- Open Access
An ultra-stable redox-controlled self-assembling polypeptide nanotube for targeted imaging and therapy in cancer
© The Author(s) 2018
- Received: 17 August 2018
- Accepted: 24 November 2018
- Published: 8 December 2018
- Protein nanotube
- Intermolecular disulfide bonds
- RGD motif
- Integrin targeting
The development of multimodal systems combining imaging and drug delivery components have come into focus due to their theranostic efficacy . Different materials for designing nanocarriers have been proposed such as nanogels , polymeric micelles , liposomes  along with various targeting agents . A desirable property of such systems is the ability to target the tumor cells and release the drug stably in the blood stream . To achieve this, targeted delivery systems have been proposed . The Arg-Gly-Asp (RGD) is the most widely studied and used peptide for decorating biomaterials to achieve specific targeting in the biomedical field [7–12]. This tripeptide has proved to be very effective in binding integrin receptors as efficiently as the principal integrin-binding domains within extracellular matrix (ECM) proteins such as fibronectin, vitronectin and fibrinogen . Integrins are heterodimeric cell surface receptors with alpha and beta subunits . They mediate interaction among cells via their adhesion to the extracellular matrix. There are 24 integrin heterodimers, and several of them are up regulated in various tumor types including breast cancer . The RGD motif exhibits association with several types of integrins such as α5β1, αvβ3 and αvβ5 integrins .
Our group had previously introduced nanotubular structures formed by self-assembly of a polypeptide fragment at the C-terminal end (residues 249–289) of human insulin-like growth factor binding protein-2 (hIGFBP-2249–289) . Wild type hIGFBP-2249–289 has two cysteines in its primary sequence. However, the polypeptide fragment we considered had an additional cysteine due to a mutation at R281 . The polypeptide (hIGFBP-2249–289 (R281C)) thus had an odd number of cysteines, which resulted in spontaneous self-assembly to form soluble nanotubular structures via intermolecular disulfide bonds. The nanotubes formation/disassembly can be controlled by choosing suitable redox conditions. Further, the polypeptide fragment contains a RGD motif in its sequence. Upon formation of nanotubes, an array of RGD is displayed on the surface providing a unique feature for active targeting of cancer cells through integrin binding.
We show that the multi-RGD containing protein nanotube activates integrin signalling and can be loaded with a cytotoxic drug. The drug loaded nanotubes show cytotoxicity selectively towards cancer cells and can get dissembled as it approaches the cell environment. In addition, the nanotubes can be used for cellular imaging by conjugating them with a fluorescent tag.
Monitoring the self-assembly of the nanotubes
In parallel with SDS-PAGE, at the same time points, the appearance of new molecular species in solution was monitored with the help of 2D [15N, 1H] heteronuclear single quantum correlation (HSQC) (Fig. 1b), wherein each peak in the 2D spectrum corresponds to one amino acid residue of the protein. Notably, new spectral signatures are observed with the progress in oligomerization. The intensity profiles of a few resonances depicting the decrease in the signal on day 1 and appearance of new resonances as a function of time is shown in Additional file 1: Figure S1. Note that the old resonances represent both old and new conformers for those residues which do not undergo a change in their chemical shift. The low spectral dispersion in the 2D [15N, 1H] spectrum indicates that the polypeptide fragment is largely unstructured, which was also verified in our earlier studies .
The self-assembly of the polypeptide fragment into nanotubular structures is governed by intermolecular disulfide formation as described previously . We therefore examined the oxidation of thiol group of cysteines in the polypeptide as the oligomerization progressed using 2D [13C, 1H] HSQC NMR experiment. Figure 1c shows an expanded portion of the 2D [13C, 1H] HSQC spectrum depicting the state of oxidation of one of the three cysteines, Cys 44, that is, the conversion of thiol (–SH) to disulfide (–SS–) due to oxidation. During the course of self-assembly, a significant growth in the cross peak intensity of the resonance corresponding to the disulfide state is seen with the appearance and growth of the peak at ~ 38 ppm, which is a characteristic chemical shift signature of the 13Cβ of cysteine involved in a disulfide bond . At the same time, a reduction in the intensity of thiol peaks at ~ 29 ppm is observed, which is the 13Cβ chemical shift for the reduced thiol group (–SH) of cysteine . The other two cysteines (Cys 12 and Cys 33) were also observed to undergo a similar oxidation profile. After completion, the nanotubes formed were observed using transmission electron microscopy (TEM). The TEM images show the hollow tubular forms (Fig. 1d). The images reveal an outer diameter of ~ 35 nm and an inner diameter of ~ 25 nm.
