RGD Peptide-Grafted Graphene Oxide as a New Biomimetic Nanointerface for Impedance-Monitoring Cell Behaviors

Li, Jianxia; Zheng, Leilei; Zeng, Lin; Zhang, Yan; Jiang, Lin; Song, Jinlin

doi:https://doi.org/10.1155/2016/2828512

Journal of Nanomaterials

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Abstract Introduction Materials Results and Discussion Conclusion Acknowledgments References Copyright Related Articles

Research Article | Open Access

Volume 2016 | Article ID 2828512 | https://doi.org/10.1155/2016/2828512

RGD Peptide-Grafted Graphene Oxide as a New Biomimetic Nanointerface for Impedance-Monitoring Cell Behaviors

Jianxia Li,^1,2,3Leilei Zheng,^1,2,3Lin Zeng,¹Yan Zhang,¹Lin Jiang,¹and Jinlin Song^1,2,3

Academic Editor: Rajesh R. Naik

Received11 Aug 2016

Revised07 Nov 2016

Accepted20 Nov 2016

Published25 Dec 2016

Abstract

A new biomimetic nanointerface was constructed by facile grafting the bioactive arginylglycylaspartic acid (RGD) peptide on the graphene oxide (GO) surface through carbodiimide and N-hydroxysuccinimide coupling amidation reaction. The formed RGD-GO nanocomposites own unique two-dimensional structure and desirable electrochemical performance. The linked RGD peptides could improve GO’s biocompatibility and support the adhesion and proliferation of human periodontal ligament fibroblasts (HPLFs) on RGD-GO biofilm surface. Furthermore the biologically active RGD-GO nanocomposites were demonstrated as a potential biomimetic nanointerface for monitoring cell biobehaviors by electrochemical impedance spectroscopy (EIS). By analysis of the data obtained from equivalent circuit-fitting impedance spectroscopy, the information related to cell membrane capacitance, cell-cell gap resistance, and cell-electrode interface gap resistance in the process of cell adhesion and proliferation could be obtained. Besides, this proposed impedance-based cell sensor could be used to assess the inhibition effect of the lipopolysaccharide (LPS) on the HPLFs proliferation. Findings from this work suggested that RGD peptide functionalized GO nanomaterials may be not only applied in dental tissue engineering but also used as a sensor interface for electrochemical detection and analysis of cell behaviors in vitro.

1. Introduction

For in vitro cytological analysis, cell adhesion and proliferation behaviors are influenced by the extracellular microenvironment, while the corresponding microenvironment parameters adjustment can show impacts on the biological behaviors of cells [1, 2]. In order to analyze cell biological behaviors in vitro, the cells need to be cultivated on the surface of support materials owning desirable properties, especially with good biocompatibility. In addition, physical and chemical properties of the support materials, including surface roughness, hydrophilicity, surface chemical functional groups, topological morphology, and surface charge, are able to show great impact on the behaviors of cell adhesion and proliferation on their surface [3, 4]. Therefore, design and development of a novel biocompatible surface are necessary to facilitate the study of cell behaviors of adhesion and proliferation and attracting great attention.

Graphene oxide (GO), a derivative of graphene, is hydrophilic and owns oxygen-containing functional groups (e.g., hydroxyl, epoxy, carbonyl, and carboxyl) [5–8]. Due to its excellent physicochemical properties, GO is widely used as cell growth interface for in vitro cytological analysis applications [9–11]. In addition, through various chemical modification and functionalization, GO can also be used for electrochemical and biomedical applications [12–15].

