Surface Charge Density Dependent DNA
Capture through Polymer Planar Nanopores
Fabricated by NIL
Junseo Choi, Zheng Jia, and Sunggook Park*
Department of Mechanical & Industrial Engineering andCenter for BioModular Multiscale Systems for Precision Medicine
Louisiana State University
Baton Rouge, LA USA 70803
E-mail: sunggook@lsu.edu

Nanopore-based fluidic devices are considered as a promising tool for DNA sensing due totheir label-free, high-throughput, and low-cost features [1]. The sensing mechanism is simple:
when a negatively charged DNA molecule passes a nanopore filled with electrolyte, ion
transport through the nanopore is temporarily blocked, resulting in a transient current signal
as a molecular signature. The nanopore-based DNA sensing platforms can be classified into
two categories: biological nanopores and solid-state nanopores which have their own
advantages and disadvantages [2]. However, regardless of the kinds of nanopore sensing
platforms used, efficient capture of DNA molecules into nanopores is the basic but
challenging operational requirement [3]. Among several factors for improving DNA capturein nanopore-based sensing platforms, controlling surface charge density of nanopore walls is
the most effective approach for polymer-based solid-state nanopores because of theavailability of different polymers.
In this work, we will study the effect of surface charge density on the capture of doublestranded (ds) DNA molecules into a polymer planar nanopore numerically andexperimentally. First, we simulated the effective driving force (Feff) for the translocation of a
dsDNA through a planar nanopore with different sizes and surface charge densities (Figure1). The simulation results were then verified by performing dsDNA translocation experiments
using a planar nanopore with 10 nm equivalent diameter imprinted on three polymer
substrates having different surface charge densities, e.g. poly(ethylene glycol) diacrylate(PEGDA), poly(methyl methacrylate) (PMMA), and cyclic olefin copolymer (COC) by using
nanoimprint lithography (NIL) and thermal bonding (Figure 2). A Si master mold wasprepared via a combination of photolithography and focused ion beam milling, which wasreplicated into two different UV resins (e.g. hydrophobic PFPE (Fluorolink MD 700) for
imprinting PEGDA and tri(propylene glycol) diacrylate (TPGDA) for imprinting PMMA andCOC) on a PET backbone substrate by using UV-NIL. Using the resin molds, PEGDA wasUV-imprinted by exposing to flash-type UV light (250−400 nm) for 1 min at an intensity of∼1.8 W/cm2. PMMA and COC were thermally imprinted at 135 °C, 3.5 MPa and 160 °C, 5MPa for 15 min, respectively. For bonding at 70 °C, 1 MPa for 15 min, a thin COC sheet withlow Tg (Tg = 78°C) was used as a cover plate for all three planar nanopore substrates. Then,lambda-DNA was electrically driven through the bonded substrates in order to study lambdaDNA capture through the planar nanopores.

Reference:[1] Haque, F.; Li, J.; Wu, H.-C.; Liang, X.-J.; Guo, P.; “Solid-State and Biological Nanopore
for Real-Time Sensing of Single Chemical and Sequencing of DNA” Nano Today 2013, 8,56-74.
[2] Dekker, C.; “Solid-State Nanopores” Nat. Nanotechnol. 2007, 2, 209-215.
[3] He, Y.; Tsutsui, M.; Fan, C.; Taniguchi, M.; Kawai, T.; “Gate Manipulation of DNA
Capture into Nanopores” ACS Nano 2011, 5, 8391-8397.

Figure 1. Simulated effective driving force (Feff) for a rod-shaped DNA located at the mouth ofnanopores with different pore sizes and various surface charge densities.

Figure 2. SEM images of Si master mold (a, e) and imprinted planar nanopore on PEGDA (b, f),PMMA (c, g), and COC (d, h) substrates. The scale bars are 3 µm in white and 100 nm in red.