Stability of nanotubes
Effect of nanotube on integrin signalling
Nanotube-FITC conjugate for imaging cancer cells
To evaluate competitive displacement of the nanotubes by the RGD inhibitor, cells were treated for 1 h with 25 µM of inhibitor after 4 h of incubation of cells with nanotube-FITC. Figure 5 shows prominent loss of nanotube-FITC intensity after treatment with the inhibitor. On the other hand, free FITC does not show a significant decrease in its internalization profile in the presence or absence of the inhibitor in HeLa cells (Additional file 1: Figure S4). This demonstrates the specificity of nanotube-FITC interactions with integrin receptors on the cancer cell surface and underscores the potential of the nanotubes in conjugation with fluorescent dyes as a potential tool for imaging cancer cells.
To evaluate the fate of nanotube after binding to the cell surface, we treated HeLa cells for a longer period of time with the nanotube-FITC conjugate. Additional file 1: Figure S3c shows the presence of FITC signal within cellular environment at 8 h, revealing the internalization of FITC tagged nanotubes in cytoplasm. Once internalized, the reducing environment in the cell helps in dissembling the nanotubes, which provides a natural degradation pathway for the nanotubes. The disassembly of the nanotubes in vitro upon addition of a reducing agent has been shown in our earlier studies . This implies that the redox controlled self-assembling nanotubes can be utilized as an efficient drug delivery system.
Nanotube as a drug carrier: nanotube-DOX
For targeted drug delivery, the presence of multiple RGD units on the nanotubes was employed. Doxorubicin (DOX) was used to measure drug release from nanotubes under pH and redox stimuli. DOX is known to exhibit its antitumor ability by interacting with the cellular DNA in nuclei of cancer cells leading to inhibition of transcription . The hIGFBP-2249–289 nanotube constituting a combination of polar and non-polar amino acids along the frame of tubular surfaces makes it an efficient nanocarrier for DOX via electrostatic and hydrophobic interactions. DOX has two possibilities for getting entrapped, either on the exterior of the tube or in the interior (hollow space) of the tube. Zeta potential was used as a measure to probe the electrostatic interaction between DOX and the nanotubes and is shown in Additional file 1: Figure S5a–c. The zeta potential decreases from −21.4 to −12.2 mV for the DOX loaded nanotube, which can be attributed to a rise from the electrostatic attachment of DOX to the nanotube (Additional file 1: Figure S5c). An efficient loading is evident from the characteristic spectral signature seen from UV–Vis spectra in the region 490–500 nm after loading the drug (Additional file 1: Figure S5d). Nanotube-DOX was drop casted on a glass surface and allowed to dry, followed by diffusion limited spreading and the confocal imaging, which confirmed loading of the drug in the interior and exterior of the nanotubes (Additional file 1: Figure S5e). Additional file 1: Figure S5f shows the transmission electron microscopic image for the same nanotube-DOX sample when drop casted on carbon grid.
The efficiency of drug loading was estimated by UV–Vis spectroscopy. The drug loading content (LC) and drug encapsulation efficiency (EE) were estimated (as described in Materials and Methods), which are important parameters that characterize the performance of anti-cancer drug delivery system . The nanotube-DOX had a LC of 55% and EE of 25%.
In-vitro cytotoxicity of the nanotubes was measured for model cell lines: HeLa, MDAMB231 (Fig. 5) and the non-tumorigenic keratinocytes (HaCaT cells; Additional file 1: Figure S6). Cytotoxicity evaluation was done using MTT assay. First, we evaluated the biocompatibility of the nanotube alone in both the cell lines. As shown in Additional file 1: Figure S6, hIGFBP-2249–289 nanotube treatment did not cause any appreciable cytotoxicity after 48 h, suggesting biocompatibility with these cell lines. On the other hand, treatment with 5.5 μM of free DOX for 48 h could kill almost 70% of HeLa and 65% of MDAMB231 cells. In HeLa, the IC50 for nanotube-DOX is 0.69 µM and for free DOX is 0.78 µM. In the case of MDAMB231, the IC50 was 3.45 µM and free DOX is 3.97 µM. This implies that the nanotube-DOX does not affect the efficiency of free DOX encapsulated within and it is delivering the drug with minimal cytotoxicity.
Quantification of cellular uptake of DOX
Visualization of cellular uptake of DOX
Nano drug delivery systems are considered as one of the most prospective platforms for cancer therapy because of their important physicochemical properties, including increased drug accumulation in solid tumors by the enhanced permeability and retention (EPR) effect and reduced side effects . In recent years, RGD based targeted delivery systems have come into focus due to their specificity and efficacy [22–28]. For instance, multivalent RGD based peptide nanoparticles have been proposed . A self-assembled multivalent RGD-peptide array has been demonstrated for integrin binding . Functional self-assembling RGD containing peptide nanofiber hydrogel was designed for nerve generation . Disulfide based multifunctional RGD containing conjugate was introduced for targeted theranostic drug delivery . Disulphide connectivity is known to be stable in blood pool but is efficiently cleaved by cellular thiols, including Glutathione and Thioredoxin .
