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ISSN: 2155-6210
Journal of Biosensors & Bioelectronics
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In-Flow DNA Extraction Using on-Chip Microfluidic Amino-Coated Silicon Micropillar Array Filter

Hanaa M Hegab1,2,3,4*, Soliman M3, Ebrahim S3 and Op de Beeck M2

1KACST-Intel Consortium Center of Excellence in Nano-manufacturing Applications (CENA), Riyadh, Saudi Arabia

2Imec, Kapeldreef 75, Leuven, Belgium

3Institute of Graduate Studies and Research, Alexandria University, Alexandria, Egypt

4Institute of Advanced Technology and New Materials, City of Scientific Research andTechnological Applications, Borg Elarab, Alexandria, Egypt

*Corresponding Author:
Hanaa M Hegab
IMEC, Kapeldreef 75
Leuven, Belgium
Tel: +32488694814
E-mail: [email protected]

Received Date: July 28, 2013; Accepted Date: August 29, 2013; Published Date: September 05, 2013

Citation: Hegab HM, Soliman M, Ebrahim S, Op de Beeck M (2013) In-Flow DNA Extraction Using on-Chip Microfluidic Amino-Coated Silicon Micropillar Array Filter. J Biosens Bioelectron 4:140. doi: 10.4172/2155-6210.1000140

Copyright: © 2013 Hegab HM, et al. This is an open-access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.

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Keywords

Micropillar filter; DNA extraction on chip; APTES; Continuous flow

Introduction

The prospect for the commercialization of microfluidic LOC systems has powered over the recent decade, in particular for medical and the life science diagnostic applications. This development has been prompted by creating massive surface area such as integrated architectures, and extremely functional lab-on-a-chip technologies [1]. Towards commercialization, there is a need for economic manufacture which involves optimized cost for materials and high affinity for DNA separation for a range of back-end processing steps, such as surface modification of solid phase integrated architectures. The development of micro total DNA analysis systems (μTAS) has shown a large potential to integrate sample preparation and target amplification as well as detection in a single disposable cartridge. The DNA extraction step has been shown to play an important role in various subsequent analysis steps, including Polymerase Chain Reactions (PCR) [2], DNA hybridization [3], DNA biosensors [4], capillary electrophoresis [5], etc. Despite its importance and a plethora of available DNA extraction techniques, new methods to further simplify DNA extraction directly on chip are still needed, specially, as many methods use reagents or operational steps that are not compatible with standard microfluidic devices. For example, traditional chemical DNA extraction techniques entail the use of centrifugation and organic solvents to purify DNA.

Microfluidics Solid Phase Extraction (SPE) methods may provide an alternative to traditional DNA extraction methods, allowing for more rapid and straightforward on-chip sample preparation. Most SPE methods use silica as the solid phase, with chaotropic salts to bind DNA. Some researchers used micropillar chip to purify DNA from a whole blood sample, based on chaotropic salts [6]. High concentrations of chaotropic salts are, however, often difficult to remove from the sample and may inhibit following PCR reactions or other molecular techniques [7]. A possible solution was provided by Melzak et al. [8] where it was shown that after DNA binding to silica in the presence of chaotropic salts, elution at a low ionic strength could be achieved. Additionally, micro-sized SPE methods come with a number of additional inherent advantages, such as compact reagent consumption, avoidance of cross-contamination, and the possibility of direct integration with downstream methods like PCR, detection or electrophoretic separation [9-12].

