Photothermal therapy of melanoma tumor using multiwalled carbon nanotubes
Received 14 February 2017
Accepted for publication 29 April 2017
Published 20 June 2017 Volume 2017:12 Pages 4509—4517
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 3
Editor who approved publication: Prof. Dr. Thomas J. Webster
Zahra Sobhani,1,2 Mohammad Ali Behnam,3 Farzin Emami,3 Amirreza Dehghanian,4 Iman Jamhiri5
1Quality Control Department, Faculty of Pharmacy, 2Center for Nanotechnology in Drug Delivery, Faculty of Pharmacy, Shiraz University of Medical Sciences, 3Opto-Electronic Research Center, Electrical and Electronics Engineering Department, Shiraz University of Technology, 4Pathology Department, 5Stem Cell Technology Research Center, Shiraz University of Medical Sciences, Shiraz, Iran
Abstract: Photothermal therapy (PTT) is a therapeutic method in which photon energy is transformed into heat rapidly via different operations to extirpate cancer. Nanoparticles, such as carbon nanotubes (CNTs) have exceptional optical absorbance in visible and near infrared spectra. Therefore, they could be a good converter to induce hyperthermia in PTT technique. In our study, for improving the dispersibility of multiwalled CNTs in water, the CNTs were oxidized (O-CNTs) and then polyethylene glycol (PEG) was used for wrapping the surface of nanotubes. The formation of a thin layer of PEG around the nanotubes was confirmed through Fourier transform infrared, thermogravimetric analysis, and field emission scanning electron microscopy techniques. Results of thermogravimetric analysis showed that the amount of PEG component in the O-CNT-PEG was approximately 80% (w/w). Cell cytotoxicity study showed that O-CNT was less cytotoxic than pristine multiwalled nanotubes, and O-CNT-PEG had the lowest toxicity against HeLa and HepG2 cell lines. The effect of O-CNT-PEG in reduction of melanoma tumor size after PTT was evaluated. Cancerous mice were exposed to a continuous-wave near infrared laser diode (λ=808 nm, P=2 W and I=8 W/cm2) for 10 minutes once in the period of the treatment. The average size of tumor in mice receiving O-CNT-PEG decreased sharply in comparison with those that received laser therapy alone. Results of animal studies indicate that O-CNT-PEG is a powerful candidate for eradicating solid tumors in PTT technique.
Keywords: Photo thermal therapy, CNTs, hyperthermia, PEG, melanoma
Cancer still remains one of the world’s most disastrous diseases. Conventional cancer treatments like surgical intervention, radiation, and chemotherapeutic drugs also kill healthy cells and cause toxicity to the body.1 A promising area that is making revolutionary strides in methods of cancer treatment is cancer nanotechnology, which includes the integration of fields like engineering, material sciences, optics, pharmaceutics, chemistry, and physics with cancer biology.2
Hyperthermia is a simple method of cancer therapy in which irradiation of near infrared (NIR) light increases the local temperature of tumor and disturbs the cancer cells. Internalized nanoparticles (NPs) to the tumor sites could be stimulated by laser irradiation, to produce localized heat in the range of 40°C–45°C so as to destroy cancer cells.2–5 NPs such as single-walled carbon nanotubes,6 multiwalled carbon nanotubes (MWNTs),7,8 graphene,9,10 iron oxide NPs,11 gold nanorods,12 and gold nanoshells13,14 are used to transform NIR radiation to vibrational energy. Therefore, heat generation based on laser irritation could elevate malignant tissues’ temperature and destroy tumors.15 Inducing high temperature for a sufficient time causes physical damage like protein denaturation and membrane lysis and could increase oxidative stress, finally causing coagulative necrosis or apoptosis.5,15 Utilizing the NIR light in the range 700–1,100 nm to induce hyperthermia is really efficient because biological systems mainly lack chromophores to absorb NIR light. NIR wavelength, compared to other range of wavelengths, is more transmissive through the body and is poorly attenuated by biological systems.16,17 By localization and excitation of potent NPs in the tumor region, lesions could be cured without direct access to the tumor site and selectively destroyed.18 This method promises to ablate recurrent, unconventional, and inaccessible tumors. The wide electromagnetic absorbance spectrum of carbon nanotubes (CNTs) creates exceptional properties compared to other plasmonically heated nanomaterials (like gold nanoshells and nanorods) that is dependent on the size and shape of CNTs.19 CNTs promise an extraordinary combination of attributes in improving the next generation of photothermal agents because of their strong ability to transform NIR radiation into heat.20 NIR exposure of CNTs excites electrons to the excited state and releases vibrational energy through heat, which could be used to induce cell death.21,22 Studies show that CNTs can achieve thermal destruction using tenfold-lower doses in solution and using threefold-lower laser power than that required for gold nanorods,23 and these also indicate that MWNTs are more potent than bulk single-walled nanotubes in transferring the NIR light into heat.2 Studies by Murphy et al24 reported that the inflammation and fibrosis induced by CNTs could be reduced by shortening the length of CNTs. One of the conventional methods to shorten and exfoliate the CNT bundles is oxidation. Oxidation also enhances the wettability, surface reactions, functionality, and cell penetration of CNTs.25–27 To improve the poor dispersibility of CNTs into aqueous media, different hydrophilic polymers can be used. Functionalization of CNTs with polyethylene glycol (PEG) moieties (PEGylation) has been utilized to enhance the solubility, biocompatibility, and cell membrane penetration of the moieties.28,29
In this study, at first we solubilized oxidized-MWNTs with PEG to enhance their hydrophilicity and biocompatibility and then evaluated their efficacy in treatment of melanoma via hyperthermia treatment in vivo.