The present study introduces the first example of a water soluble self-assembling nanotube formed by a polypeptide fragment from a human protein, which can effectively target cancer cells providing a platform for both imaging of cells and delivery design of suitable therapeutics. The nanotube is formed via redox controlled self-assembly and the array of multiple RGD motifs present on the nanotube makes it suitable for targeting cancer cells via the integrin pathway. This was verified by the induction of integrin mediated pFAK signaling and cellular uptake in the presence and absence of an integrin inhibitor.
The polypeptide fragment is derived from a natural source i.e. polypeptide fragment of human insulin-like growth factor binding protein-2. It therefore exhibits excellent biocompatibility which is reflected in the in vitro cytotoxicity evaluation in cancer cells and non-tumorigenic cells. The intermolecular disulfide formation drives self-assembly of the polypeptide into nanotubular forms providing a stable framework. The nanotubes are stable over a wide range of temperature and pH exhibiting protease-resistance due to Cys281 mutation, which is known to be one of the proteolytic sites in human IGFBP-2 . In addition, the polypeptide hIGFBP-2249–289, being part of C-terminal domain of full length IGFBP-2 lacks major proteolytic sites [30, 31] and hence is expected to be unaffected by proteases.
Notably, no additional modification such PEGylation is needed, which is commonly used for providing biocompatibility to various nanoparticles  and physical rigidity to the nanoplatforms . Our experiments reveal the potential of this system for targeted therapeutics that includes drug delivery and imaging. In vitro drug release profiles confirm its ability to effectively deliver the cargo. Disulfide connectivity makes to redox responsive to the cellular GSH and lysosomal environment, which again renders the nanoplatform as a biocompatible redox responsive system suitable for targeted therapy. The cellular uptake of nanotube-FITC at 8 h reveals the presence of the nanotube-FITC signal in intracellular environment which can be a result of redox response of the nanotube.
Preparation of the protein nanotubes
Expression and purification of monomer
To express the monomeric form of the protein, the pGEX-6p2-IGFBP-2249–289 (C281) plasmid10 was used for transformation of BL21 (DE3) pLysE E. coli cells. The glutathione-S-transferase (GST) Gene Fusion system was used for the over expression and purification of the construct . The amino acid sequence of the polypeptide is:
The underlined first 11 N-terminal residues correspond to additional amino acids introduced by the gene fusion system as described previously . For bacterial culture, 10 ml of Luria–Bertani (LB) (Hi-media, M575) medium containing 100 µg/ml Ampicillin (Himedia, CMS645) was inoculated with a transformed colony and grown overnight at 37 °C. Later, cells were regrown to mid-log phase (OD600 nm ~ 0.6) at 37 °C with 100-fold dilution from overnight primary culture in fresh 100 µg/ml Ampicillin containing LB medium. Overexpression of the fusion protein was achieved by inducing the cells with 1 mM isopropyl β-d-thiogalactoside (IPTG, Calbiochem, 420322, India) for 6 h at 30 °C. Cells were harvested by centrifugation at 6000 rpm for 20 min, followed by cell lysis in phosphate buffered saline (PBS), pH 7.5, 1 mM PMSF (phenylmethylsulfonyl fluoride, Himedia, cat no. India), on ice by sonication in six steps, 20 s cycles each, with an intervening period of 2.0 min. Cell lysate was centrifuged (twice) at 30,000g for 45 min at 4 °C to separate insoluble cell debris and the soluble fraction containing the protein. Soluble fraction was loaded on 50% slurry of pre-equilibrated glutathione-sepharose beads (Novagen, 70541, India) with PBS at 4 °C, for 3 h on nutator. The fusion protein-bound to the affinity beads was collected by centrifugation at 4000 rpm for 5 min and washed three times with 10 bed volumes of PBS (pH 7.5, 50 mM phosphate, 50 mM NaCl). It was further washed three times with 10 bed volumes of high (25 mM HEPES, 0.05% NaN3, 0.5 M NaCl, and 0.1% Triton X-100, pH 7.5) and low (25 mM HEPES, 0.05% NaN3, 0.1 M NaCl, and 0.1% TritonX-100, pH 7.5) salts. This was followed by washing twice with cleavage buffer (1.5 M NaCl, 0.5 M Tris–HCl, pH 7.5) to remove impurities and non-specifically bound protein. On column cleavage was performed by pre-scission protease HRV-3C Protease (Human rhinovirus 3C protease cleaves at Q-G bonds, Millipore, 71493-3, India). 10 µl (20 units) of HRV-3C Protease was added for each millilitre of glutathione-sepharose bed volume, in addition with 490 µl of cleavage buffer. It was then nutated at 4 °C for 16 h. Cleaved protein was eluted by centrifuging at 4000 rpm, 5 min and further subjected to exchange with PBS buffer (pH 7.4). Purity of purified protein was confirmed by loading it on SDS-PAGE. The monomeric form of the protein was then allowed to undergo oligomerization in PBS to form self-assembled nanotubes. No external agent was necessary for initiating the oligomerization. Formation of the nanotubes was monitored by SDS-PAGE, NMR spectroscopy, TEM and Dynamic Light Scattering (DLS).
