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Top-Down Nanofabrication and Characterization of 20 nm Silicon Nanowires for Biosensing Applications

  • M. Nuzaihan M. N ,

    Affiliation Institute of Nano Electronic Engineering, Universiti Malaysia Perlis, 01000 Kangar, Perlis, Malaysia

  • U. Hashim,

    Affiliations Institute of Nano Electronic Engineering, Universiti Malaysia Perlis, 01000 Kangar, Perlis, Malaysia, School of Microelectronic Engineering, Universiti Malaysia Perlis (UniMAP), 02600 Pauh, Perlis, Malaysia

  • M. K. Md Arshad,

    Affiliations Institute of Nano Electronic Engineering, Universiti Malaysia Perlis, 01000 Kangar, Perlis, Malaysia, School of Microelectronic Engineering, Universiti Malaysia Perlis (UniMAP), 02600 Pauh, Perlis, Malaysia

  • A. Rahim Ruslinda,

    Affiliation Institute of Nano Electronic Engineering, Universiti Malaysia Perlis, 01000 Kangar, Perlis, Malaysia

  • S. F. A. Rahman,

    Affiliation Chemistry Department, Faculty of Science, Universiti Putra Malaysia, 43400 UPM Serdang, Selangor, Malaysia

  • M. F. M. Fathil,

    Affiliation Institute of Nano Electronic Engineering, Universiti Malaysia Perlis, 01000 Kangar, Perlis, Malaysia

  • Mohd. H. Ismail

    Affiliation School of Microelectronic Engineering, Universiti Malaysia Perlis (UniMAP), 02600 Pauh, Perlis, Malaysia


A top-down nanofabrication approach is used to develop silicon nanowires from silicon-on-insulator (SOI) wafers and involves direct-write electron beam lithography (EBL), inductively coupled plasma-reactive ion etching (ICP-RIE) and a size reduction process. To achieve nanometer scale size, the crucial factors contributing to the EBL and size reduction processes are highlighted. The resulting silicon nanowires, which are 20 nm in width and 30 nm in height (with a triangular shape) and have a straight structure over the length of 400 μm, are fabricated precisely at the designed location on the device. The device is applied in biomolecule detection based on the changes in drain current (Ids), electrical resistance and conductance of the silicon nanowires upon hybridization to complementary target deoxyribonucleic acid (DNA). In this context, the scaled-down device exhibited superior performances in terms of good specificity and high sensitivity, with a limit of detection (LOD) of 10 fM, enables for efficient label-free, direct and higher-accuracy DNA molecules detection. Thus, this silicon nanowire can be used as an improved transducer and serves as novel biosensor for future biomedical diagnostic applications.


Silicon nanowires with nanometer-scale widths and micrometer-scale lengths are receiving considerable attention for sensor applications, and many research groups have demonstrated these materials’ promising nanotechnology and exciting potential for use in the future “Biosensing” era [17]. In particular, silicon nanowires offer interesting prospects for integration with complementary metal-oxide semiconductor (CMOS) [811] and lab-on-chip (LOC) technologies [1213] as well as real-time [1416], label-free [1519] and high sensitivity sensing [1, 4, 15, 2023]. The fabrication of silicon nanowires has been demonstrated by both bottom-up [3, 15, 24] and top-down [3, 8, 14, 22, 2426] approaches.

The bottom-up approach usually uses metal-catalytic growth [4, 27]. However, there are several issues using this approach, as observed by Hsiao et al. [2]. In this report, difficulty in the exact positioning of nanowires on the device is the main issue, although metal contamination [2, 8] and the control of structural parameters [2] (i.e., randomly oriented growth and poor length and diameter size distributions) are other issues that need to be considered for the fabrication of nanowires.

In contrast, the top-down approach enables a more precise control of the geometry and a very accurate alignment with other structures on the device [14]. Better control of electrical properties can be achieved due to the very well defined widths and lengths of the silicon nanowires. Moreover, the top-down approach has higher yield and more reproducible results than does the bottom-up approach due to the maturity of the existing silicon fabrication and silicon-on-insulator (SOI) technologies.

