“…In fact, our method allows discriminating non-specific bindings with GRP, MYC, SCGB2A1, SCGB2A2, TOP2A and DT from the target TACSTD1, with a difference of 100 nA, approximately. Finally, the limit of detection of 0.05 nM represents a threefold improvement over previous similar work [19]. This low-density DNA sensor has the potential to be implemented in low cost miniaturized labon-a-chip systems capable of complex and real time measurements for point-of-care applications and pharmacological personalised therapies.…”
Section: Discussionmentioning
confidence: 82%
“…A crucial parameter in the performance of electrochemical DNA assays is the quality of the metal electrode used. The simplest approach to the formation of efficient DNA sensing surfaces consists in the self-assembly of thiolated DNA strands onto gold [19]. Gold is typically preferred due to its inertness and stability for DNA immobilization as well as wide electroanalytical potential working range.…”
The request of high specificity and selectivity sensors suitable for mass production is a constant demand in medical research. For applications in point-of-care diagnostics and therapy, there is a high demand for low cost and rapid sensing platforms. This paper describes the fabrication and functionalization of gold electrodes arrays for the detection of deoxyribonucleic acid (DNA) in printed circuit board (PCB) technology. The process can be implemented to produce efficiently a large number of biosensors. We report an electrolytic plating procedure to fabricate low-density gold microarrays on PCB suitable for electrochemical DNA detection in research fields such as cancer diagnostics or pharmacogenetics, where biosensors are usually targeted to detect a small number of genes. PCB technology allows producing high precision, fast and low cost microelectrodes. The surface of the microarray is functionalized with self-assembled monolayers of mercaptoundodecanoic acid or thiolated DNA. The PCB microarray is tested by cyclic voltammetry in presence of 5 mM of the redox probe K 3 Fe(CN 6 ) in 0.1 M KCl. The voltammograms prove the correct immobilization of both the alkanethiol systems. The sensor is tested for detecting relevant markers for breast cancer. Results for 5 nM of the target TACSTD1 against the complementary TACSTD1 and non-complementary GRP, MYC, SCGB2A1, SCGB2A2, TOP2A probes show a remarkable detection limit of 0.05 nM and a high specificity.
“…In fact, our method allows discriminating non-specific bindings with GRP, MYC, SCGB2A1, SCGB2A2, TOP2A and DT from the target TACSTD1, with a difference of 100 nA, approximately. Finally, the limit of detection of 0.05 nM represents a threefold improvement over previous similar work [19]. This low-density DNA sensor has the potential to be implemented in low cost miniaturized labon-a-chip systems capable of complex and real time measurements for point-of-care applications and pharmacological personalised therapies.…”
Section: Discussionmentioning
confidence: 82%
“…A crucial parameter in the performance of electrochemical DNA assays is the quality of the metal electrode used. The simplest approach to the formation of efficient DNA sensing surfaces consists in the self-assembly of thiolated DNA strands onto gold [19]. Gold is typically preferred due to its inertness and stability for DNA immobilization as well as wide electroanalytical potential working range.…”
The request of high specificity and selectivity sensors suitable for mass production is a constant demand in medical research. For applications in point-of-care diagnostics and therapy, there is a high demand for low cost and rapid sensing platforms. This paper describes the fabrication and functionalization of gold electrodes arrays for the detection of deoxyribonucleic acid (DNA) in printed circuit board (PCB) technology. The process can be implemented to produce efficiently a large number of biosensors. We report an electrolytic plating procedure to fabricate low-density gold microarrays on PCB suitable for electrochemical DNA detection in research fields such as cancer diagnostics or pharmacogenetics, where biosensors are usually targeted to detect a small number of genes. PCB technology allows producing high precision, fast and low cost microelectrodes. The surface of the microarray is functionalized with self-assembled monolayers of mercaptoundodecanoic acid or thiolated DNA. The PCB microarray is tested by cyclic voltammetry in presence of 5 mM of the redox probe K 3 Fe(CN 6 ) in 0.1 M KCl. The voltammograms prove the correct immobilization of both the alkanethiol systems. The sensor is tested for detecting relevant markers for breast cancer. Results for 5 nM of the target TACSTD1 against the complementary TACSTD1 and non-complementary GRP, MYC, SCGB2A1, SCGB2A2, TOP2A probes show a remarkable detection limit of 0.05 nM and a high specificity.
Nowadays, electrochemical biosensors are reliable analytical tools to determine a broad range of molecular analytes because of their simplicity, affordable cost, and compatibility with multiplexed and point-of-care strategies. There is an increasing demand to improve their sensitivity and selectivity, but also to provide electrochemical biosensors with important attributes such as near real-time and continuous monitoring in complex or denaturing media, or in vivo with minimal intervention to make them even more attractive and suitable for getting into the real world. Modification of biosensors surfaces with antibiofouling reagents, smart coupling with nanomaterials, and the advances experienced by folded-based biosensors have endowed bioelectroanalytical platforms with one or more of such attributes. With this background in mind, this review aims to give an updated and general overview of these technologies as well as to discuss the remarkable achievements arising from the development of electrochemical biosensors free of reagents, washing, or calibration steps, and/or with antifouling properties and the ability to perform continuous, real-time, and even in vivo operation in nearly autonomous way. The challenges to be faced and the next features that these devices may offer to continue impacting in fields closely related with essential aspects of people’s safety and health are also commented upon.
“…Following cleaning the electrodes were functionalised, via coself-assembling (Acero Joda et al, 2012;Henry et al, 2010;Joda et al, 2014) of the DNA thiolated probes (1 mM) and a spacer (Dithiol 16-(3,5-bis((6-mercaptohexyl)oxy) phenyl)-3,6,9,12,15-pentaoxahexa-decane), DT1, CAS# 936115-52-5, where the DT1 also serves to prevent non-specific binding (Civit et al, 2010), SensoPath Technologies, Bozeman, MT, USA) (100 mM) in 1 M KH 2 PO 4 and left to incubate for 3 h at room temperature within a humidified chamber. Subsequently, the electrode array was rinsed with Milli-Q water and dried with nitrogen gas.…”
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