Synthesis of mixed-sequence oligonucleotides on mesoporous silicon: chemical strategies and material stability
© Terracciano et al.; licensee Springer. 2014
Received: 24 April 2014
Accepted: 12 June 2014
Published: 25 June 2014
Rapid screening tests in medical diagnostic and environmental analysis are often based on oligonucleotide biochips. In this paper, we studied the stability of functionalized mesoporous silicon supports in the solid-phase synthesis of oligonucleotides, exploiting several chemical procedures. A 19-mer mixed sequence has been successfully synthesized on aminosilane-modified porous silicon photonic structures. The process and the materials have been characterized by optical reflectivity, atomic force microscopy and high-performance liquid chromatography.
DNA chip technology has greatly evolved over the last decade, moving from pure genomics towards a number of biotechnology applications such as human disease diagnostics , environmental monitoring and food control [2, 3]. DNA chips can be classified as a special class of biosensors since they are realized by immobilization of single-stranded oligonucleotides (ONs), the bioprobe, on a transducer surface. Any molecular interaction between the bioprobe and its ligands, such as hybridization to the complementary DNA sequence or protein binding, is then transduced into an analytical signal by an electrochemical-, optical- or surface plasmon resonance-based or electrical device, depending on the specific technology used. Porous silicon (PSi) is by far one of the most popular transducer materials due to its peculiar physical and chemical properties . PSi is fabricated by electrochemical etching of crystalline silicon in aqueous hydrofluoric acid. Depending on etch time, current density and acid concentration, several porous morphologies can be obtained, from micropores (average pore size <5 nm) to macropores (average pore size >50 nm) . The resulting sponge-like matrix possesses a very large specific surface area (up to 300 m2/cm3): gases and liquids can easily get into pores, thus changing the optical, chemical and electrical properties of PSi . Even if electrochemical etching induces silicon dissolution, the resulting PSi surface is smooth enough to get very good quality optical devices, also in the case of multilayered structures . Periodic, or quasi-periodic, alternation of high- and low-porosity layers is used for fabrication of Bragg reflectors, microcavities and Thue-Morse sequences: all these photonic devices exhibit resonance wavelengths that can be used as monitoring peak in quantifying biomolecular interaction from the optical point of view [8–10]. The PSi surface can be properly passivated and functionalized in order to covalently bind biological molecules such as single- or double-stranded DNA, proteins, enzymes, antibodies, aptamers and so on, which act as bioprobes. There are many routes to achieve surface functionalization which are based on proper chemical or biological processes: the PSi surface can be activated by specific chemical groups, namely -SH, -NH2 or -COOH, that could form very stable bonds, such as sulphide or peptide bond, with the biological molecule considered . For some biomolecules that are usually synthesized ex situ and then coupled on the PSi surface, there is also the possibility of directly growing the molecules using PSi as support in the so-called solid-phase synthesis .
In this article, we describe the fabrication and the characterization of a PSi-based DNA chip for biochemical optical sensing through in situ mixed-sequence ON growth. Since the chemistry used for the solid-phase synthesis of ON can be quite aggressive against the PSi solid support, the chemical stability of PSi supports is a key issue that must be checked and satisfied for each considered substrate. In particular, it is well known that PSi suffers upon exposure to alkaline solutions (commonly used for the deprotection of nucleobases) that can easily corrode the silicon skeleton, so a trade-off between PSi surface passivation and suitable solid-phase synthesis chemistry must be found. We focused our studies on silanization of PSi by using two different siloxanes and also on the exploitation of different chemical approaches for the ON deprotection in order to preserve the stability of PSi during all phases of synthesis and sensing.
Mesoporous silicon microcavity fabrication
PSi microcavities constituted by a λ/2 layer (optical thickness) sandwiched between two 9.5-period Bragg reflectors (BRs) were obtained alternating low (L) and high (H) refractive index layers whose thicknesses satisfy the Bragg relationship nHdH + nLdL = mλB/2, where m is an integer and λB is the Bragg wavelength. The microcavities were prepared by electrochemical etching of highly doped p+ crystalline silicon (0.001-Ω cm resistivity, <100 > -oriented, 500 μm thick) in HF solution (HF:ethanol 1:1) in the dark at room temperature (RT). Before the anodization process, the silicon substrate was immersed in HF solution for 2 min to remove the native oxide layer. Since the PSi fabrication process is self-stopping, it is possible to obtain adjacent layers with different porosities by changing the current density during the electrochemical etching . A current density of 200 mA/cm2 for 1.2 s was applied to obtain low refractive index layers (nL = 1.542; dL = 125 nm) while a current density of 100 mA/cm2 was applied for 1.4 s for high refractive index layers (nH = 1.784; dH = 108 nm). After the electrochemical process, the pore dimension was increased to favour the infiltration of biological matter by rinsing the fresh-made PSi microcavities in a KOH ethanol solution (1.5 mM) for 15 min . The structures were then thermally oxidized against uncontrolled environmental aging and corrosion in alkaline solutions. The thermal oxidation has been performed in pure O2 by a two-step process: pre-oxidation at 400°C for 30 min followed by oxidation at 900°C for 15 min.