Considering these advantages, we report a top-down nanofabrication of silicon nanowires using direct-write electron beam lithography (EBL). We describe the nanowire fabrication steps, such as sample preparation, pattern design, the EBL process, anisotropic etching using inductively coupled plasma-reactive ion etching (ICP-RIE) and the size reduction process. We highlight the important process parameters for EBL and size reduction for our nanometer-scale devices. Wire widths and heights as small as 20 nm and 30 nm, respectively, were fabricated on SOI substrates, and the nanowires successfully detected DNA molecules in a microfluidic environment by monitoring the changes in the current, resistance and conductance before and after DNA hybridization. These results prove that the silicon nanowires are promising for the detection of specific biomarkers and other targeted proteins.

Methods and Materials

1. Top-down nanofabrication of silicon nanowires using EBL

The top-down nanofabrication process of silicon nanowires is briefly illustrated in Fig 1. Four key process steps are required to form the silicon nanowires: sample preparation, pattern design, EBL and anisotropic etching. Details of each process step are elaborated as follows.

Fig 1. Top-down nanofabrication process steps of silicon nanowires using EBL.

a. Sample preparation.

The silicon nanowires were fabricated from SOI (<100>) wafer (Soitec) with 200 nm of buried oxide (BOX) and a 50 nm p-type Boron-doped silicon top layer (resistivity: 8.5–11.5 Ω.cm with doping density of 1015 First, the SOI wafer was cleaned using standard RCA 1 (mixing DI water: 5, ammonium hydroxide (27%): 1 and hydrogen peroxide (30%): 1) and RCA 2 (mixing DI water: 6, hydrochloric acid (30%): 1 and hydrogen peroxide (30%): 1) solutions to remove contaminants, followed by soaking in dilute hydrogen fluoride (HF) to remove the native oxide. All of the chemicals and solvents used in this cleaning process were purchased from Futurrex and Mallinckrodt Baker. After the cleaning process, the SOI wafer was cut into small pieces measuring 2 cm by 2 cm. Next, high-performance negative tone resists (ma-N2400 series were purchased from Microresist Technology GmbH) were spin coated on the sample and then dehydrated on a hotplate. The coated samples were then left for several minutes on a cooling plate to control the sample temperature for uniform resist characteristics. Detailed parameters of the resist coating process are summarized in Table 1. The ma-N2400 series resists are composed of a phenolic resin (novolak) as the polymeric bonding agent and an aromatic bisazide as the photoactive compound (PAC) dissolved in safer solvents, and they are very sensitive to electron beam radiation [2830]. The advantages of the ma-N2400 series are its good thermal and etch stability. These resists can be developed without swelling in an alkaline aqueous developer and do not chemically modify the surface [2830].

b. Nanowire pattern design.

The nanowire patterns were designed with various dimensions using RAITH ELPHY Quantum GDSII Editor developed by Raith GmbH. ELPHY Quantum is a universal lithography system that makes it possible to produce micro- and nanostructures by means of electron beam writing using a scanning electron microscope (SEM) [31], with pattern-placement accuracy below 20 nm [32]. Two type patterns were designed; one is an array of 20 identical nanowires with a 40-nm width and a 400-μm length (Fig 2(A)), and the other is an array of single nanowires with 5 different widths (40, 50, 60, 70 and 80 nm) and a 400-μm length (Fig 2(B)). For both designs, the 400-μm length was designed to ensure that the nanowires come into contact with the electrode pad in the subsequent fabrication process. In addition, both patterns were designed to increase the probability of adhesion or reaction of the analytes to the nanowire surface during testing [33].

Fig 2. The overall design for silicon nanowires.

(a) Array and (b) single, with the drain and source electrode pads.

c. Electron beam lithography (EBL).

The next step was the EBL exposure process. EBL was performed with JOEL JSM 6460LA SEM equipped with a Raith ELPHY Plus pattern generator. Detailed exposure process conditions for both resists are summarized in Table 2. After the EBL exposure process, the sample was left for 5 minutes before proceeding with the development process. Development was executed for various developing times using the ma-D 532 developer to determine whether the unexposed resist dissolved sufficiently. Developing times were varied from 15 to 45 seconds, depending on the thickness and type of resist. Then, the developed samples were rinsed in de-ionized water (DIW) for 5 minutes and blown dry with air. After rinsing, the samples were hard baked at 90°C for 60 to 90 seconds to improve the resist’s adhesion to the samples and its resistance to the anisotropic etching process. The developed samples were then characterized using high power microscopy (HPM), SEM (JEOL 6460), and atomic force microscopy (AFM).

d. Anisotropic dry etching.

