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A procedure for the differential pulse voltammetric determination of NTZ at a screen-printed electrode surface modified with the ss-ds-DNA layer was also described.
The incorporation of Cl-IPBD into the DNA layers is tested here using a dual approach: (a) Differential Pulse (DP) or Square Wave (SW), as well as Alternating Current (AC) and impedance spectroscopy is used to monitor the redox activity of Cl-IPBD and (b) Alternating Current (AC) is used to detect the Cl-IPBD condensation via capacitative/resistive (C/R) mode.
In our hypothesis, this variation in optical signal is due to the interference between visible light reflected from surface of the Au electrode and DNA layer, which is in accordance with a previous research [34].
Since the initial accumulation of the pUC19 plasmid in the electrode layer has been detected in a 'label-free' procedure, i.e. without the addition of the redox probe, then the electroactive compound under investigation, accumulated in the DNA layer, can be, in fact, regarded as an actual redox probe and tested.
After centrifugation again, the aqueous layer was transferred into new tubes, and DNA was precipitated and washed.
This new redox-active layer was applied for the construction of the DNA biosensor.
The clear aqueous layer was transferred to a tube and the DNA precipitated in 2 volumes of ethanol.
DNA tetrahedron molecular layer is designed on the interface of a gold working electrode, which provides the recognition element for PSA capture.
layer was collected.
The additional catalase (Cat) layers assembled into the films could effectively protect the DNA from damage by decomposing the H2O2 produced in situ, and only when the Cat layers were located in close proximity to the GOD layers, the protection of DNA in the inner layers was most effective.
The buffy coat layer is stored for future DNA extraction.
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