On the other hand, arginine-glycine-aspartic acid (RGD) peptide is a kind of well-known targeting ligand, which could effectively enhance integrin-overexpressing tumor cell uptake of RGD-modified nanomaterials [16–22]. In addition, RGD peptide is also known as the cell adhesion peptide, which resides in the cell attachment region of fibronectin and can promote cell adhesion, proliferation, and differentiation [23–28]. As an intensively studied cell binding sequence, RGD peptide functionalized substrates have been developed to enhance the cell behaviors and employed as tissue engineering scaffolds [29–35]. For example, Borchard and coworkers have developed an RGD-functionalized chitosan derivative for enhanced cell adhesion applications [29]. Several RGD-functionalized GO nanomaterials have been developed for biomarker detection [12], molecule analysis [36], and targeted photothermal therapy of cancers [37, 38] and other biomedical applications [14]. However, the current used biological functionalization of graphene oxide requires the introduction of a third linkage [12], which would not only increase the complexity of the experimental procedure, but also may change the physical and chemical properties of GO.

In this present work, RGD-modified GO nanomaterials were developed via the covalent linkage of the carboxyl functional groups on the surface of GO and the amine groups of RGD peptide. This synthesis procedure can not only endow the GO with desirable biocompatibility, but also maintain the physical and chemical properties of GO. Scheme 1 illustrates the modification procedure of RGD peptide onto the GO surface and the following cell analysis experiment. The GO films were firstly formed by natural drying of aqueous solution of GO. Then RGD peptides with amine functional groups were immobilized onto the GO film surface via the EDC/NHS coupling amidation reaction to form RGD-GO nanomaterials. Using human periodontal ligament fibroblasts (HPLFs) as a model, the effect of RGD-GO films on cell behaviors of adhesion and proliferation was investigated, which was further compared with that of the unmodified GO control. For further investigating their potential applications in vitro cytological analysis, RGD-GO nanomaterials were modified onto the electrode surface to study the change of electrochemical impedance spectroscopy when HPLFs were cultured on its surface with and without chemical treatment.

2. Materials and Method

2.1. Materials

GRGDSP polypeptide sequences containing RGD motif were synthesized by Scilight Biotechnology, LLC (Beijing, China). GO (30–50 nm in diameter) was provided by Nanjing JCNANO Technology Co., LTD. The received GO was dispersed in deionized water with a concentration of 1 mg mL⁻¹ and suffered ultrasonic treatment for 15 minutes before use. DMEM F-12 medium and fetal bovine serum (FBS) were purchased from Gibco (USA). Penicillin/streptomycin was provided by Hyclone. CCK-8 assay kit and Actic-Traker Green were purchased from Beyotime Biotechnology. LPS was purchased from Sigma-Aldrich. All the other reagents obtained from Sigma-Aldrich were of analytical grade and were used as received without further purification. All used solutions were prepared using deionized (DI) water (resistivity higher than 18.0 MΩ cm). ITO conductive glasses were ultrasonic-cleaned for 15 min in acetone, ethanol, and DI water and dried before use.

2.2. Characterization Technique

Fourier transform infrared spectroscopy (FT-IR) measurements were recorded on a Magma-IR 750 infrared spectrometer. Atomic force microscope (AFM) images were acquired at tapping mode by using Nanoscope III (Veeco Company) with Nanoscopy analysis software. Cell fluorescence images were obtained by confocal microscope (Leica SP8) with a magnification of 100X. Electrochemical measurements were performed on a CS315 electrochemical workstation (Correst, Co., Ltd) with a three-electrode system, in which the modified ITO conductive glass (1 mm in diameter) was used as working electrode, Ag/AgCl (sat. KCl) as reference electrode, and platinum wire as auxiliary electrode.

