Sensor For Detection Of Uric Acid Research Articles

Uricase biofunctionalized plasmonic sensor for uric acid detection with APTES-modified gold nanotopping

Current uric acid detection methodologies lack the requisite sensitivity and selectivity for point-of-care applications. Plasmonic sensors, while promising, demand refinement for improved performance. This work introduces a biofunctionalized sensor predicated on surface plasmon resonance to quantify uric acid within physiologically relevant concentration ranges. The sensor employs the covalent immobilization of uricase enzyme using 1-Ethyl-3-(3-dimethylaminopropyl)carbodiimide (EDC) and N-Hydroxysuccinimide (NHS) crosslinking agents, ensuring the durable adherence of the enzyme onto the sensor probe. Characterization through atomic force microscopy and Fourier transform infrared spectroscopy validate surface alterations. The Langmuir adsorption isotherm model elucidates binding kinetics, revealing a sensor binding affinity of 298.83 (mg/dL)−1, and a maximum adsorption capacity of approximately 1.0751°. The biofunctionalized sensor exhibits a sensitivity of 0.0755°/(mg/dL), a linear correlation coefficient of 0.8313, and a limit of detection of 0.095 mg/dL. Selectivity tests against potentially competing interferents like glucose, ascorbic acid, urea, D-cystine, and creatinine showcase a significant resonance angle shift of 1.1135° for uric acid compared to 0.1853° for interferents at the same concentration. Significantly, at a low uric acid concentration of 0.5 mg/dL, a distinct shift of 0.3706° was observed, setting it apart from the lower values noticed at higher concentrations for all typical interferent samples. The uricase enzyme significantly enhances plasmonic sensors for uric acid detection, showcasing a seamless integration of optical principles and biological recognition elements. These sensors hold promise as vital tools in clinical and point-of-care settings, offering transformative potential in biosensing technologies and the potential to revolutionize healthcare outcomes in biomedicine.

Black phosphorus nanosheets-based effective electrochemical sensor for uric acid detection

Black phosphorus nanosheets-based effective electrochemical sensor for uric acid detection

Rod-shaped units based cobalt(II) organic framework as an efficient electrochemical sensor for uric acid detection in serum

Benefits from the unique [Co3(COO)4(μ3-O)2]n rod-shaped units and aromatic π-conjugated ligand, a 3D cobalt(II) organic framework was selected to explore its potential as a uric acid (UA) electrochemical sensor by coating onto the glassy carbon electrode (GCE). By utilizing electrocatalytic oxidation effects, the prepared modified electrode of 1/CB/GCE shows remarkable electrochemical sensing performances for detecting UA in PBS solution (pH = 7) with high sensitivity, high selectivity, good recyclability, and low detection limit of 3.4 ppb. This work demonstrates MOF-based composite materials have great potentials in clinical medicine, thereby providing a new way to design and develop electrochemical biosensors.

Rod-Shaped Inorganic Sbus Based Cobalt(Ii) Organic Framework as an Efficient Electrochemical Sensor for Uric Acid Detection in Serum

Rod-Shaped Inorganic Sbus Based Cobalt(Ii) Organic Framework as an Efficient Electrochemical Sensor for Uric Acid Detection in Serum

Gold Nanoparticles and Uricase Functionalized Tapered Fiber Sensor for Uric Acid Detection

In this paper, a tapered optical fiber-based sensor is developed for the detection of uric acid (UA) in human serum. The fiber probes were fabricated using single-mode fiber (SMF) with taper diameter of $40~\mu \text{m}$ . The diameter of taper section has culminated on the basis of excretion of evanescent waves and their handling capacity. To enhance the sensitivity, taper section (sensing region) was immobilized with synthesized gold nanoparticles (AuNPs). The AuNPs were used to initiate the excitation of surface plasmons (SP) at the fiber surface and ultimately leads to the localized surface plasmon resonance (LSPR) phenomenon. The comparative studies were also done to analyze the effect of size of AuNPs by immobilizing the sensor probes with ~10 nm and ~30 nm size of AuNPs. The UV-Vis spectrophotometry, high resolution-transmission electron microscopy (HR-TEM) and scanning electron microscopy (SEM) were used for the characterization of AuNPs solution and developed sensor probes. The sensing ability of sensors was authenticated by recording the transmitted intensity of LSPR spectrum for a wide range of UA from $10~\mu \text{M}$ to $800~\mu \text{M}$ . The detected range of UA completely covers its concentration available in human serum that is from $150~\mu \text{M}$ to $420~\mu \text{M}$ . Thereafter, the wavelength shift in LSPR spectrums was evaluated to determine the sensitivity and detection limit of sensors. The selectivity of the sensor probe was enhanced by functionalizing it with uricase enzyme (0.672 U/ml). The specificity of uricase functionalized sensor probes were also analyzed in the presence of other biomolecules found in human-serum.

