Applied Science and Convergence Technology 2021; 30(4): 111-114
Published online July 30, 2021
Copyright © The Korean Vacuum Society.
Kyung Ho Kima,†, Jai Eun Ana,†, Jun-Seob Kimb, Joonwon Baec,*, and Oh Seok Kwona,d,*
aInfectious Disease Research Center, Korea Research Institute of Bioscience and Biotechnology (KRIBB), Daejeon 34141, Republic of Korea
bDepartment of Nano-Bioengineering, Incheon National University, Incheon 22012, Republic of Korea
cDepartment of Applied Chemistry, Dongduk Women’s University, Seoul 02748, Republic of Korea
dNanobiotechnology and Bioinformatics (Major), University of Science & Technology (UST), Daejeon 34141, Republic of Korea
This is an Open Access article distributed under the terms of the Creative Commons Attribution Non-Commercial License (http://creativecommons.org/licenses/by-nc/3.0) which permits unrestricted non-commercial use, distribution, and reproduction in any medium, provided the original work is properly cited.
In this study, a convenient high-performance portable sensor platform for simple, fast, and efficient detection of H1N1 virus is demonstrated using a graphene-based transistor type architecture. A uniform graphene layer was generated and patterned by conventional methods such as lithography and vapor deposition, subsequently, electrodes were introduced on the patterned graphene layer to obtain transistor type sensor geometry. Then, the graphene surface was functionalized with antibody for H1N1 virus detection and sensor performance test. The transition curve, linearity, and sensitivity (10 pfu/mL) of the sensor component were measured. In addition, the portable H1N1 diagnosis platform for simple, fast, and convenient virus detection was produced and demonstrated. Consequently, the sensor performance was maintained in the portable sensor platform compared with the graphene-based sensor component. This presented portable H1N1 diagnosis platform showed better performance than the lateral flow assay.
Keywords: Graphene, Portable biosensor, Field-effect transistor, H1N1
The respiratory viruses may cause various symptoms and diseases such as fever, cough, bronchitis, and pneumonia. Due to the corona-19 virus pandemic, the need for ultrasensitive high-performance sensors to detect potentially prevalent respiratory viruses has increased dramatically worldwide . On the other hand, corona and influenza viruses bring similar symptoms, therefore, it is significant to develop elaborated biosensors to detect and distinguish individual virus for accurate diagnosis at early stage. Even if diverse methodologies and devices to diagnose harmful viruses have been proposed and studied, it is still a challenging task because of the sensitivity and accuracy is less competitive than the molecular diagnosis such as polymerase chain reaction . Lateral flow assay (LFA) is also a good candidate for virus detection, but its performance is still far from that required for practical use [3, 4]. Therefore, it is necessary to produce a novel biosensor showing high sensitivity and selectivity to a specific virus. Moreover, portal or mobile biosensors are more desirable to minimize infection and to suppress spread at the same time.
To date, our research group has reported extensive research activities regarding demonstration of the graphene-based biosensors detecting diverse biomaterial, such as hormone, biomolecule, virus, and pathogens [5–7]. Therefore, it has been proved that graphene can be used effectively for biosensors with sophisticated structure and geometry. Because graphene is patternable and its surface can be modified for functionalization, various sensing media such as receptor, aptamer, and antibody can be incorporated for effective target capture [8,9]. In addition, introduction of electrodes with various geometry can lead to a transistor type sensor . By using the transistor structure, sensor performance such as sensitivity, linearly, and selectivity can be elevated remarkably. Also, underlying inherent sensor characteristics such as transition curve can be obtained.