2.3. Preparation and Characterization of the Biofilms of RGD-GO Nanomaterials

Firstly, 100 L of GO aqueous solution (1.0 mg mL⁻¹) was dropped onto the clean surface of ITO conductive glass and then dried under the lamp. Subsequently, 100 L aqueous solution containing 173 M EDC and 15 M NHS was dropped onto the GO surface and left to react for 3 h to activate the surface -COOH groups of GO. After that the activated film was gently rinsed with DI water. RGD peptide solution (1 mg mL⁻¹) was dropped onto the activated GO surface and incubated for 4 h. For cell related test, the RGD-GO biofilms were synthesized in 24-well plates and cleaned with sterile DI water before cells were seeded. The morphologies of the GO film before and after modification were characterized by AFM. The chemical compositions of RGD-GO film were detected by FTIR measurements. Meanwhile, the electrochemical properties of RGD-GO biofilms were investigated by electrochemical impedance spectroscopy (EIS), which was performed in 0.01 M PBS. The sine wave with amplitude of 10 mV was used as the excitation signal with the scan frequency range from 1 to 105 Hz. The obtained EIS data were analyzed through the established equivalent circuit using ZView 2.0 software (Scribner Associates, Southern Pines, NC, USA).

2.4. Cell Culture

Human periodontal ligament fibroblasts (HPLFs) were obtained from human periodontal ligament tissue (Affiliated Stomatology Hospital of Chongqing Medical University, China) and were cultured in DMEM F-12 medium supplemented with FBS (10%) and penicillin/streptomycin (1%) and incubated at 37°C and 5% CO₂ in a humidified atmosphere. After incubation, the cells were collected and redispersed at the density of 1.5 10⁵/mL. Then 100 μL cell dispersions were seeded onto the RGD-GO films and cultured for 24 h. After that the nonadherent and dead cells were removed by washing with PBS buffer.

2.5. Cell Viability and Morphology Observation

Cell viability of HPLFs cultured on RGD-GO biofilms was evaluated using the well-established CCK-8 assay. RGD-GO biofilms or GO films were formed in the wells of the plate, followed by washing with sterilized DI water and 30 min UV treatment. Then cells were seeded into 24-well plates and cultured for 2, 24, 48, and 72 h. After primary medium was discarded, the culture medium containing 10% CCK-8 was added and incubated for 2 hours. Then 200 μL medium was transferred to a new 96-well plate. The results were expressed as absorbance values through a microplate reader (Bio-Tek Instruments, Inc.) at the wavelength of 490 nm.

For cell morphology observation to study the cell adhesion and proliferation behaviors, 100 μL cell dispersions were seeded onto the RGD-GO-modified cell plate at the density of 1.5 10⁵/mL. After 24 h incubation, the adhered cells were fixed with 4% paraformaldehyde for 10 min. Then cytoskeleton and cell nucleus were stained with Actin-Tracker Green and DAPI, respectively. Fluorescence images of the cells were captured using a laser scanning confocal microscope and the data were analyzed by image J software. The cells cultured on GO films treated through the similar protocol were used as control.

2.6. Electrochemical Impedance Analysis

For this test, 100 L of HPLFs dispersions (1.5 10⁵/mL) was dropped onto the surface of RGD-GO-modified ITO electrode, Then the electrode was cultured at 37°C and 5% CO₂ in a humidified atmosphere to make the cells adhesion and proliferation for 2, 24, 48, and 72 h, respectively. After that the surfaces of the electrode were washed with PBS several times to remove the weakly attached cells and dead cells. EIS was performed in 0.01 M PBS (pH = 7.4) buffer. Meanwhile, the RGD-GO-modified ITO electrode without cell seeded was used as a blank control and GO-modified ITO electrode seeded with cells was used as an experimental control.

For analysis of the inhibition effect of LPS on HPLFs proliferation, 1 mL HPLFs cells (1.0 10⁵ cells mL⁻¹) were seeded on the RGD-GO-modified ITO electrode and incubated for 24 hours at 37°C. Then different concentration of LPS was added into cell and incubated for another 24 hours. Then EIS measurement was conducted in PBS. All EIS measurement parameters and data processing were same as prementioned. The control group was cells without LPS treatment. The LPS induced impedance change was calculated as , where is the highest impedance change value at a special frequency for LPS treated group and is for LPS free group. In parallel, the effect of LPS on HPLFs cells viability was analyzed using CCK-8 assay. Briefly, HPLFs were seeded into 96-well plates (1.0 10⁵ cells/mL); 24 h after seeding, cells were treated by different concentration of LPS for 24 hours. Then, 10 L of CCK-8 solution was added into each well and incubated at 37°C for 1 h. The absorbance value was recorded at 450 nm wavelength with a microplate reader (Varioskan, Thermo Scientific). The relative cell viability was characterized by , where and refer to absorbance value of LPS treatment group and untreated group, respectively.