Silica has been utilized in micro-scale devices to extract DNA from complex biological samples with volumes on the order of tens of microliters [13]. Some other efforts to miniaturize DNA extraction by providing a large surface area to volume ratio has been described using silica resins or beads in a capillary system [14]. Other systems included micro-fabricated silica pillars to increase the surface area within the micro-channel by 300–600% [15]. Although the binding capacity in such micro-chip reached approximately 82 ng/cm2, the elution was limited to only 10% of loaded-DNA. To solve this issue, another researcher used functionalization of micro- or nanoparticles to provide massive active surface areas [16-18]. Recently, a bead-packed microfluidic device with a built-in flexible wall was developed by Hwang et al. [19] to automate extraction of nucleic acids from Methicillin-Resistant Staphylococcus aureus (MRSA) in nasal swabs. A flexible PolyDiMethylsiloxane (PDMS) membrane was designed to manipulate the Surface-to-Volume Ratio (SVR) using positively charged polyethylene imine PEI coated beads-packed chambers. That device captured DNA electrostatically in the range of 0.05-0.15 μm-1 and demonstrated a typical SPE protocol composed of binding, washing, and eluting. Mixing by asynchronous membrane vibration during the eluting step enabled ca. 90% DNA recovery with ca. 10 μl of liquid solution from the captured cells on the bead surfaces.

Although the effectiveness of APTES in immobilizing DNA has been demonstrated and studied by many researchers on different devices [20], to the best of our knowledge, the work presented here is the first attempt to coat a glass-bonded μPFchip with APTES and use it in demonstrating successful extraction of bacteriophage lambda DNA (λDNA), as a preliminary step towards DNA extraction from blood. The use of the pre-purified λDNA at this stage stemmed from the need to determine the purification efficiency of amino-coated μPF with high accuracy. In this study, μPF chips were fabricated for the purpose of DNA extraction under continuous flow conditions. The filters were made out of silicon and coated with APTES in-flow pass. The binding efficiency of such amino-coated μPF was investigated and compared to the efficiency of uncoated filters under the same conditions. In addition, we propose a simple and effective washing and eluting steps based on using pure water at 80°C, which allows direct detection of collected DNA using UV Nano-Droplet without the need of fluorescence intercalating dyes and fluorescence measurement tools, as is common when using chaotropic salts or eluting DNA with high concentrated buffers.

Materials and Methods

Materials and experimental consideration

In this study, used bacteriophage lambda DNA (λDNA) was purchased from Invitrogen (Carlsbad, CA). Sulfuric acid (98% v/v) and hydrogen peroxide (30% v/v) were obtained from Fluka (USA), while all other reagents, including 3 aminopropyltriethoxysilane (APTES) and Sybr Green dye were purchased from Sigma-Aldrich (USA). The 150 mM phosphate buffer solution (PB) pH 7.4 was prepared in the lab prior to use.

The μPF was fabricated using Deep Reactive Ion Etching (DRIE), as described earlier [21]. The μPF was sealed by a Pyrex glass wafer using anodic bonding. In this work only micropillar filters with a pillar diameter of 15 μm and an inter-pillar distance of 5 μm were used. The filter channels were 4.3 mm wide and 7.3 mm long and contained a regular array of 43,000 pillars, each pillar being 300 μm high. Hence pillar filter has a total surface area of 6.6 cm2 and a total volume of 4.9 μl. The microstructure of the fabricated filter was imaged using scanning electron microscope, as depicted in Figure 1.The experimental setup requires the filter to be clamped between aluminum plates and connected to a syringe pump [NE-1010, Pro sense (withdraw type). B.V, USA] using fused silica capillaries of 280 μm inner diameter. These capillaries were connected to the filters by means of Nano Tight™ unions and fittings. The set-up is shown in Figure 2. To control the injection and withdraw of a certain volume, a well-controlled injection loop was utilized. To switch between injection, washing or elution fluid, a rotational valve (Lab smith MV201-T116, USA) was used.

biosensors-bioelectronics-micropillar

Figure 1: (A) A micropillar filter chip image which contains three devices, filter 2 was used for this experiment being 4300 μm wide, 7300 μm long and 300 μm deep. (B) Scanning electron microscope images of the Si μPF fabricated using deep reactive ion etch, showing a tilted view of the cylinder-shaped micropillars and (C) a magnified view of micropillars array.

biosensors-bioelectronics-continuous

Figure 2: Real and schematic diagram of the continuous flow DNA purification set-up using the μPF chip.