In this work, a convenient high-performance portable sensor platform was produced using graphene-based field effect transistor type sensor module for selective detection of H1N1 virus. The sensor platform was built as a 3-layer device, in which each layer conducted designated functions. Graphene was produced by the chemical vapor deposition (CVD) and played a role of conductive substrate for signal transduction. Transistor structure was obtained by conventional patterning of graphene layer and vapor deposition of electrodes. The successful formation of sensor geometry was proved using diverse instrumental analyses such as transmission electron microscopy (TEM) and Raman spectroscopy. The sensing medium, antibody was attached to the graphene surface
Copper foil (0.001 in thick) was purchased from Alfa Aesar. Glutaraldehyde (GA) and ammonium persulfate (APS) was purchased from Sigma Aldrich Co., Ltd. 950 PMMA A4 4 % in anisole, was purchased from Micro Chem Co., Ltd. H1N1 antibody (ab84612) was purchased by Abcam plc. Lateral flow assay (STANDARD Q Influenza A/B) was purchased from Biosensor, INC. High-resolution transmission electron microscopy (HR-TEM) images were obtained with FEI Tecnai instrument to figure out the monolayer graphene through wet transfer process onto copper grid. Raman spectroscopy were measured with a BX41RF-LED instrument (Olympus, 633 nm laser) to further prove the single layer of the used graphene. FT-IR were obtained with Alpha-P model for surface modification.
Single layer graphene was fabricated on the copper foil by CVD method using H2, CH4, and Ar gases. After, single layer graphene was transferred using wet transfer process, PMMA was removed by hot acetone vapor.
The electrodes were fabricated through micro electromechanical system process. First, 4 inch wafer with single layer graphene transferred was coated with photoresist followed by baking with respective condition. Photolithography was used for graphene micropatterning followed by the development of the pattern. To micropattern the graphene and to form the FET channel, reactiveion etching was used. Electrode patterning was performed through photolithography to form source/drain pattern. Metal (Cr/Au) deposition was demonstrated with E-beam to form source/drain and underwent the lift-off process using acetone. Formation of passivation layer was performed with photolithography followed by SiO2 deposition and lift-off process. After the final process, 4 µL GA (2 %) was dropped on the graphene channel for 4 h at 4 °C, then 4 µL of H1N1 antibody (Ab, 1 µg/mL) was treated on the bis(2-aminoethylene)perylene-3,4,9,10-tetracarboxyldiimide (PDA)-conjugated graphene for 4 h at 4 °C.
The influenza H1N1 virus was grown in the chicken eggs for 3 days at 37 °C, cultured virus was collected by using centrifuge 4,000 rpm, 10 min, 4 °C. The collected H1N1 virus was counted through plaque assay, the counted virus was diluted using phosphate buffered saline (pH 7.4) solution to 10 pfu/mL.
In this study, a graphene layer played several important roles such as substrate, signal transduction, and providing electrical conductivity. The graphene layer is generally advantageous for these purposes owing to its inherent properties such as high conductivity, heat dissipation, facilitated charge transport, and chemical/physical inertness [11–13]. In this experiment, a graphene layer was produced by the chemical vapor deposition method. This method is considered superior to the chemical reduction method [14–17]. A copper substrate was used after strict cleaning and chemical vapor deposition process was operated according to the designated cycle under argon atmosphere as depicted in Fig. 1(a), which was composed of annealing, growth, and cooling step. The gas feed ratios were selected as results of repetitive experiments in our group. When the chemical vapor deposition was conducted under the conditions, a single layer graphene was formed as confirmed in our previous study . TEM image of the graphene layer is shown in Fig. 1(b). A uniform and homogeneous layer was observed extensively and there was no trace of regional buckling and dewetting. Electron diffraction image in Fig. 1(b) also shows that the graphene layer possessed a highly crystalline structure, because perfect hexagonal diffraction patterns were obtained. Raman spectrum in Fig. 1(c) also supports that the nature of prepared layer was graphitic as observed at around 1600 cm−1, while a peak associated with an amorphous character also appeared at 2650 cm−1 . It was demonstrated that a graphene layer was effectively produced on the original substrate.