3. Results and Discussion

3.1. Synthesis and Characterization of RGD-GO Biofilms

The preparation process of RGD-GO biofilms was shown in Scheme 1. The GO films were formed by natural drying of aqueous solution of GO. Then RGD peptides with amino functional groups were immobilized onto the GO film surface owning abundant surface carboxyl groups via the EDC/NHS-activated amidation reaction to form RGD-GO biofilms. Figure 1 shows the AFM images of GO and RGD-GO film deposited onto ITO electrode surface. From Figure 1(a), it can be seen that GO nanosheets were stacked with each other, resulting in a loose and porous structure. It can also be known that the line roughness of GO film was nm, and the surface roughness was nm. When RGD peptides were covalently bounded onto the GO films, their surface morphology displayed similar characterization without obvious difference. From the data, it can be known that the line roughness of the formed biofilms was nm, and the surface roughness was nm. The increase of roughness of the RGD-GO biofilms could be attributed to the surface grafting of RGD peptides.

(a)

(b)

The covalent bonding of RGD peptides onto the GO surface could be further confirmed by FTIR measurements. Figure 2 shows the FTIR spectra of GO and RGD-GO films. The FTIR spectrum of GO displays several absorption peaks of oxygen-containing functional groups, such as C-OH stretching vibration peak at 1732 cm⁻¹ and -OH vibration peak at 3429 cm⁻¹. The peaks at 1078, 1396, and 1630 cm⁻¹ were attributed to the absorption peak of epoxy group (C-O-C), O-H deformation, and carbonyl group (C=O), respectively [39]. By contrast, the FTIR spectrum of RGD-GO biofilms clearly displayed two new peaks at 1533 and 1290 cm⁻¹, corresponding to the characteristic peaks of amide I and amide II of the RGD peptides [40]. It was also noticed that the absorption peak at 1732 cm⁻¹ assigned to carboxyl groups (C-OH) became weak. This may provide another evidence for the successful modification of RGD peptide, during which process many of the surface carboxyl groups of GO films would be consumed.

The EIS measurement is a noninvasive material interface analysis tool since it uses low amplitude AC voltage (~10 mV) as the detection excitation signal [41, 42]. Figure 3(a) shows EIS complex curves of the bare ITO electrode, GO-modified ITO electrode, and RGD-GO-modified ITO electrode. The results for these three electrodes showed distinguishable difference, indicating that each electrode owned distinct electrode impedance property. To figure this out, Randle’s equivalent circuit (with Warburg element equivalent circuit) was employed for fitting the impedance spectroscopy data (Figure 3(b)). Randle’s equivalent circuits are usually used to explain the electrode interface system containing bilayer capacitance and Faraday impedance [43].

(a)

(b)

(c)