Modification of μPF surface with APTES

Filters were cleaned with piranha (3H2SO4: 1H2O2) and dried on a hot plate at 110°C for 15 minutes before silanization. That particular piranha clean step was applied to all filters used in this work, including the uncoated filter. The silanization protocol used was an optimized surface modification process for DNA capture and release [22]. Based on that study, a 50 μl of APTES solution in water (3 v/v %) was injected into the μPF at a flow rate of 1 μl min-1 and then the filter surface was silanized for 30 min. The μPF was then washed twice with deionized water to remove any unbounded APTES. After washing, the filters were cured at 80°C for 4 hours then allowed to cool down to room temperature before use.

Characterization of μPF performance

To assess the μPF performance, λDNA was captured and eluted after washing using a continuous flow process. To introduce the DNA into the μPF filter, a sample loop of 10 μl was filled with purified λDNA, with concentrations ranging from 25-300 ng/μl dissolved in 150 mM PB (pH 7.4), i.e. the total initial DNA loading ranged between 250-3000 ng for the various tests performed. For the DNA capturing step, the full content of the sample loop was injected inside the filter from the entrance side and collected at the exit side, in order to determine the amount of λDNA that was not trapped. Afterwards, the μPF chip was rinsed with 25 μl PBS, and eluents were collected, to determine the amount of λDNA eluted during this washing step. Finally, to elute the captured λDNA, the elution loop was loaded with water at 80°C using flow rate of 100 μl/min via the withdraw option on the automatic syringe pump (time elapsed=15 sec), then 25 μl of water at 80°C was flushed through the filter with flow rate of 50 μl/min and again, λDNA aliquots were collected (see Figure 2). It should be emphasized that neither the water temperature inside the capillary nor at the exit of the μPF are known. Due to the good thermal conductivity of the silicon substrate, it is likely that temperature slightly drops below 80°C during the process. In addition to evaluating the filters using various λDNA loadings, also flow rate variations ranging from 5-50 μl/min were examined.

Fluorescence detection using UV inverted microscopy was utilized to visualize the λDNA during the extraction process. Taking advantage of the transparent anodic bonded glass side of μPF, the chip was sandwiched between an inverted microscope camera and a flexible aluminum holder, in order to capture images of λDNA extraction inside the μPF after injection, washing and elution steps. To stain the λDNA sample, Syber Green dye with dilution of 1:10,000 was used. It is recommended to keep the solution with diluted dye in the freezer overnight and keep it away from direct light prior to usage.

To highlight the benefits of the APTES coating, an uncoated μPF was also included in the study and was tested with the highest DNA initial loading (i.e., 3000 ng). It should be noted that the uncoated μPF was also cleaned with piranha (3H2SO4: 1H2O2) and dried on a hot plate at 110°C for 15 minutes before exposure to λDNA. For all collected samples (unbound, washed and eluted fractions) the λDNA concentrations were determined by UV measurements (Nano-Droplet 2000, Thermo Scientific).

Results

Fluorescence visualization of λDNA extraction

By examining the fluorescence intensity from the images of injected stained sample, obtained by inverted microscope, one can assess whether the DNA was trapped or not. For example, if the fluorescence intensity remains the same after washing this indicates DNA trapping. The inverted microscope images of the injected stained sample indicate that the amino coated μPF trapped most of the λDNA, as shown in Figure 3, for the test with 500 ng λDNA loading of the injection fluid. After washing the μPF with 25 μl PB, almost the same fluorescence intensity level was observed, as indicated in Figure 3B, which proves that the λDNA is trapped by the μPF. However, after flowing 12.5 μl of water at 80ºC through the μPF, most of the λDNA was eluted, as shown in Figure 3C and Figure 3D, depicting the reduction in fluorescence intensity after a partial elution step. This demonstrates the possibility of achieving complete elution of the captured λDNA by merely using water at 80°C.

biosensors-bioelectronics-Inverted

Figure 3: Inverted microscope (IM) image of Syber Green stained λDNA trapped to amino coated μPF (A) after injection step, (B) after a washing step with 25 μl PB, (C) after a first elution step with 12.5 μl of water at 80°C, and (D) after a second elution step with 12.5 μl of water at 80°C.