Characterization of nanotubes by NMR spectroscopy
The monomer (hIGFBP-2249–289 (Cys281)) and the nanotubes formed were characterized by NMR spectroscopy. The incorporation of NMR active isotopes i.e. 13C and 15N into the protein was achieved by growing the transformed BL21 (DE3) pLysE E. coli cells in a minimal (M9) medium containing 13C6-glucose  and/or 15NH4Cl  as the sole sources of anabolic carbon and nitrogen. Bacterial culture and purification of the proteins were carried out using previously described protocol. Protein estimation was done using Lowry’s method .
About 0.8 mM purified protein was dissolved in PBS and 5% 2H2O (for locking). All NMR data were recorded at 298 K on a Bruker Avance III 800 MHz NMR spectrometer equipped with a cryogenically cooled triple resonance probe. Two-dimensional (2D) [13C, 1H] HSQC was acquired with 8 transients and 256 complex points with a measurement time of 40 min each and 2D [15N, 1H] HSQC spectra were acquired with 2 transients and 256 complex points, with a measurement time of 10 min each. The 2D [15N, 1H] HSQCs experiment was used for time dependent monitoring of oligomerization of self-assembling hIGFBP-2249–289 (Cys281) for 3 days and 2D [13C, 1H] HSQCs were acquired to monitor the oxidation of Cysteine during self-assembly as a function of time for 8 days.
Assessment of oligomerization by SDS-PAGE
Self-assembly of hIGFBP-2249–289 (Cys281) into nanotubular structures in the initial stages was monitored by SDS-PAGE. This was carried out in parallel with the 2D [15N, 1H] HSQC NMR experiment mentioned above. Protein fractions were collected on day 1, day 2 and day 4 and stored at − 20 °C to arrest the oligomerization. Samples for SDS-PAGE were prepared in a buffer containing 240 mM Tris–HCl (pH 6.8), 8% (w/v) SDS, 0.1% Bromophenol blue and 40% (v/v) glycerol. Protein fractions taken in this buffer were heated at 96 °C for 10 min, and then centrifuged briefly. The samples were resolved on 15% SDS–polyacrylamide gels in Tris–glycine electrophoresis buffer (pH 8.3) containing 25 mM Tris base, 250 mM glycine and 0.1% SDS at 100 Volts for 120 min. Coomassie brilliant blue g-250 staining was performed for visualization of oligomeric bands.
Preparation of nanotube conjugated with FITC
C is a constant value given for a protein, MW is the molecular weight of the protein, 389 Da is the molecular weight of FITC, 195 is the absorption E0.1 % of bound FITC at 490 nm at pH 8.0 (0.35 × A495) is the correction factor due to the absorbance of FITC at 280 nm , E0.1 % is the absorption at 280 nm of a protein at 1.0 mg/ml.
Preparation of nanotube-DOX
Transmission electron microscopy (TEM)
For acquiring TEM images, the nanotubes were prepared at room temperature (25 °C) by allowing self-assembly under redox control i.e. having no reducing agent present in PBS buffer. The TEM studies were recorded under 200 kV on a Technai F-30 TEM instrument equipped with a cryoprobe. Drop casting method was used and samples were stained with Uranyl acetate (0.5%), then air dried for 1 h and desiccated for overnight on copper grids of 200 mesh.
Fluorescence spectra were acquired on a Perkin Elmer Fluorescence spectrometer. Spectra were recorded for protein samples prepared in 10 mM Tris buffer at pH 7.4 and data were recorded using a 1.0 cm path length quartz cuvette. An excitation wavelength of 280 nm (tyrosine excitation) was used having slit width 2.5 nm and emission spectra were collected from 300 to 550 nm with λmax at 340 nm.
The UV–Visible spectra were recorded for nanotube-DOX and nanotube-FITC conjugate on a Shimadzu UV-1800 UV–Vis spectrophotometer with slit width of 1 nm using a quartz cuvette having a path length of 1 cm with a wavelength range of 200–800 nm.
Dynamic light scattering (DLS)
The Nano tubular size distribution was measured on Zetasizer (Malvern, Southborough, MA, USA). The changes in the surface charges of free nanotube and nanotube-DOX were probed via the zeta potential using Nano ZS (Malvern, Southborough, MA, USA) .