Herein, taking into account of the film surface roughness, the interference of electrolyte composition to reaction rate, the uneven current distribution produced by nonstandard electrode placement, and so on, constant phase element was used to replace traditional Randle’s equivalent circuit in order to obtain a better fitting [44]. Wherein, represented the ohmic resistance of the electrolyte solution, represented charge transfer resistance, CPE represented constant phase element ( = 1/), and represented Warburg impedance. By fitting the EIS data with equivalent circuit, the values of respective elements corresponding to each electrode were obtained. Figure 3(c) shows that there was an obvious change in and CPE-. When the GO films were deposited onto the ITO electrode surface, the value decreased from 1.06 Ω to 2.14 Ω, and the CPE- value increased from 2.8−6 C to 3.6−6 C. This could be attributed to the fact that the deposition of GO improved the dielectric constant and increased the surface area of electrode-electrolyte interface bilayer capacitance. In RGD-GO case, the value increased to 4.74 Ω compared to that of the GO-modified electrode. This may be caused that the negatively charged RGD peptides repelled electron transfer via electrostatic force. Meanwhile, the CPE- value further increased to 5.3−6 C, indicating the further increase of the dielectric constant and the electrode interface area. These results were consistent with the obtained AFM images. These results not only confirmed the successful modification of RGD-GO films onto the electrodes, but also made it possible to realize the quality control of the manufacturing process of the RGD-GO-modified electrodes.

3.2. Cell Viability and Morphology Observation

The biocompatibility of RGD-GO biofilms was investigated by cell viability test and cell morphology observation. The results of cell viability for HPLFs cultured on the GO films and RGD-GO biofilms were shown in Figure 4. It can be seen that cell viability gradually increased with the culture time, indicating that both GO films and RGD-GO biofilms had good biocompatibility. In addition, HPLFs on RGD-GO biofilms showed better cell viability than that of GO films with significant difference.

Cell morphology was further studied to confirm the biocompatibility of the formed films. As shown in Figure 5(a), cells fully spread on the surface of both films and exhibited well-structured cytoskeletons. The adhesion and proliferation ability of HPLFs were significantly improved by the modification of RGD peptide. The cell spreading area and cell density cultured on RGD-GO biofilms were showing significant difference when compared to that of on GO films (Figures 5(b) and 5(c)). These results suggested RGD-GO biofilms could enhance adhesion and proliferation behaviors of HPLFs more effectively than GO films. This could be attributed to the immobilized RGD peptides, which owned good biocompatibility and could endow GO films biomimetic functions. The RGD peptides could act as cell binding points to fulfill the role of extracellular matrix supporting the biological behavior of cells, which could increase the cell capture ability of the films and further promote cell adhesion and proliferation.

(a)

(b)

(c)

3.3. Preliminary Application of RGD-GO for Impedance-Monitoring Cell Behaviors

For this analysis, it is a prerequisite that HPLFs could be cultured onto the RGD-GO-modified ITO electrode. The morphologies of HPLFs cultured on the functionalized electrode for different times were observed using microscope (Figure 6). It can be seen that after 2 h incubation HPLFs displayed a successful adhesion onto the surface of the RGD-GO-modified ITO electrode. With the increase of the incubation time, cells extended pseudopodia and started spreading. The cells completely spread after 24 h incubation and showed good proliferation after 48 h incubation. The density of HPLFs obviously increased after 72 h incubation and no apoptosis was observed.