Each developed sample was then loaded into a SAMCO ICP-RIE 10iP for anisotropic etch profile of silicon. This etcher can achieve anisotropic sidewall profiles in high aspect ratio openings. The resist pattern acted as a mask for the silicon etching [31] by protecting areas where a chemical reaction between the surface materials and reactive gases was not required. The ICP-RIE was performed under a pressure of 5 mTorr and a radio frequency (RF) power of 500 W using CF4 (30 sccm) and O2 plasma (28 sccm) for 1 minute. The resist pattern was stripped using acetone, which revealed silicon nanowires with a good anisotropic profile. The etch profile and feature sizes of the silicon nanowires were determined by SEM and AFM. In addition, energy-dispersive x-ray (EDX) was carried out to identify the elemental composition of nanowires after dry etching process.

2. Size reduction of silicon nanowires by thermal oxidation

The silicon nanowires were then oxidized in a dry O2 environment at 1000°C for 10–20 minutes, depending on the thickness of the silicon layer. To reduce the width of the silicon nanowires, the oxidized sample was dipped in buffered oxide etch (BOE) for 5 seconds to remove the SiO2 layer. The BOE soak time is crucial and thus needs to be optimized to avoid any removal of the buried oxide (BOX) and to maintain a layer isolating the electrodes from the substrate. To understand the size reduction process, Fig 3(A), 3(B) and 3(C) illustrate the process flow chart for size reduction by thermal oxidation. Fifty-four percent of the oxide formed outside the original silicon surface, and 46% of the oxide formed underneath it, all of which was removed during the BOE etching process. The aspect ratio was calculated by measuring the size difference in SEM and AFM images before and after the size reduction process.

Fig 3. Process flow diagram.

(a) Silicon nanowires produced by EBL and ICP-RIE, (b) size reduction by thermal oxidation, (c) BOE etching of the oxidized surface reduces the size of silicon nanowires, (d) silicon nanowires with the corresponding contact pads and (e) the sensor consisting of silicon nanowires integrated with the microfluidic channel.

3. Development of metal contact pads

After the fabrication of silicon nanowires using EBL and the size reduction process, metal contact pads were formed to allow electrical measurements on the fabricated silicon nanowires. In the device design, larger metal contact pads for the source (S) and drain (D) were connected to each end of the fabricated silicon nanowires. As shown in Fig 2(A) and 2(B), the array design allowed three pads with 20 nanowires per pad, while the single design allowed the five different size nanowires to be individually characterized. The pad mask was designed using AutoCAD and printed onto the chrome mask glass surface. Two different types of metal contact pads, 150 nm gold (Au) on 10 nm titanium (Ti) and 100 nm aluminum (Al), were developed using a lift-off method. First, the fabricated silicon nanowires were spin coated with negative resist (NR9-6000PY) at 3000 rpm for 25 seconds, followed by patterning with conventional lithography using a chrome pad mask. Subsequently, Au/Ti or Al was deposited onto the sample patterned with the negative resist using an Auto 306 thermal evaporator, followed by a resist stripping process for 3 minutes. Fig 3(D) shows the silicon nanowires with metal contacts at both ends (S and D) for further connection to the outer electronics. The rest of the silicon nanowire sensor was fabricated after the formation of metal contact pads.