Atomic Force microscopy (AFM)
AFM experiments were performed on a NX-10 AFM (Park systems) system in the non-contact mode. The protein sample was dropped onto freshly cleaved mica and incubated for 20 min. After rinsing with Milli-Q water twice, the sample was dried in a desiccator. The Al back-coated Si probe (ACTA, AppNano Inc, USA) had a resonance frequency of 300 kHz and nominal spring constant of 40 Nm−1. The tip radius was < 10 nm. Images were obtained at a scan rate of 1 Hz.
HeLa (Cervical cancer cell line), MDA-MB-231 (Breast cancer cell line) and HaCaT (Human keratinocytes) cells were maintained in growth medium consisting of Dulbecco’s Modified Eagle’s Medium (DMEM, Gibco, India) with high glucose, supplemented with 10% FBS and 1% penicillin–streptomycin. The cells were grown in 75 mm2 flasks (BD Falcon) and passaged every 3 days. All culture reagents were purchased from Thermo fisher scientific. The serum free media was used to eliminate any confounding effects from serum adsorption to the nanotubes. Within the time-period (5 h) of the experiment, no adverse cellular responses were observed from serum deprivation or serum shock after a transfer from serum containing growth media.
Cytotoxicity of nanotube, DOX loaded nanotube and free DOX were assessed in HeLa and MDAMB231 using the MTT ((3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide) assay. About 5 × 103 cells were seeded per well of a 96-well plate and allowed to attach during incubation for 24 h in a humidified incubator at 37 °C. Cells were treated with different concentrations of nanotubes, free DOX or DOX loaded nanotubes ranging from 0.2 to 6.4 μg/ml. 4 h before termination of the assay, and MTT was added. Mitochondria of viable cells oxidize MTT to produce purple Formazan crystals. Formazan crystals were dissolved in 100 μl of DMSO and incubated for 15 min with shaking at RT, protected from light. The absorbance of each well was measured at 570 nm using a microplate reader (Synergy HT, BioTek Instrument Inc., Winooski VT). Absorbance was converted to the percent cell viability and IC50 concentrations calculated as the concentration that caused 50% inhibition of cell growth.
Western blot analysis
Cells were maintained as mentioned above in 65 mm dishes. HeLa cells were serum starved for 24 h to remove the effect of serum on cells. Cells were treated with nanotubes for 1 h in serum-free DMEM. An additional set of cells was treated for 1 h with nanotubes without the integrin pathway inhibitor (RGDS) under the same conditions. For control treatments, cells were pretreated with 25 µM RGDS peptide for 1 h. Later, cells were washed once with DPBS (Dulbecco’s phosphate-buffered saline) and lysed in detergent lysis buffer (150 mM NaCl (Sigma Aldrich, USA), 0.1% SDS (Calbiochem, Germany), 0.5% NP40 (Amresco, USA), 1 mM EDTA (pH 8) and protease inhibitor cocktail, PIC (Calbiochem) with gentle vortexing at 4 °C for 20 min and centrifuged at 10,000 × g for 10 min. The soluble fraction was separated and, protein estimation was done by Bradford assay. 30 µg of total protein was dissolved in SDS sample buffer (240 mM Tris–HCl (pH 6.8), 8% (w/v) SDS, 0.1% bromophenol blue and 40% (v/v) glycerol), heated at 96 °C for 10 min and centrifuged briefly. Samples were resolved on 12.5% SDS–polyacrylamide gels in Tris–glycine electrophoresis buffer (pH 8.3) containing 25 mM Tris base, 250 mM glycine and 0.1% SDS at 100 Volts for 2 h. Proteins were then transferred from the gel onto a PVDF membrane (Immobilon-P, Millipore) in 25 mM Tris base, 250 mM glycine and 20% methanol using a BioRad transfer apparatus (BioRad Laboratories, USA). Membranes were blocked with 5% non-fat dry milk solution prepared in Tris buffered-saline, pH 7.4 containing 0.1% Tween 20 (TBST) for 1 h at room temperature and then probed with the respective primary antibody at their prescribed dilutions in 2% BSA in TBST (TBT) overnight at 4 °C. The following antibodies were used for Western blotting: Phospho FAK Tyr 397 (#3283, Cell signaling), Total FAK (#3285, Cell signaling) and β-Actin (#A5441, Sigma-Aldrich, USA). After primary antibody incubation, membranes were washed three times (15 min each) with TBST and incubated with HRP-conjugated secondary antibodies (Santa Cruz, USA) for 1 h at room temperature followed by washing three times (15 min each) with TBST. Enhanced chemiluminiscence substrate (#786-00, femto LUCENTTM PLUS-HRP, G-biosciences) or SuperSignal West Femto substrate (Pierce Protein Research Products, Thermo Scientific, USA) was added followed by exposing the membrane to X-ray film, development and fixation. Developer and fixer were purchased from Eastman Kodak Company, USA.
