DISSERTATION
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Results and Discussion<br />
coiling on the surface due to their persistence length and flexible behavior. This leads to a steric<br />
hindrance towards the hybridization with target DNA. Thus, in the next step of the DNA sensor<br />
the build-up the ssDNA-modified surface is passivated using self-assembling properties of thiol<br />
molecules (Figure 3.6, c), as originally proposed by Tarlov et al. 74,75 . The formed thiol<br />
monolayer removes unspecifically adsorbed ssDNA from the electrode surface and forces<br />
grafted DNA to obtain an orientation that is more favorable for hybridization. It should be noted,<br />
that the DNA still does not obtain a perpendicular position with respect to the surface but rather<br />
lies down on the thiol layer due to its flexibility. Consequently, since the flux of the redox<br />
mediator to the electrode surface is facilitated, a decrease in Rct is commonly observed in EIS<br />
measurements upon the passivation step (Figure 3.8). On the other hand, tDNA can also<br />
unspecifically bind on the bare electrode surface (data not shown) and therefore this step is very<br />
important for preventing the unspecific adsorption of the target DNA and with this a false<br />
signal.<br />
Figure 3.7. Typical Nyquist plots representing the Rct increase upon ssDNA immobilization.<br />
ssDNA immobilization was performed in 10 mM PB with 450 mM K2SO4<br />
containing 1 µM ssDNA by incubation at 37 °C. EIS was measured in 10 mM PB with 20<br />
mM K2SO4 containing equimolar concentrations (5 mM) of K3[Fe(CN)6] and K4[Fe(CN)6].<br />
A DC potential of 220 mV was applied superimposed with a 5 mV AC perturbation. The<br />
frequency range was from 30 kHz to 10 mHz.<br />
3.2 Importance of knowing the surface 37