4. Preparation of microfluidic channel

The fabricated device was then integrated into a microfluidic channel. The microfluidic channel was fabricated on top of the silicon nanowires to allow solution to be directed over an active area of the silicon nanowires. Furthermore, the channel allows only a very small volume, which limits the flow and ensures the accurate detection of target DNA in the solution to be analyzed. The two main methods for microfluidic channel preparation are open chamber [7] and closed microfluidic channels [7], as shown in Fig 4(A) and 4(B), respectively. As seen in Fig 4(A), the open chamber microfluidic channel was lithographically patterned and developed on the fabricated device with a 100-μm-thick spin-coated negative resist (SU-8) or a positive photoresist (PR1-2000A). The dimensions of the open chamber microfluidic channel were 5 mm in length and 0.1 mm (100 μm) in width. For the closed microfluidic channel, a 0.1-mm (100-μm)-wide channel with 1.2-mm diameter inlet/outlet holes was fabricated using polydimethylsiloxane (PDMS) on a SU-8 master mold and then bonded to the fabricated silicon nanowires, as shown in Fig 4(B). Fabrication of the SU-8 master mold began with spin-coating SU-8 2010 series (MicroChem) at 300 rpm for 25 seconds on the cleaned silicon substrate surface and then baking at 95°C for 35 minutes. Next, the coated sample was exposed using conventional lithography for 240 seconds, followed by the development process. The PDMS pre-polymer was made from a 10:1 mass ratio mixture of a silicon elastomer base and a curing agent (Dow Corning’s Sylgard Elastomer 184); the mixture was vigorously stirred for 45 to 60 minutes to ensure a perfectly mixed pre-polymer and was subsequently poured on the master mold surface to generate a negative replica (i.e., an inverse structure) of the mold. The PDMS was then cured on the master mold at 70°C in an oven for 2 hours to remove all gas bubbles. The PDMS inverse structures were then mechanically peeled off the SU-8 master mold and cut to the final dimensions around the microfluidic channel as shown in Fig 4(B). Finally, the fabricated PDMS microfluidic channel and silicon nanowires were bonded together with an O2 plasma treatment at 300 mT of air pressure for 30 seconds.

Fig 4. Schematic diagram of a cross-sectional view of the silicon nanowires integrated with the microfluidic channel.

(a) Open chamber with a spin-coated resist (SU-8 or PR1-2000A) and (b) closed PDMS microfluidic channel.

5. Surface functionalization of silicon nanowires

Functionalization of the silicon nanowire surface is necessary to prepare a suitable platform for DNA detection. The three steps involved in the surface functionalization of silicon nanowires are surface modification, immobilization and hybridization, as shown in Fig 5.

Fig 5. Schematic illustration of the surface functionalization.

Surface modification by APTES and glutaraldehyde, DNA immobilization and DNA hybridization on the silicon nanowire surface.

a. Surface modification.

Surface modification is a chemical process that favors the formation of the active groups that are necessary for the covalent immobilization of biomolecules on a surface. In this research, the surface modification began by cleaning the surface of nanowires using DI water and IPA, followed by drying for 5 minutes. Next, the silicon nanowires were immersed in 2% 3-aminopropyltriethoxysilane (APTES (v/v)) in a mixture of 95% ethanol and 5% water for 2 hours at room temperature to obtain surface-exposed amine groups on the surface of the nanowires [21]. Then, the samples were washed with ethanol 3 times to remove any unreacted APTES and dried on a hot plate at 120°C for 10 minutes. Next, the APTES-functionalized nanowires surface was immersed in a 2.5% glutaraldehyde (Sigma-Aldrich) with phosphate-buffered saline (PBS, pH 7.4) solution for 1 hour at room temperature. Glutaraldehyde was introduced as a linker to bind the amine-terminated APTES and present aldehyde groups on the surface. Subsequently, the samples were washed with PBS solution for 5 minutes to remove excess glutaraldehyde.

b. DNA immobilization.

For the immobilization procedure, a 27-mer amine-terminated probe (5’-NH2-C6-AACAGCATATTGACGCTGGGAGAGACC-3’) (Integrated DNA Technologies, Inc.) was used to bind the available aldehyde groups on the silicon nanowire surface. This probe was diluted with PBS (pH 7.4) to a 10 μM DNA probe solution before immobilization on the APTES-functionalized nanowire surface. Next, the probe was injected into the microfluidic channel flowing through the silicon nanowire sensing area, and the sensor was incubated at room temperature for 4 hours. Then, any unbound probe was washed away with PBS 3 times.

c. DNA hybridization, de-hybridization and control.