Figures 2(a) and 2(b) shows the digital images of the prepared sensor and its electrode structure. First, the graphene layer was patterned to an array of ribbons with a high aspect ratio using conventional lithography and etching methods. Subsequently, Au electrodes such as source and drain were introduced
The successful preparation of the sensor device was analyzed with FT-IR spectroscopy and electrical measurement. The FT-IR spectra in Fig. 2(c) show the characteristic peaks for PDA, antibody, and antibody/PDA layer. Note that the peak locations were totally different. In addition, the contribution of antibody was significantly higher than that of PDA as shown in the spectrum of the antibody/PDA (red color), because the antibody layer was located on top of the PDA layer. The ohmic relation curves in Fig. 2(d) indicates that the introduction of PDA layer increased the resistivity of the system, thus the slope of PDA/graphene (Gr) (blue color) decreased compared with that of pristine Gr. This meant that the PDA layer acted a role of resistance to the graphene layer leading to an increase in resistivity . Because the antibody molecules were also electrical insulating, therefore, this layer also acted as a resistance to the graphene layer. Consequently, the slope of antibody/PDA/Gr (red color) increased compared with other curves. This trend was consistent with the FT-IR spectroscopy result.
The transistor type sensor geometry used in this study is described in Fig. 3(a). As mentioned above, use of the gate electrode is desirable for stable signal transduction and amplification. In addition, the auxiliary container is necessary for the introduction of liquid analyte, because H1N1 viruses needs to be added as buffer solution. Even if the effective attachment of antibody to the graphene surface was confirmed by FT-IR and ohmic relation, supplementary transition curve measurement was conducted before and after antibody attachment [Fig. 3(b)]. It was clear that the transition voltage decreased approximately 0.1 V from 2.43 to 2.33 V. This was associated with the change in the electrical properties the graphene surface due to the presence of antibodies. The sensitivity tests were conducted with varying H1N1 concentration. When the antibody was absent, there was no signal associated with the antibodyvirus interactions. On the contrary, the signal increased steadily after addition of H1N1 virus from 10 to 105 pfu/mL. When a blank buffer solution was added, a peak appeared and became extinct rapidly to the original level. However, the base-line rose and maintained after addition of H1N1 virus. Conversion of the data in Fig. 3(c) as a function of concentration led to a linearity curve in Fig. 3(d). While there was no variation without antibody, the correlation was remarkable after antibody addition. Selectivity of the sensor to the H1N1 virus was already secured with the selection of antibody. The selectivity of Ab-conjugated FET sensor platform was performed by injection of another interference virus [Fig. 3(e)]. Although there is no significant signal toward interference viruses such as influenza B and SARS-COV2 spike protein, the response obviously showed toward influenza A.
The diagnosis performance of portable sensor platform is demonstrated in Fig. 4. The mobile platform is organized as a three-story stacked structure. The bottom layer contains an auxiliary battery to provide electric power for on-site operations. The middle layer has a printed circuit board (PCB), which controls the overall operation of device and have an interface with mobile phones. The top layer is a three-electrode probe to measure sensitivity and linearity of the graphene-based sensor module. Once a signal was detected by the sensor module, the result data was processed by the PCB board on the second layer and communicated to the mobile phone as a digital value. The mobile phone window indicated that it was possible to detect 102 pfu/mL virus using the mobile sensor platform. The validity of the graphene-based sensor device was further demonstrated by manufacture of lateral flow assay with the H1N1 antibody. A distinct red line appeared at control sample (“C”), but a line was not observed for “A” at the virus concentration of 103 pfu/mL. On the contrary, a red line was observed both for “C” and “A”, when the virus concentration was increased to 104 pfu/mL. Those observations indicated that the detection limit of the LFA was 104 pfu/mL and the sensitivity of the mobile sensor platform was 102 times higher than that of LFA device.
In this work, a portable diagnosis platform to detect H1N1 viruses using a graphene-based ultrasensitive high performance sensor device was manufactured and its performance was also demonstrated compared with lateral flow assay. The graphene layer prepared
This research was supported by the Defense Acquisition Program Administration (ADD-911255201).