3.4. Cell Proliferation Detection

In vitro assessment of cell proliferation is the most basic experiment for tissue engineering [45, 46]. EIS is simpler and allows direct assessment compared with traditional cell growth assays such as MTT, BrdU labeling, and trypan blue staining. The basic principle and more details of EIS for monitoring the changes during cells adhesion and proliferation have been reported [47, 48]. Cells adhesion and growth on the surface of a planer electrode can hinder unrestricted current flow from the electrode into the electrolyte and increase the overall electrode impedance like insulating particles [49, 50]. When the frequency of the ac signal is sufficiently high, a certain amount of current can capacitively couple through the plasma membranes and get across the cell layer on transcellular pathways. However, for most low frequency, the current has to bypass the cellular bodies. Accordingly, trans- and paracellular currents impedance originate not only from the plasma membrane together with the integrity of intercellular tight junction, but also from the cell-substrate adhesion zone. Comparing with the well-developed transepithelial/transendothelial electrical resistance (TEER), used only for measurement the cell barrier integrity of endothelial and epithelial monolayer [51, 52], EIS can obtain more integrated information of cell morphological changes during the overall process of cell adhesion, spreading, and proliferation on the surface of specific substrates. In addition, since the trans- and paracellular impedance are dependent on the frequency of the ac signal, they can be separated and quantified individually by fitting the experimental impedance data to a mathematical model. In this study, based on its excellent biocompatibility and special electrochemical property, RGD-GO film was employed as a sensor interface, instead of traditional gold-film electrode; for impedance-monitoring HPLFs proliferation (Figure 7(a)) is a Nyquist plot of RGD-GO-modified electrode system with HPLFs cultured on its surface for different incubation times. It can be seen that the charge transfer control feature semicircle significantly changed in the high frequency region of impedance spectroscopy with HPLFs adhesion and proliferation on the electrode surface. The diameter of the semicircle increased with the process of cell proliferation (Figure 7(a)). For the control group, the impedance spectroscopy of blank electrodes did not show charge transfer control feature semicircle after incubation in culture medium at different times (Figure 7(b)). These results suggested that the change of impedance was caused by the cell adhesion and proliferation behaviors. The appearance of EIS charge transfer control feature semicircular was related to plasma membrane capacitance characteristics and poor conductivity of the cells on the electrode surface [53]. Meanwhile, the behaviors of cell adhesion and proliferation on the electrode interface could increase the resistance of electron transfer and slow down the speed of charge transfer, making this a feasible method to take advantage of impedance spectroscopy to study cell behaviors [50, 54].

(a)

(b)

(c)

(d)

Then, the equivalent circuit model was used to quantify the cell adhesion and proliferation behaviors on the ITO electrode. According to the change of impedance spectroscopy before and after cell incubation, cells were equivalent to a circuit that was connected in series by a parallel circuit and a component. RGD-GO-modified ITO electrode was fitted by an equivalent circuit of Randle’s circuit containing the Warburg resistance element. So the whole electrode system could be considered as an equivalent circuit connected in series by the electrode equivalent circuit and the cell equivalent circuit (Figure 7(c)). Where was cell-electrode gap resistance, was intercellular resistance and was cell membrane capacitance.

The impedance data were analyzed using the nonlinear least squares curve fitting method, as depicted in Figure 7(d). With the adhesion and proliferation of cells on the RGD-GO-modified ITO electrode surface, the values of rapidly decreased within the incubation time of 2–24 h. This value reached to a stable range of 8.2 to 8.5 nF when cells completely spread out to form cell monolayer at the incubation time of 48–72 h. The final value was just slightly higher than that of the GO-modified ITO electrode, which was stable at the range of 7.6–8.1 nF. This change was effected by cell thickness, cell spreading area, and the number of ion channels of cells [55]. In addition, with HPLFs adhesion and proliferation on the RGD-GO-modified ITO electrode surface, the value of sustained increasing and reached to a maximum value around 338 Ω after 72 h incubation. Since value reflects the gap resistance between cell and electrode surface, the larger the value, the smaller the gap between cell and electrode surface, indicating the strength of the cell behaviors of adhesion and proliferation [56, 57]. The measured value of the RGD-GO-modified ITO electrode surface was higher than that of the GO-modified ITO electrode, indicating that RGD modification could enhance the cell behaviors and the related biomimetic capacity properties of the electrode. The value of continued to increase with incubation time for both electrodes, which indicated that the gap between cells became narrow, and the degree of cell proliferation increased [56]. The measured values of the RGD-GO-modified ITO electrode were higher than that of the GO-modified ITO electrode, especially at the incubation time of 48 h. At the formation of cells monolayer at 72 h, reached to the maximum value of 1382 Ω for the RGD-GO-modified ITO electrode. These results suggested that cells displayed a better proliferative activity on the RGD-GO-modified ITO electrode surface than on the GO-modified surface, which was in accordance with the previous data of cell counting. The formed RGD-GO biofilms could be used as a promising electrochemical impedance detection interface.