Confocal image acquisition and analysis
For microscopic analysis, cells were grown on sterile coverslips with all treatments performed in DMEM without serum for 1 or 4 h. Treatment was terminated by removing medium and cells washing cells twice with PBS followed by nuclear staining with DAPI (4′,6-diamidino-2-phenylindole) for 10 min at room temperature. Cells were then washed with DPBS and excess buffer was removed. Coverslips were then treated with Antifade (Thermo Fisher Scientific India Private Ltd.) and sealed to a sterile glass slide and analysed by confocal microscopy (LSM 510 Meta equipped with an Airyscan module, Zeiss, GmbH, Germany).
To quantify cellular uptake, we have used FACS based approach. 80,000 cells were seeded for each sample. Cells were first gated for auto fluorescence, 0.1–0.5% population was selected to ensure no loss of data points of experimental samples. During acquisition data, 20,000 events were recorded and analysed. Cells positive for DOX fluorescence were plotted as the bar graph. The cells were treated with free DOX and nanotube-DOX for 0.5, 1, 2 and 4 h using concentrations corresponding to their IC50 values. The cells were washed with DPBS to remove the unassimilated DOX and then trypsinized. The cell suspension was then centrifuged, and the pellet was re-suspended in 300 μl of DPBS with 0.1% of FBS. The DOX uptake was estimated by quantifying the cell populations using FACS employing Cell Quest software (using a FACS Calibur instrument, BD Biosciences, San Jose CA).
All statistical analyses were performed by using the GraphPad 5.03 statistical software and all data were plotted as mean ± SD (standard deviation). Comparisons among multiple groups were assessed by two-way ANOVA, and *p value < 0.05, **p value < 0.01, ***p value < 0.001 were considered statistically significant.
The manuscript was written through contributions of all authors. All authors have given approval to the final version of the manuscript. GA purified polypeptide sample and prepared nanotube and conjugates for NMR, SDS-PAGE, DLS, Zeta potential, fluorescence, TEM, AFM and cell biology experiments; performed NMR experiments, Cytotoxicity assay, FACS analysis, Confocal analysis and analysed the data and prepared/reviewed the manuscript. BKV cultured HeLa and HaCaT cell lines. Performed Western blot, FACS and confocal imaging experiments. MS carried out the NMR assignments of the monomer and nanotubes. Performed fluorescence experiments. AS cultured MDAMB231 and HeLa cell lines and performed MTT assay with GA, SAR provided the initial clone hIGFBP-2249–289 (R281C). PK conceived and designed the experiments, gave inputs for carrying out all cell biology experiments and helped in interpretation of data, helped in preparation/review of the manuscript. HSA conceived and designed the experiments, helped in carrying out NMR experiments and data analysis and prepared/reviewed the manuscript. All authors read and approved the final manuscript.
The NMR facility at NMR Research Centre, supported by Department of Science and Technology (DST), India is gratefully acknowledged. H.S.A. acknowledges research grant from DST. B.K.V supported by a fellowship from University Grants Commission, India, and PK laboratory acknowledges support from DBT-IISc partnership funding and infrastructure support from DST-FIST funding to MRDG. The facilities for FACS, Confocal microscopy, TEM and AFM at IISc are gratefully acknowledged. We thank Shilpa Patil for giving inputs for preliminary design of cell biology experiments and Tirupathi Ravula for his inputs in fluorescence studies.
The authors declare that have no competing interests.