Silane surface modifications
Eight oxidized PSi microcavities (PSi-Ma-h) were immersed in piranha solution (H2O2:H2SO4 1:4) at RT for 30 min to generate Si-OH groups on the PSi surface. After that, the samples were extensively washed in Milli-Q® water flow (Millipore, Billerica, MA, USA) and dried with nitrogen gas. Structures were then silanized by immersion in different 5% aminosilane solutions, (3-aminopropyl)triethoxysilane (APTES) or (3-aminopropyl)-dimethyl-ethoxysilane (APDMES), in dry toluene for 30 min at RT. Samples PSi-Ma,c,e,g were silanized by APTES and samples PSi-Mb,d,f,h by APDMES. The reaction conditions were optimized on a crystalline silicon-varying solvent for silane dissolution and incubation time . The PSi-silanized samples were rinsed three times in the solvent used for the process so as to remove the ungrafted silanes. The last step of silanization is curing at 100°C for 10 min.
● Coupling: reaction of the protected phosphoramidite dissolved in dry acetonitrile and activated via protonation by weakly acidic tetrazole (0.45 M in acetonitrile) with the 5′-OH ON terminal group.
● Oxidation: oxidation of the unstable phosphite triester linkage to the more stable phosphotriester by a standard oxidizing solution of iodine in pyridine/acetonitrile.
● Capping: acylation of the unreacted 5′-OH ON terminal groups by acetic anhydride in pyridine and tetrahydrofuran to minimize deletion products and simplify the purification process.
● Detritylation: removal of the 5′-dimethoxytrityl (DMT) protecting group from the support-bound 5′-terminal nucleotide with the deblocking solution of trichloroacetic acid in dichloromethane (3% w/w).
The amount of DMT cation released by acid treatment was used as a direct measure of the efficiency of the ongoing synthesis. The release of the protecting group generates a bright red-orange colour solution in which the quantity of the DMT cation can be measured online by UV-vis spectroscopy at 495 nm (ϵ = 71,700 M−1 cm−1). At the end of each growing cycle, the support was thoroughly washed with acetonitrile before the beginning of the successive cycle.
The devices PSi-Ma,b-NH2 (Ma = APTES, Mb = APDMES) were left in contact with 33% aqueous ammonia at 55°C for different times to investigate the effect of standard ON deprotection condition (55°C for 17 h) on the PSi matrix . Two additional aminosilane-modified devices, PSi-Mc,d-NH2, (Mc = APTES, Md = APDMES) were incubated in anhydrous K2CO3 (0.05 M)/dry methanol solution at 55°C for different times to investigate the ‘ultra-mild’ ON deprotection condition (55°C for 2 h) . Finally, the exposure to dry ammonia solution (NH3/MeOH dry) was also explored as an alternative deprotection strategy . To this aim, the aminosilane-modified samples PSi-Me,f-NH2 (Me = APTES, Mf = APDMES) were exposed to dry ammonia overnight at RT. The dry ammonia was generated by dissolving NaOH pellets in a sidearm flask containing aqueous ammonia; the generated gas was passed through a KOH drying tube and bubbled into a flask equipped with a rubber septum and containing anhydrous MeOH at 0°C.
30 min; 1 h; 2 h
30 min; 1 h; 2 h; 5 h; 8 h; overnight
Atomic force microscopy
A XE-100 AFM (Park Systems, Suwon, South Korea) was used to study sample morphology. Surface imaging was obtained in non-contact mode using silicon/aluminium-coated cantilevers (PPP-NCHR 10 M, Park Systems, Suwon, South Korea) 125 mm long with a resonance frequency of 200 to 400 kHz and nominal force constant of 42 N/m. The scan frequency was typically 1 Hz per line. The scan area in surface analysis was 1 μm × 1 μm.