After immobilization, the 27-mer complementary target DNA (3’-TTGTCGTATAACTGC GACCCTCTCTGG-5’) (Integrated DNA Technologies (IDT), Inc.) was applied to hybridize the immobilized DNA on the nanowires. The sample was hybridized at room temperature overnight and then washed with PBS to remove the excess target DNA. The 27-mer complementary strand was diluted to various concentrations (10 fM to 10 μM) with PBS. To ensure successful hybridization, the electrical properties of the hybridization samples were then measured using I-V measurement. After the electrical measurements, the samples were washed with hot DI water at 90°C for 5 minutes to de-hybridize the complementary DNA pairs on the nanowires. To confirm the specificity of the sensor, the immobilized DNA that remained on the nanowires was hybridized with 27-mer (same length) non-complementary DNA (3’-CCTGTACCGGGTCTATGATTGTGTCTT-5’).

6. Optical and electrical characterization

The morphology and electrical properties of the silicon nanowires were then characterized. High power microscopy (HPM) (OLYMPUS-BX51) was used as the basic optical inspection tool for sample and device structures. Scanning electron microscopy (SEM) (JEOL JSM-6460LA) was used to determine the quality of the silicon nanowires, particularly the shape, diameter and uniformity. Energy-dispersive x-ray (EDX) was carried out to identify the elemental contents and purity of materials. Atomic force microscopy (AFM) (SPA400-SPI3800, Seiko Instruments Inc., Japan) was used to study the surface and 3D profile of the silicon nanowires. The electrical characterization was carried out to investigate the current-voltage (I-V), specificity and sensitivity of the silicon nanowire sensor using a KEITHLEY 6487 picoammeter/voltage source. A direct current (DC) voltage of 0–1 V was applied between the two metal contacts of silicon nanowire sensor to test the fabricated silicon nanowires, the amine-terminated APTES, DNA immobilization and hybridization. All measurements were performed at room temperature and under a microfluidic environment.

Results and Discussion

1. Characteristics of the ma-N2400 series negative electron beam resist

An important aspect of this silicon nanowire fabrication method was the characteristics of negative electron beam resist. Fig 6(A) clearly shows that the resist film thickness is inversely proportional to the spin speed of the ma-N2400 series, whereby an increase in the spin speed process leads to a decrease in the resist thickness. This resist interacted with and adhered to the silicon surface, thus creating a thin electron beam resist layer. A thinner and more uniform electron beam resist layer is preferable to produce better resolution and good resistance to the plasma etching process, which are crucial for obtaining nanostructures with high aspect ratios [28]. The resulting ma-N2400 series resist film thicknesses were approximately 250–400 nm at maximum spin speed of 6000 rpm for 30 seconds, as shown in Fig 6(A). This is an optimal resist thickness for exposure parameters described in Table 2. The ma-N2403 is thinner than the ma-N2405 because of its different viscosity and density. To investigate the effect of dose on the feature size (width), the ma-N2403 e-beam resist coatings (250 nm) were exposed through the nanowire patterns with different electron doses, with the accelerating voltage and developing time kept constant at 20 keV and 40 seconds, respectively. Different feature sizes of e-beam resist have different dose requirements [34]. Fig 6(B) and 6(C) show SEM and AFM images of developed resist patterns with widths of approximately 100 nm and approximately 70 nm exposed with electron doses of 200 μC/cm2 and 150 μC/cm2, respectively. Fig 6(B) and 6(C) show that the feature size is very sensitive to electron dose value. As the dose increases, more electrons are transferred to the coated resist and the feature size become thicker [35]. This is in good agreement with the findings reported by Grigorescu et al. [36], who noted that the feature size increases with increasing electron doses. The high-resolution resist pattern with a thickness of 250 nm and a width of approximately 70 nm (Fig 6(C)) was later used for the silicon etch (dry) process by RIE to form the silicon nanowires. In addition to its excellent resolution capability, the ma-N2400 series resists are simple resists with easy process control and are considerably more resistant to dry and wet etching.

Fig 6. ma-N 2400 series resist characteristics.

(a) The resist thickness curve decreasing with the spin speed (rpm), SEM and AFM images of resist pattern after development process (b) 100 nm width exposed with an electron dose of 200 μC/cm2 and (c) 70 nm width exposed with an electron dose of 150 μC/cm2.