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- Alibolandi M, Abnous K, Sadeghi F, Hosseinkhani H, Ramezani M, Hadizadeh F. Folate receptor-targeted multimodal polymersomes for delivery of quantum dots and doxorubicin to breast adenocarcinoma: in vitro and in vivo evaluation. Int J Pharm. 2016;500:162–78.View ArticlePubMedGoogle Scholar
- Cuggino JC, Molina M, Wedepohl S, Igarzabal CIA, Calderón M, Gugliotta LM. Responsive nanogels for application as smart carriers in endocytic pH-triggered drug delivery systems. Eur Polym J. 2016;78:14–24.View ArticleGoogle Scholar
- Wei T, Chen C, Liu J, Liu C, Posocco P, Liu X, et al. Anticancer drug nanomicelles formed by self-assembling amphiphilic dendrimer to combat cancer drug resistance. Proc Natl Acad Sci USA. 2015;112:2978–83.View ArticlePubMedGoogle Scholar
- Tomitaka A, Arami H, Huang Z, Raymond A, Rodriguez E, Cai Y, et al. Hybrid magneto-plasmonic liposomes for multimodal image-guided and brain-targeted HIV treatment. Nanoscale. 2018;10:184–94.View ArticleGoogle Scholar
- Poshteh Shirani M, Rezaei B, Khayamian T, Dinari M, Karami K, Mehri-Lighvan Z, et al. Folate receptor-targeted multimodal fluorescence mesosilica nanoparticles for imaging, delivery palladium complex and in vitro G-quadruplex DNA interaction. J Biomol Struct Dyn. 2017;35:1–14.View ArticleGoogle Scholar
- Wang M, Thanou M. Targeting nanoparticles to cancer. Pharmacol Res. 2010;62:90–9.View ArticlePubMedGoogle Scholar
- Bellis SL. Advantages of RGD peptides for directing cell association with biomaterials. Biomaterials. 2011;32:4205–10.View ArticlePubMedPubMed CentralGoogle Scholar
- Conde J, Tian F, Hernández Y, Bao C, Cui D, Janssen KP, et al. In vivo tumor targeting via nanoparticle-mediated therapeutic siRNA coupled to inflammatory response in lung cancer mouse models. Biomaterials. 2013;34:7744–53.View ArticlePubMedGoogle Scholar
- Liang G, Xinru Y, Keqing H, Yang K, Yuejian C, Ying Z, et al. Screening of novel RGD peptides to modify nanoparticles for targeted cancer therapy. Biomater Sci. 2018;6:125–35.View ArticleGoogle Scholar
- Wonder E, Simón-Gracia L, Scodeller P, Majzoub RN, Kotamraju VR, Ewert KK, et al. Competition of charge-mediated and specific binding by peptide-tagged cationic liposome-DNA nanoparticles in vitro and in vivo. Biomaterials. 2018;166:52–63.View ArticlePubMedGoogle Scholar
- Zhen F, Yan C, Chaochu C, Leming S, David HW, Zui P, et al. Near infrared fluorescent peptide nanoparticles for enhancing esophageal cancer therapeutic. Nat Commun. 2018;9:2605–16.View ArticleGoogle Scholar
- Wang Q, Yan H, Jin Y, Wang Z, Huang W, Qiu J, et al. A novel plectin/integrin-targeted bispecific molecular probe for magnetic resonance/near-infrared imaging of pancreatic cancer. Biomaterials. 2018;183:173–84.View ArticlePubMedGoogle Scholar
- Arnaout MA, Mahalingam B, Xiong JP. Integrin structure, allostery, and bidirectional signaling. Annu Rev Cell Dev Biol. 2005;21:381–410.View ArticlePubMedGoogle Scholar
- Desgrosellier JS, Cheresh DA. Integrins in cancer: biological implications and therapeutic opportunities. Nat Rev Cancer. 2010;10:9–22.View ArticlePubMedPubMed CentralGoogle Scholar
- Swain M, Thirupathi R, Krishnarjuna B, Eaton EM, Kibbey MM, Rosenzweig SA, et al. Spontaneous and reversible self-assembly of a polypeptide fragment of insulin-like growth factor binding protein-2 into fluorescent nanotubular structures. Chem Commun. 2010;46:216–8.View ArticleGoogle Scholar
- Kibbey MM, Jameson MJ, Eaton EM, Rosenzweig SA. Insulin-like growth factor binding protein-2: contributions of the C-terminal domain to insulin-like Growth Factor-1 Binding. Mol Pharm. 2006;69:833–45.Google Scholar
- Pal I, Brahmkhatri VP, Bera S, Bhattacharyya D, Quirishi Y, Bhunia A, Atreya HS. Enhanced stability and activity of an antimicrobial peptide in conjugation with silver nanoparticles. J Colloid Interface Sci. 2016;483:385–93.View ArticleGoogle Scholar
- Zheng Y, Ji S, Czerwinski A, Valenzuela F, Pennington M, Liu S. FITC-conjugated cyclic RGD peptides as fluorescent probes for staining integrin αvβ3/αvβ5 in tumor tissues. Bioconjug Chem. 2014;25:1925–41.View ArticlePubMedPubMed CentralGoogle Scholar