A novel electrochemical sensor for uric acid detection based on PCN/MWCNT

A simple, novel electrochemical sensing platform based on porous g-C3N4 (PCN) and multi-walled carbon nanotubes (MWCNTs) for the sensitive detection of uric acid (UA) has been proposed. The obtained PCN possessed good biocompatibility and large specific surface area with good dispersion, which was beneficial to electrocatalysis. The introduction of MWCNT as the conducting matrix improved the poor conductivity of PCN. Due to synergistic effect, the redox peak currents of UA substantially enhanced at PCN/MWCNT-modified electrode. The oxidation peak current exhibited linear responses to the concentration of UA in the range from 0.2 to 4 μM and 4 to 20 μM, and the limit of detection was calculated as 0.139 μM (signal-to-noise ratio of 3 (S/N = 3)). The sensor based on PCN/MWCNT-modified electrode was also successfully applied in human serums and also showed excellent selectivity, reproducibility, and stability. This work illustrated that the fabricated electrochemical sensor was promising for analytical applications.

Synthesis and characterization of α-Fe2O3/polyaniline nanotube composite as electrochemical sensor for uric acid detection

We report the synthesis of α-Fe2O3/polyaniline nanotube (PAn NTs) composite as an electrochemical sensor for uric acid (UA) detection. Field emission scanning electron microscopy (FESEM) indicates a hexagonal shape of the α-Fe2O3 while a nanotube morphology of the PAn. Impedance spectroscopy results confirm a significant decrease in the charge transfer resistance of the glassy carbon electrode (GCE) modified with α-Fe2O3/PAn NTs due to the presence of PAn NTs. The results show that the increase in the conductivity of α-Fe2O3 in the presence of PAnNTs could improve the catalytic performance of α-Fe2O3/PAn NTs composite, compared to the pure α-Fe2O3 nanoparticles. From differential pulse voltammetry, a linear working range for the concentration of UA between 0.01 µM and 5 µM, with a LOD of 0.038 µM (S/N = 3) was obtained. The sensitivity of the linear segment is 0.433 μA µM−1. The reliability of the modified electrode towards the detection of UA was investigated in the presence of interfering acids such as ascorbic acid, citric acid and succinic acid.

Development of Electrochemical Sensor for Uric Acid Detection in Intestinal Closed Loop

Uric acid is a ulitimate metabolite of purine nucleotides in humans, because the uricase had been lost completely. So, the serum uric acid level is higher than other mammalians. The advantage of the higher serum uric acid levels has been suggested to be antioxidant activity of uric acid. On the other hand, hyperuricemia is an abnormally high level of uric acid in the serum that leads to uric acid precipitation in tissues and the main risk factors for the onset of gout, hypertension, chronic kidney disease, atherosclerosis, diabetes and so on. There are two important physiological mechanisms caused hyperuricemia: (a) increase production of the uric acid from dietary and endogenous substrates that raise purine levels and (b) reduced renal and extra-renal excretion of uric acid. It is commonly accepted that two thirds of the urate is excreted from the kidney into urine. The remaining one third is excreted via extra-renal excretion, mainly intestine. Recently, importance of the uric acid excretion from intestine has been gathering attention because the considerable inpact of urate transporter function in the intestine on the serum uric acid level has been revealed gradually. A novel concept in hyperuricemia was proposed as “extra renal underexcretion type”.[1] Intestinal closed loop method is one of the basic techniques to investigate the excretion of uric acid via trasporters in intestin. However, it needs troublesome procedure and time consuming process. If it is possible to detect the concentration of excreted uric acid with electrochemical sensor, dynamic analysis of urate excretion via the urate transporters will easily be available. In this study, we developed an electrode to detect uric acid sensitively. Gold beads electrode was prepared according to the literature.[2] 6-Ferrocenyl-1-hexanethiol which works as a mediator for the uric acid oxidation was used to make self -assenbled monolayers (SAMs) on gold surface. 6-Hydroxyl-1-hexananethiol, 5-Carboxyl-1-pentanethiol and 6-Amino-1-hexanethiol were also used to construct mixed SAMs. Gold beads electrodes were soaked in the ethanol solution containing these alkanethiols. The SAM-coated electrode was used as working electrode (C.E: Pt wire, R.E.: Ag/AgCl). Uric acid dissolved in phosphate buffer (pH 7.4) was added to the measurement system. Cyclic voltammograms were measeured in buffer by addition of uric acid (-0.2 to +0.5 V). Oxdation current based on the uric acid oxidation was observed with 6-Ferrocenyl-1-hexanethiol modified electrode at around +0.45 V. The oxidation current was increased with increasing of uric acid concentration. When the mixed SAMs-coated electrodes were examined, similar responses were observed regardress the component of SAMs. However, no response was observed from the SAM-coated electrode without 6-Ferrocenyl-1-hexanethiol. Responsible change was observed at oxidation current by 0.1 mg/mL change of uric acid. Furthermore, ammperometric measurement showed the step-like current change according to the added uric acid concentration.