2. Morphology of the silicon nanowires

A top view SEM image of the silicon nanowires after the dry etch process is shown in Fig 7(A). The results indicate that the silicon nanowires were formed with good uniformity, high resolution and good pattern placement. The width of the silicon nanowires is approximately 60 nm. The cross-sectional SEM image shown in the Fig 7(A) inset further revealed that these nanowires exhibit clear rectangular cross sections, though the AFM image shows the profile features to be approximately 60 nm in width and 50 nm in height. Compared with the resist pattern in Fig 6(C), the silicon nanowires reduced in width by approximately 10 nm after the dry etch process. The results show that dry etching process produced a silicon nanowire with more surface roughness and greater width, which is in agreement with the findings of Enami et al. [37]. The size reduction process is the major focus of this research. To achieve the smallest possible width of silicon nanowires with good aspect ratios, dry oxidation and wet etching (BOE) are preferred [21, 3840]. The width of the silicon nanowires could be precisely controlled by controlling the etching time and using self-limiting oxidation [21]. The 60-nm silicon nanowires were dry oxidized and first expanded to approximately 100 nm (Fig 7(B)). Then, the SiO2 was etched away, which resulted in a final width of 20 nm (Fig 7(C)). The AFM image in Fig 7(C) shows the morphology and a profile of approximately 20 nm in width and 30 nm in height. These images prove that 20 nm (46%) of the grown oxide extends inward and that 25 nm (54%) of the grown oxide extends outward from the original dimensions of the silicon nanowires. The aspect ratio h/w can be calculated using Eq (1), as shown below: (1) where h is the height, w is the width and c is reduction value. The aspect ratio was calculated to be 1.5 when the observed values of h and w were 30 nm and 20 nm, respectively. The AFM results demonstrate that the top width of the silicon nanowires is smaller than its base width due to the limitations of the AFM physical probe, which is not ideally sharp. As a consequence, the AFM image reflects not the true sample topography but the interaction between the silicon nanowire and probe [41]. Hence, we have also demonstrated the accuracy and repeatability of measurements as shown in the inset of Fig 7(D). Three samples from each step (before and after reduction process) were used in the measurement test using AFM. The results show that the samples have good repeatability and very high accuracy. In addition, EDX was carried out to identify the elemental contents and purity of the nanowire. The EDX spectrum of the fabricated silicon nanowire is presented in Fig 7(A). The amount of silicon (Si) and oxygen (O) elements were achieved around 77.82% and 22.18% from the total percentage weight, respectively. There is a strong Si peak at 1.8 keV together with the O peak at 0.5 keV in the spotted nanowire, indicating that was silicon nanowire successfully fabricated.

Fig 7. SEM and AFM images of the silicon nanowires.

(a) 60 nm width and 50 nm height. The inset is the cross-section of the silicon nanowires. EDX spectrum shows the purity of silicon (Si) on the nanowire. (b) The silicon nanowires were oxidized to a width of 100 nm and then (c) etched in BOE to remove the SiO2, thus producing 20-nm-wide and 30-nm-high silicon nanowires. The inset is the SEM image of silicon nanowires at 15 keV with 100 000 magnification. (d) The size (width) of silicon nanowire for three samples (before and after size reduction process).

3. Electrical characterization of fabricated silicon nanowires

The quality of the silicon nanowires was further characterized electrically by measuring the current-voltage (I-V) characteristic between the source (S) and drain (D) electrodes before introducing DNA detection to the silicon nanowires. The Ids-Vds characterization of the silicon nanowires after each stage (before and after size reduction process) was plotted as shown in Fig 8(A). The device exhibited an almost linear relation between the current and voltage (i.e., ohmic behavior). After the size reduction process (width = 20 nm), the drain current (Ids) was much lower than the Ids measured before the size reduction process (width = 60 nm). At Vds = 1 V, the Ids value dropped by 23 pA, from 132 pA to 109 pA. The decrease was caused by the increase in resistance at the silicon nanowires after the size reduction process. Fig 8(B) shows that the average resistance values of silicon nanowires for 20 nm and 60 nm were 8.9 GΩ, and 7.2 GΩ, respectively. The resistance of the wire is inversely proportional to its width. The results indicate that the lightly doped silicon nanowires (1015 produced high resistance and sensitivity due to the pronounced electromagnetic interference [17], which is important for biomedical applications. In addition, the electrical conductance for 20 nm and 60 nm was 0.25 nS and 0.27 nS, respectively. From Fig 8(B), the smaller feature size nanowire (20 nm) has lower conductance than does the bigger nanowire (60 nm) due to the large surface effects of smaller wire [14]. The electrical measurements confirmed that this top-down nanofabrication process produces high-quality silicon nanowires with great potential for further development.