3.5. Assay of the Inhibition Effect of LPS on HPLFs Proliferation

LPS is one of the most primary aetiological agents known to associate with deep periodontal tissues destruction and periodontal disease [58, 59]. HPLFs are the main part of the periodontal ligament which protects the roots of the tooth and anchor them to the jaws. Therefore, understanding the inhibition effect of the LPS on the HPLFs proliferation is meaningful. In this work, for demonstrating the versatility of the proposed RGD-GO film based EIS sensors, LPS was used as a model to investigate the effect of LPS on HPLFs proliferation. The Nyquist plots responses and impedance frequency responses for LPS treatments were recorded and shown in Figures 8(a) and 8(b), respectively. Concentration-dependent inhibition effect on LPS proliferation could be observed by comparing the diameter of the well-defined semicircle at high frequency in Nyquist plots and impedance value at special frequency in Bode plots. With the increase of LPS concentration, the diameter of the semicircle decreased and the overall impedance value decreased as well, which was due to the constriction of cell plasma membrane and cell detachment from the electrode surface under the condition of cell apoptosis induced by LPS. Additionally, the quantification of the inhibition effect of LPS can be calculated from the maximum impedance changes at a frequency of 1.15 kHz, and the relationship curves between the relative cell viability and concentration of LPS were shown in Figure 8(c). From Figure 8(c), it can be seen that the obtained EIS results show similar trend with those from traditional colorimetric CCK-8 assay. However, some slight differences between the two results existed and the underlying cause has yet be fully elucidated, but two main hypotheses presented. Firstly, the proposed EIS cell biosensor used the biomimetic RGD-GO film as the cell growth substrate, while CCK-8 assay adopted polystyrene as the cell growth substrate. The different biophysical-chemical properties of both substrates might regulate cell activity and in turn affect cellular response to LPS. Secondly, the essential difference between these two methods, that is, one based on morphological changes of cells immobilized on electrode surface and the other based on the enzymatic cleavage of the CCK-8 to formazan by cellular mitochondrial dehydrogenases present in viable cells, might be the primary cause for the difference between results. Therefore, for obtaining more reliable results using the proposed EIS cell sensor, control experiments, parallel groups, and strict quality control are needed. Furthermore, despite their diversity, the proposed EIS cell biosensor has several advantages over traditional optical methods, including low-cost (not needing much more expensive instruments and reagents), noninvasive, laborsaving, and higher precision (RSD < 5% for the proposed EIS cell sensor versus RSD < 10% for CCK-8 assays).

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Figure 8

EIS detection of inhibition effect of the LPS on the HPLFs proliferation on RGD-GO-modified ITO microelectrode. (a) Nyquist plots responses recorded after addition of LPS with different final concentrations for 24 h. (b) Impedance frequency responses recorded after addition of LPS with different final concentrations for 24 h. The arrow shows the frequency where the maximum impedance change is induced by LPS. (c) Inhibition effect of the LPS on the HPLFs determined by the proposed EIS cell biosensor and colorimetric CCK-8 assay. ().

4. Conclusion

In this reported work, RGD-modified GO nanomaterials were successfully synthesized and characterized. The resulting RGD-GO possesses good stability and special electrochemical property and promotes the adhesion and proliferation behaviors of HPLFs. As a preliminary application, the formed RGD-GO nanomaterials can be deposited onto the ITO electrode and possess the potential as a nanointerface for studying the adhesion and proliferation behaviors of HPLFs by EIS technique. Besides, the inhibition effect of the LPS on the HPLFs proliferation has been demonstrated. Therefore, the RGD-GO nanomaterial can be used not only as a scaffolder for dental tissue engineering, but also as a promising biosensor interface to study the physiological and pathological behavior of living cells.

Competing Interests

The authors declare that there are no competing interests regarding the publication of this paper.

Acknowledgments

Lin Zeng is thankful for the support of Health Bureau of Chongqing (20142134).

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Copyright © 2016 Jianxia Li et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

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