Effect of flow rate

Figure 4 illustrates the influence of sample flow rate on the purification profile of DNA using amino-coated μPF with various initial DNA loading. For each initial DNA loading tested, the nontrapped, washed and eluted concentration of DNA collected upon exiting the μPF is determined and plotted. For comparison, tests are also performed on an uncoated μPF, using an initial DNA loading of 2000 ng. The measurements of the corresponding DNA concentrations during the various stages of the DNA extraction process using the uncoated μPF are plotted in Figure 4F.

biosensors-bioelectronics-Purification

Figure 4: Purification profile of DNA using an amino-coated μPF as a function of flow rate corresponding to an initial loading of (A) 250 ng, (B) 500 ng, (C) 1000 ng, (D) 2000 ng, (E) 3000 ng. For comparison, the performance of an uncoated μPF using 2000 ng of intial DNA loading is shown in (F). Columns represent (left to right) the initial, non-trapped, washed and eluted DNA fragments from μPF during purification process.

It can clearly be seen that the effect of flow rate on the concentration of collected non-trapped DNA is limited (higher flow rate gives only slightly higher amount of non-trapped DNA) when the initial amount of introduced DNA is lower than ~1000 ng. Remarkably, for DNA loading ~2000 ng and higher, the flow rate influence on nontrapped DNA becomes more important. In such case, the amount of collected non-trapped DNA is about 50% of the amount present in the introduced sample, regardless of the flow rate. This may suggest that a level of saturation has been reached. Hence the amount of introduced DNA is divided between a portion strongly captured by the filter and another that is loosely attached to other surfaces on the filter. While the loosely attached DNA is removed during the washing step, the captured DNA is collected only during the final elution step. As expected, for the uncoated filter, the amount of washed DNA is quite high, indicative of lack of strong binding between the DNA and the filter, as reflected in Figure 4F. Comparing the results using an amino-coated and uncoated filter with same initial DNA loading (Figures 4D and 4F, respectively),it is obvious that the majority of the DNA is bound successfully to the coated μPF surfaces and is collected only during the elution step. Although the flow rate has no important influence on the DNA trapping, it has a clear influence on final DNA elution. For all initial DNA loadings, a higher flow rate results in more DNA loss during the washing step, which results in a smaller DNA collection during the final elution step. This effect is seen for both, amino-coated and uncoated filters. So the so-called ‘DNA capture efficiency’ is clearly dependent on flow rate. For a fixed initial λDNA amount, this dependence of capture efficiency on flow rate was investigated in more detail, with flow rates ranging from 5-50 μl/min. As can be clearly deducted from Figure 5, the capture efficiency is significantly higher with lower flow rate. This effect is more pronounced when higher initial DNA loadings are applied. For example, at 2000 ng of initial λDNA loading and a flow rate of 5 μl/min, the capture efficiency for the coated and uncoated μPF decreased from 52 to 23% and from 18 to 3%, respectively, compared to that measured at the low flow rate of 50 μl/min, as shown in Figure 6. Similar to the capture efficiency trend with the flow rate, the elution recovery % is significantly decreasing with increasing the flow rate over the tested range, as shown in Figure 7. The trend is also a strong function of the initial DNA loading.

biosensors-bioelectronics-loading

Figure 5: The effect of different loading flow rates (5, 10, 20 and 50 μl /min) on captured DNA efficiency using an amino-coated μPF and an uncoated filter (results with label ‘2000 ng blank’). Various initial DNA concentrations are tested as indicated in the legend.

biosensors-bioelectronics-purified

Figure 6: Purification profile of pre-purified DNA (2000 ng initial loading) using coated (blue) and uncoated (black) μPF as a function of loading flow rate.

biosensors-bioelectronics-function

Figure 7: DNA elution recovery % profile of pre-purified DNA using aminocoated μPF as a function of flow rate.