Fig 8. Electrical properties of silicon nanowires.

(a) Ids-Vds characteristic shows p-type ohmic behavior and (b) the resistance and conductance histograms for 20 nm and 60 nm nanowires. The arrow highlights the direction from low to high width of the silicon nanowires.

4. Specificity and sensitivity of DNA detection by the 20 nm silicon nanowires

To evaluate the specificity and sensitivity of DNA molecule detection, a 20-nm silicon nanowire that was perfectly aligned and integrated with the open chamber microfluidic channel was developed, as illustrated in Fig 4(A). To ensure that the target DNA was identified precisely and accurately, an amine-based method was used in this research. The large amount of SiOH (silanol) groups with excellent proton donors (H+) and acceptors (SiO) [42] on the silicon nanowires/SiO2 surface (i.e., the native oxide) was reacted with an APTES solution to obtain surface-exposed–NH2 (amine) groups for biomolecule immobilization with the help of glutaraldehyde linkers [21], as illustrated in Fig 5. Glutaraldehyde is a homo-bifunctional linker and has the potential to bridge two amine functional groups [43]. One end interacts with amine-terminated APTES, and the other end is free to react with the amine-terminated probe DNA. Subsequently, the DNA probe could bind effectively to the silicon nanowire surface to react with the target DNA. The hybridization specificity of the silicon nanowire sensor for the detection of DNA was further evaluated by analyzing fully complementary target DNA and non-complementary target DNA (control group). Fig 9(A) shows the Ids-Vds characteristics of silicon nanowire biosensor. The sensor with APTES surface modification on the nanowire surface resulted in Ids = 240 pA, which increased by 131 pA compared with the Ids = 109 pA observed for the initial sensor at Vds = 1 V. Furthermore, upon DNA immobilization and hybridization, a further significant increase in Ids was observed. The sensor with the target complementary DNA (10 μM) resulted in Ids = 857 pA, which is 517 pA higher than the DNA probe (10 μM), Ids = 340 pA at Vds = 1 V. Because the silicon nanowires is p-type, this Ids increment depended on the enhanced hole current density on the surface (due to accumulation of more positive charges carriers) induced by the negatively charged probe/target hybridized DNA, thus resulting in a change in resistance. Fig 9(B) shows that the average resistance of the p-type silicon nanowires decreased upon the addition of negative surface charges at the surface. An obvious 66.5% increase in resistance was observed when 10 μM target complementary DNA was hybridized to the immobilized DNA probe, as shown in Fig 9(C). Consequently, the electrical conductance values of silicon nanowires increased, as shown in Fig 9(D). The increase in conductance for the p-type silicon nanowire device is consistent with an increase in negative surface charge density associated with the binding of negatively charged DNA to the surface. These results are in good agreement with previously reported results [6,21,44]. The multiple layers of surface functionalization (molecules) bound to the silicon nanowires, which caused the current flow to increase, thus proving that the silicon nanowire sensor was sensitive to chemical changes and reactions. To further verify that the current and resistance changes were due to the hybridization of the complementary target DNA, 10 μM of non-complementary target DNA (control group) was hybridized to the immobilized DNA probe. As shown in Fig 9(A), no significant Ids change was observed in this case, which indicates that there is no significant reaction binding of the non-complementary target DNA to the silicon nanowire surface. Furthermore, Ids returned to the original value of the immobilized DNA probe, although there was a negligible resistance change (1.9%) with the non-complementary control group (Fig 9(C)), indicating that no duplex forms between the pair of sequences, which is consistent with the previously reported results [17,19, 23, 44]. Therefore, the silicon nanowires offer very good specificity with excellent discrimination between fully complementary and non-complementary sequences.

Fig 9. Silicon nanowire biosensor.

(a) Ids-Vds characteristic, (b) the average resistance values after various surface functionalizations, (c) hybridization specificity demonstrated by the response (i.e., resistance change) to the complementary and non-complementary DNA sequences and (d) the electrical conductance by different steps of surface functionalization.

