitivity of the sensor) also started to reduce by rising pH. It means that, aptamer attached Juglone can only reach its maximum working sensitivity at pH 7.0.
According to the obtained data, the maximum faradic current of working electrode has been increased by increasing the ionic strengths in the medium . Although the adequate ionic strength of buffers is an essential parameter for electrochemical experiments , there are some limitations for the presence of large ionic concentrations in electrochemical based aptasensors. The high ionic environments could reduce the electrochemical responses of aptasensors via two main mechanisms. The aptamer-target complex forms by the electrostatic interactions, Van der Waals forces, hydrogen bonding, or a combination of these effect between aptamer and its own target [34-38].
Also, the aptamer folding is being formed by pairing the organic bases with the hydrogen bonding . Since, the concentrated ionic solution affects these forces [40, 41], the affinity of the aptamer to its target may be reduced because of two problems: (1) the organic bases could not pair completely and this phenomenon affects the complete folding of the aptamer. The unfolded aptamer could not have an effective affinity to its own target and this may lead to a reduction in the response of aptasensors [8, 14-16]. (2) The same effects may also reduce the affinity of the aptamer (if not affected) towards the target in high salt concentrations. By reducing the folding status of aptamer and aptamer-target complex formation, the faradic current of the working electrode decreases and the sensor would not work correctly. In brief, increasing the ionic concentration of buffers can have some limitations for electrochemical based aptasensors and these limitations are independent from the redox molecule. The response of the fabricated sensor to different concentration of the codeine had been described by the previously published mechanism . In the presence of higher concentrations of codeine, more complexes of aptamertarget are being formed and the faradic current of working electrode increases. The increase in response continues to reach a plateau which indicates the saturation of all immobilized aptamers by the target molecules. In another word, the fabricated aptasensor shows a linear response to the presence of different concentrations of its own target, i.e. codeine (Figure 3).
Figure 3. The fabricated aptasensor was used for detection of different concentrations of codeine. The obtained data demonstrated the linear response of sensor to the presence of its own target.
As mentioned before, pH is an important problem in the analytical experiments. The obtained data show that the sensor works accurately only at 7.0 to 8.0 pH ranges. Despite of Juglone ability to show electroactivity in a wide range of pH [22, 23], the aptasensor did not showed enough sensitivity. This phenomenon may occurred by the influence of pH not only on the aptamertarget complex formation but also on the aptamer folding. However, the quinone based redox molecules have potential usage in a wide pH ranges and more experiments with different molecules are needed to be done in future works [22, 23].
Despite of the sensitivity of the aptasensors to large concentration of ions in the environment, the Juglone was used successfully in a 2 M NaCl containing PBS buffer. Therefore, the ability of this redox molecule in a high chloride containing solution is a considerable result. As mentioned before, Ferrocene which is a chloride sensitive redox molecule, can be replaced by Juglone as an appropriate alternative attached redox molecule in the RNA or DNA-based biosensors for usage in the chloride containing buffers and solutions. Another main point is the pH dependency of the aptamer folding and aptamer-target complex formation, and should be considered more carefully in selecting redox molecules for aptasensor designing.
Figure 4. The effect of pH on the response of the aptasensor. The aptasensor was used to detect codeine in the different pH ranges, i.e. 5.5 to 9.0. The obtained data show an optimum response of the sensor only in pH range of 7- 8.
The authors would like to thank the Research Center for Pharmaceutical Nanotechnology and vice chancellor for research of Tabriz University of medical sciences, IRAN, for financially supporting this project as a part of Ph.D. thesis (Mehdi Saberian). Also we would like to thank Exir Pharmaceutical Co., IRAN, for providing codeine phosphate.