Effect of initial λ DNA loading

As portrayed in Figure 4, the captured amount of λDNA by the amino-coated μPF is proportional to the initial λDNA loading (ng). In Figure 8, the amount of captured DNA is plotted versus the initial DNA loading of the injected samples, for various flow rates. The graphs show clearly that lower flow rates give better filtering results for all initial DNA loadings. Furthermore, the results strongly suggest that a saturation in filtering efficiency exists; the curves in Figure 8 all show initially a strong increase in captured DNA with increasing DNA loading, but a clear flattening occurs for higher DNA loadings. Based on the tested range of initial DNA amounts, the saturation of the filter is estimated to be ~1229 ± 42 ng for in-flow rate of 5 μl/min. High loading levels of DNA are likely to be flushed away without adhering to the filter surface probably due to the DNA capturing saturation of the pillar surface, as described before in this study.

biosensors-bioelectronics-amino

Figure 8: Amount of captured DNA using amino-coated μPF versus initial DNA loading. Each curve is labeled with the flow rate used. For filtering with 5μl/min flow rate, the saturation region of filter efficiency, being around 3000 ng, is clearly visible.

Considering the effect of the flow rate and its relation to DNA loading, samples with smaller amounts of DNA are better suited for extraction by the amino-coated μPF. The combination of low initial loading levels and low flow rates (such as 5 and 10 μl/min) greatly enhances the probability of DNA adhering to available APTES molecules, resulting in much better results. A compromise between the initial DNA loading and flow rate is to be made according to the specific experimental conditions being employed. The difference of the amount of DNA captured in APTES-coated and uncoated μPF was was consistent with the presence of amino groups introduced on the surface during filter coating. Therefore these results suggest that DNA collection, based on electrostatic interaction between positive charge of APTES amino group and negative charge of DNA sample, was successfully achieved.

Discussion

In this study, the fabricated and tested μPF features pillars have a remarkably high aspect ratio, resulting in pillars of 300 μm high. This drastically increased the total pillar surface area of the filter from 0.07 cm2 (without pillars) to 6.6 cm2, producing a 1.35 cm2/μl surface area to volume ratio. To put this in perspective, this surface area to volume ratio is >90 times larger than that of a filter without pillars having the same macroscopic layout area, and is similar to the 200 μm deep microfluidic DNA extraction device reported by Christel et al. [23]. However, purification of DNA had been also achieved using chaotropic salts, which decrease bimolecular salvation [24]. This dehydration leads to hydrophobic interactions and counteracts repulsion forces, which drives bimolecular aggregation and precipitation on silica surface. Weak chaotropic salts, like sodium iodide and guanidinium salts, have limited ability to salt-out or precipitate proteins but are effectual nucleic acid precipitators. The same mechanism of chaotropic salt that provides silanol groups on silica surfaces drives the temporary formation of hydrogen bonding between nucleic acids and the surface. However, the weakness of this method is that the quality of obtained DNA is not usually high, and may inhibit PCR [7].

For the filters utilized in this study, where no chaotropic salts were used, the DNA most likely binds to the surface of the amino-coated μPF by means of electrostatic interaction between the positive charged amino groups, present on the surface due to APTES coating, and the negative charge on the DNA molecule. Figure 9 schematically illustrates the mechanism for the liquid phase microfluidic deposition of APTES on to Si μPF. In the presence of water, as a solvent, APTES dimerizes to form a chain of intermediate silanol through a condensation reaction. Treating the surface of Si μPF with Piranha prior to APTES coating, forms a thin silicon oxide layer. The subsequent water flow over this oxidized μPF surface causes its hydration. During the subsequent APTES coating flow, the water concentration on the surface of Si μPF will decrease due to APTES hydrolysis, but remains primarily in solution, hence it becomes more likely that the unreacted APTES monomers will react with water in the system instead of with the water on the pillar surface. As the surface water is consumed during the silanization step, the deposited APTES can no longer attain a high degree of hydrolysis, leading to an increase of C:N bonds. After silanization, the surface of the μPF is washed with water to remove any unbounded APTES molecules and curedat 80°C for 4 hours to condense the APTES chain on the surface of Si μPF via water removal and to form the –Si-o-Si- bond. The mechanism described above suggests that DNA collection, based on electrostatic interaction between positive charge of APTES amino groups and negative charge of DNA sample, was performed [25,26].

biosensors-bioelectronics-silanization

Figure 9: Schematic description of μPF silanization protocol.