DNA detection was further performed by monitoring the concentration-dependent resistance change upon hybridization to complementary target DNA as shown in Fig 10. The relative change in resistance was extracted from the Ids-Vds (Fig 10(A)). An obvious 66.5% resistance change was obtained when 10 μM concentration of complementary target DNA was hybridized to the immobilized DNA probe. While, the resistance change reduced to 52.9%, 24.3% and 8.9%, respectively when 10 nM, 10 pM and 10 fM concentration of complementary target DNA were employed. From these results, it can be concluded that, the higher concentration of the target DNA was hybridized, the more negative charges added on the silicon nanowires surface, which lead to an accumulation of more positive charges carriers (holes), resulting in the increasing of the relative change in resistance as observed. Furthermore, this observation was also in consistent with previously reported results [3, 7, 17, 43].

Fig 10. Response of the immobilized DNA silicon nanowires biosensor to the complementary DNA of varying concentrations from 10 μM down to 10 fM.

(a) Ids-Vds characteristic and (b) resistance changes versus concentration (i.e., relative change in resistance).

In biosensing, the limit of detection (LOD) is defined as the lowest detectable molar concentration of target DNA, and it is used as a primary measure of sensitivity. In this research, the LOD was evaluated by lowering the concentration of target DNA (10 fM), as shown in Fig 10(B). To the best of our knowledge, the LOD of the p-type silicon nanowire sensor demonstrated in this research is lower than that demonstrated by Pengfei et al. [20], Adam et al. [21], Ryu et al.[44] or Pham et al. [45], which were 1 nM, 0.1 nM, 1 pM and 200 pM, respectively. Our results verify that this silicon nanowire sensor is feasible as a biosensor to detect an extremely low concentration target DNA without additional labeling procedures. Table 3 summarized the analytical performance of our p-type silicon nanowire biosensors in terms of size, detection limit and advantages. Based on the data in Table 3, it is clearly shown that our work has superior performances compared to previous published works. In addition, the potential advantages of using our device are small volume consumption of analytes for biosensing elements, compatibility with integrated circuitry and possibility of multiplexed sensing. Moreover, the fabrication of silicon nanowire by the proposed top-down approach offers an excellent uniformity and reproducibility, and the sensor can be readily incorporated to commercially available detection devices.

Table 3. Analytical performance of p-type silicon nanowire in DNA biosensor technologies.


High-quality silicon nanowires with good performance as a biosensor were successfully fabricated via a top-down nanofabrication approach. The major challenges in this research involve the EBL process and the reduction of the feature size by thermal oxidation. With the proper manipulation of parameters in the EBL and size-reduction processes, the widths of the silicon nanowires are controllable, decreasing the 70-nm-wide nanowires obtained from the resist pattern to 20-nm-wide and 30-nm-high nanowires with a straight over length of 400 μm. Furthermore, considering the high-quality and repeatable fabrication process of these silicon nanowires, this research shows that silicon nanowires can be fabricated using this approach, which is compatible with established CMOS technologies. The fabricated silicon nanowires showed good electrical characteristics after surface modification, DNA immobilization and DNA hybridization. After the DNA immobilization and hybridization, the current Ids was found to increase, which is consistent with an increase in the negative charge on the nanowire surface due to negatively charged DNA. Thus, by monitoring the resistance and conductance changes upon hybridization to complementary target DNA, the silicon nanowire sensor specifically detects target DNA at femtomolar levels. The use of this approach offer good specificity and sensitivity, with an LOD of 10 fM for target DNA. The fabricated silicon nanowires have great potential as a biosensor for biomedical diagnostic applications.


This research was supported by the Ministry of Higher Education Malaysia, and the author would like to thank all staff members of the Institute of Nanoelectronic Engineering, Universiti Malaysia Perlis (UniMAP) for their technical advice and direct and indirect contributions.

Author Contributions

Conceived and designed the experiments: MNMN MFMF. Performed the experiments: MNMN MFMF SFAR. Analyzed the data: MNMN MKMA ARR. Contributed reagents/materials/analysis tools: UH MKMA ARR MHI. Wrote the paper: MNMN MHI MFMF MKMA.


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