Reflectivity spectra of PSi optical structures were obtained by a simple experimental setup: a white light was sent on PSi samples through a Y optical fibre (Avantes, Apeldoorn, The Netherlands). The same fibre was used to guide the output signal to an optical spectrum analyser (Ando AQ6315A, Tokyo, Japan). The spectra were acquired at normal incidence over the range 600 to 1,200 nm with a resolution of 5 nm. The reflectivity spectra shown in the graphs are the average of three measurements for each sample.
High-performance liquid chromatography
The purification and control of the synthesized ONs was carried out using a Jasco PU2089 PLUS HPLC system (Easton, MD, USA) equipped with an anion exchange column (1000-8/46, 4.4 × 50 mm, 5 μm, Macherey-Nagel, Düren, Germany) using a linear gradient from 0% to 100% B in 30 min, flow rate = 1 mL/min and detection at 260 nm (buffer A: 20 mM NaH2PO4 aq. solution, pH 7.0, containing 20% (v/v) CH3CN; buffer B: 20 mM NaH2PO4 aq. solution, pH 7.0, containing 1 M NaCl and 20% (v/v) CH3CN).
Results and discussion
In our previous work , we investigated the passivation ability of oxidized PSi multilayered structures by two aminosilane compounds (APTES and APDMES) used for the in situ synthesis of a 13-mer polythymine ON strand. We successfully demonstrated that even using the less aggressive carbonate/methanol solution as the ON deprotection system, hybridization with the complementary ON target took place, thus confirming that ONs can be synthesized and deprotected on the PSi surface. However, the synthesis of mixed-sequence ONs using the carbonate/methanol solution in the final ON deprotection step would require the use of highly expensive ultra-mild nucleobase-protected phosphoramidites characterized by having non-standard very labile protecting groups. In the present paper, we describe the results of alternative PSi-friendly ON deprotection conditions during the in situ synthesis of mixed-sequence ONs on PSi supports by using standard phosphoramidite nucleoside monomers, without using ultra-mild reagents.
Peak shift of devices after surface modification by APTES or APDMES
Peak shift (nm)
Peak wavelength (nm) Er±
Peak wavelength (nm) Er±
631.3 ± 0.3
653.3 ± 0.1
640.1 ± 0.1
651.0 ± 0.2
635.7 ± 0.5
656.9 ± 0.4
628.4 ± 0.6
640.7 ± 0.3
708.2 ± 0.2
730.3 ± 0.6
714.7 ± 0.1
722.3 ± 0.4
706.5 ± 0.3
727.8 ± 0.1
665.6 ± 0.4
673.7 ± 0.2
Figure 6 also shows the reflectivity spectra of devices before and after the in situ synthesis process: red shifts of 60 and 70 nm were detected, respectively, for APTES- and APDMES-modified devices, thus indicating that more ON had grown on the latter device with respect to the first one. This experimental result is ascribed to the less steric hindrance of pores due to the thinner APDMES layer, as already demonstrated in our previous work .
In both samples, we have measured the red shifts upon exposure to saturated ethanol atmosphere (data not shown here), in order to check if pores could be completely filled up by ON growth: in both cases, we measured red shifts of about 100 nm, just a little bit lower, but of the same order, than those registered in the same experiment after fabrication and silane functionalization. Even if this result is not accurate as standard pore characterization (such as gas adsorption or thermo-porometry), it clearly confirms a minor variation in pore dimensions.
In the present study, we propose and validate by optical measurements a new method to achieve the in situ synthesis of tailored oligonucleotide sequences on porous silicon supports suitable for label-free optical biosensing. In particular, we demonstrate that, differently from aqueous ammonia, the use of dry ammonia in methanol allows the effective deprotection of nucleobases without harming the structural integrity of the porous silicon matrix, thus opening the way for the direct growing of mixed-sequence ONs on optically active PSi supports using exclusively inexpensive standard phosphoramidites. A 19-mer mixed-sequence 5′-GATTGATGTGGTTGATTTT-3′ has been synthesized in mesoporous PSi microcavities, resulting in a medium-yield process, mainly due to the average pore size (about 20 nm). PSi photonic devices with pore dimensions greater than that value, but always compatible with high optical quality response in the visible-near-infrared, therefore between 50 and 100 nm, will be considered in the next experiments, in order to maximize yield synthesis. Moreover, more stable PSi supports could also be considered, such as those produced by thermal acetylation, which maintains pore size and makes it very stable from the chemical point of view .
This work has been partially supported by the national project PON Oncology.
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