- Luo D, Goel S, Liu HJ, Carter KA, Jiang D, Geng J, et al. Intrabilayer 64Cu labeling of photoactivatable, doxorubicin-loaded stealth liposomes. ACS Nano. 2017;11:12482–91.View ArticleGoogle Scholar
- Biabanikhankahdani R, Alitheen NB, Ho KL, Tan WS. pH-responsive virus-like nanoparticles with enhanced tumour-targeting ligands for cancer drug delivery. Sci Rep. 2016;6:37891–904.View ArticlePubMedPubMed CentralGoogle Scholar
- Kobayashi H, Watanabe R, Choyke PL. Improving conventional enhanced permeability and retention (EPR) effects; what is the appropriate target? Theranostics. 2014;4:81–9.View ArticleGoogle Scholar
- Montet X, Funovics M, Montet-Abou K, Weissleder R, Josephson L. Multivalent effects of RGD peptides obtained by nanoparticle display. J Med Chem. 2006;49:6087–93.View ArticlePubMedGoogle Scholar
- Welsh DJ, Posocco P, Pricl S, Smith DK. Self-assembled multivalent RGD-peptide arrays—morphological control and integrin binding. Org Biomol Chem. 2013;11:3177–86.View ArticlePubMedGoogle Scholar
- Sun Y, Li W, Wu X, Zhang N, Zhang Y, Ouyang S, et al. Functional self-assembling peptide nanofiber hydrogels designed for nerve degeneration. ACS Appl Mater Interfaces. 2016;8:2348–59.View ArticlePubMedGoogle Scholar
- Babu A, Amreddy N, Muralidharan R, Pathuri G, Gali H, Chen A, et al. Chemodrug delivery using integrin-targeted PLGA-chitosan nanoparticle for lung cancer therapy. Sci Rep. 2017;7:14674–90.View ArticlePubMedPubMed CentralGoogle Scholar
- Wang Z, Dong L, Han L, Wang K, Lu X, Fang L, et al. Self-assembled biodegradable nanoparticles and polysaccharides as biomimetic ECM nanostructures for the synergistic effect of RGD and BMP-2 on bone formation. Sci Rep. 2016;6:25090–102.View ArticlePubMedPubMed CentralGoogle Scholar
- Kim JK, Anderson J, Jun HW, Repka MA, Jo S. Self-assembling peptide amphiphile-based nanofiber gel for bioresponsive cisplatin delivery. Mol Pharm. 2009;6:978–85.View ArticlePubMedPubMed CentralGoogle Scholar
- Saraf P, Li X, Wrischnik L, Jasti B. In vitro and in vivo efficacy of self-assembling RGD peptide amphiphiles for targeted delivery of paclitaxel. Pharm Res. 2015;32:3087–101.View ArticlePubMedGoogle Scholar
- Lee MH, Sessler JL, Kim JS. Disulfide-based multifunctional conjugates for targeted theranostic drug delivery. Acc Chem Res. 2015;48:2935–46.View ArticlePubMedGoogle Scholar
- Mark S, Kübler B, Höning S, Oesterreicher S, John H, Braulke T, et al. Diversity of human insulin-like growth factor (IGF) binding protein-2 fragments in plasma: primary structure, IGF-binding properties, and disulfide bonding pattern. Biochemistry. 2005;44:3644–52.View ArticlePubMedGoogle Scholar
- Soh CL, McNeil K, Owczarek CM, Hardy MP, Fabri LJ, Pearse M, et al. Exogenous administration of protease-resistant, non-matrix-binding IGFBP-2 inhibits tumour growth in a murine model of breast cancer. Br J Cancer. 2014;110:2855–64.View ArticlePubMedPubMed CentralGoogle Scholar
- Miller JS, Shen CJ, Legant WR, Baranski JD, Blakely BL, Chen CS. Bioactive hydrogels made from step-growth derived PEG–peptide macromers. Biomaterials. 2010;31:3736–43.View ArticlePubMedPubMed CentralGoogle Scholar
- Huang X, Chisholm J, Zhuang J, Xiao Y, Duncan G, Chen X, Suk JS, Hanes J. Protein nanocages that penetrate airway mucus and tumor tissue. Proc Natl Acad Sci USA. 2017;114:6595–602.View ArticleGoogle Scholar
- Atreya HS. Isotope labeling in biomolecular NMR. Netherlands: Springer; 2012.View ArticleGoogle Scholar
- Muchmore DC, McIntosh LP, Russell CB, Anderson DE, Dahlquist FW. Expression and nitrogen-15 labeling of proteins for proton and nitrogen-15 nuclear magnetic resonance. Methods Enzymol. 1989;177:44–73.View ArticlePubMedGoogle Scholar
- Lowry OH, Rosebrough NJ, Farr AL, Randall RJ. Protein measurement with folin phenol reagent. J Biol Chem. 1951;193:265–75.PubMedPubMed CentralGoogle Scholar
- Goding JW. Conjugation of antibodies with fluorochromes: modifications to the standard methods. J Immunol Methods. 1976;13:215–26.View ArticlePubMedGoogle Scholar
- Rinderknecht H. A New technique for the fluorescent labelling of proteins. Experientia. 1960;16:430–1.View ArticlePubMedGoogle Scholar
- Brahmkhatri VP, Chandra K, Dubey A, Atreya HS. An ultrastable conjugate of silver nanoparticle and protein formed through weak interactions. Nanoscale. 2015;7:12921–31.View ArticlePubMedPubMed CentralGoogle Scholar