The binding of DNA to the surface of the uncoated Si μPF is likely to be due to the presence of silanol groups on the surface, which were formed during the filter cleaning with piranha (3H2SO4: 1H2O2) and its subsequent exposure to water. The presence of such silanol groups encourages the temporary formation of hydrogen bondsbetween nucleic acids and the surface. Evidence of such weak binding is found in the high amount of DNA in the non-trapped and washed eluents, as shown in Figure 4F. However, the binding capacity of the uncoated filter is limited, compared to the well-established performance of the APTES-coated one. For example, starting with 2000 ng of DNA loading, the overall DNA elution recovery % for amino-coated μPF is 52%, compared to only 18% for an uncoated filter under similar conditions.

The simple and effective washing and eluting steps used in this work are important aspects of this study. For the washing step, pH 7.4 PB was utilized while the elution step was carried out using pure water at 80°C. The use of hot water during the elution step allowed for direct detection of obtained DNA using UV Nano-Droplet, eliminating the need for using fluorescence intercalating dyes and fluorometer. The mechanism for our successful DNA elution step is likely to be attributed to thermodynamic instability, caused by the flow of hot water which may weaken the electrostatic interaction between DNA and APTES molecule that subsequently leads to the detachment of the DNA. The postulate for thermal instability stemmed from observation that denaturing of the DNA molecules is quite likely at elevated temperature. For example, hydrogen bonds between the nitrogenous bases in chromosomal DNA begin to weaken at 70°C, causing the DNA molecules to buckle and change their configurations [27]. Such buckling of the DNA molecule affects the number of sites to which ions can bind. Another potentially contributing factor to the DNA detachment is the straining of both the bonds and the DNA molecule at high temperature, which clearly affects the available sites for hydrogen bonding and hydration of the DNA molecules.

Compared to available commercial filter kits, the described coated- μPF device described in this work represents a strong candidate for DNA extract ion technology. For instance, a coated-μPF requires minute sample volume (only 10 μl) while using a commercial kit requires at least10 times that volume. In case of unavailability of sufficient sample volume, excessive dilution may be needed. Moreover, with coated- μPF, there is no need to centrifuge or to use organic solvents that may inhibit PCR or require a long time to incubate the sample. The capturing capacity of the coated μPF was significantly higher than that of the uncoated filter: ~186 ng/cm2 capturing capacity is obtained using APTES-coated filters, compared to ~49 ng/cm2 with uncoated filter. This reflects the important and beneficial role of the APTES coating combined the power of having a functionalized massive surface area for DNA purification.

Conclusion

In this study, the performance of a microfluidic silicon μPF device capable of capturing and eluting DNA from small sample volumes under continuous flow rate mode, was investigated and presented. Only four minutes were needed to execute experiment with even using the lower loading flow rate 5 μl/min. Results show that the capture efficiency and elution % are decreasing with increasing flow rate and this behavior is more pronounced at higher initial DNA loading. As a result, excellent filter results are obtained combining a low flow rate with low initial DNA loading, such as an elution recovery of 80%, achieved at a flow rate of 5 μl/min and DNA loading of 250 ng. An uncoated μPF with identical pillar and macroscopic dimensions as the tested APTES-coated filter was also examined and showed limited capability for capturing DNA, which was traced back to Si pillar surface oxidation during the filter cleaning and preparation step. In addition to its excellent filtering capacities, the described DNA extraction μPF device exhibits interesting possibilities regarding monolithic integration with other micro-architectures to realize a fully integrated μTAS for use in the development of a variety of genetic diagnostics.

Building on the results of the work presented, an investigation of the optimum conditions to purify DNA from whole blood sample using APTES coated μPF is warranted. In addition, further work is needed to identify and characterize a suitable cleaning process to restore the μPF to its state before being used for DNA extraction. Such work is critical for determining whether such μPF can be reused.

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