Materials and methods
Purified MWNTs (number of walls: 3–15, outer diameter: 5–20 nm, length: 1–10 μm) were purchased from Plasmachem (Berlin, Germany). PEG1000 was purchased from Sigma-Aldrich (St Louis, MO, USA). All solvent were of analytical grade.
Preparation of CNTs-PEG
For wrapping of CNTs with PEG, the CNTs should be oxidized first. For oxidation of CNTs, 1 g of MWNTs was sonicated with 20 mL nitric acid and sulfuric acid solution (1:3 v/v) for 30 minutes. Then, the solution was refluxed for 21 hours at 100°C. The solution was diluted with 1 L of deionized water, then filtered, and finally washed till the pH adjusted to 6. The filtrate was dried in an oven at a temperature of 40°C for 24 hours.30–32 The oxidized-CNTs (O-CNTs) were ready for following steps.
50 mg of O-CNTs was added to 50 mL of deionized water containing 500 mg of PEG1000.33 The mixture was sonicated for 3 minutes and stirred overnight for wrapping hydrophilic polymer around the O-CNTs. The resulting solution was centrifuged at 4,000 rpm for 10 minutes to remove any aggregates, and the supernatant containing O-CNT-PEG was collected. Excess PEG was removed by dialysis.
Characterization of O-CNT-PEG
IR measurements were performed by (Perkin Elmer Spectrum One, Fourier transform infrared [FT-IR]; Shelton, CT, USA). Thermogravimetric analysis (TGA) was carried out (BAHR-Thermoanalyse Gmbh, TGA; Hüllhorst, Germany) under dynamic atmosphere of an inert gas (N2) at 30 mL/min (room temperature). Field emission scanning electron microscopic (FESEM) analyses were performed (TESCAN MIRA 3-XMU, FESEM; Brno, Czech Republic). UV–Vis absorption of O-CNT-PEG was analyzed (PG instruments Ltd., T80+ UV–Vis spectrophotometer, Lutterworth, UK) to determine the best photoabsorption wavelength for excitation.
Cytotoxicity assay for O-CNT-PEG
To verify the cytotoxicity of modified CNTs, the cytotoxicity of MWNT, O-CNT, and O-CNT-PEG was assessed by the standard MTT assay. Two human cell lines, human cervical cancer cells (HeLa) and human hepatocellular carcinoma cell line (HepG2), were purchased from the National Cell Bank of Pasteur Institute (Tehran, Iran). HeLa and HepG2 were cultured in Roswell Park Memorial Institute medium (RPMI)-1640 medium supplemented with 10% fetal bovine serum and 1% penicillin–streptomycin at 37°C in a humidified incubator with 5% CO2. Cells in the exponential growth phase were seeded in 96-well plates at a density of 1×104 viable cells/well. After overnight incubation, cells were exposed to different concentrations of MWNT, O-CNT, and O-CNT-PEG. After 24 hours, 20 μL of MTT (5 mg/mL) and 100 μL of medium were introduced. The plates were incubated for 3–4 hours. The formazan crystals in each well were dissolved in 100 μL of dimethyl sulfoxide. After complete solubilization of the dye, plates were read at 570 nm against 690 nm on an ELISA reader. The percentage of cell viability was calculated. The cell viability was estimated as the reduction of values from a dimethyl sulfoxide control, and the values were the mean of three different experiments.
The metastatic murine melanoma cell line B16/F10 (NCBI C540 was purchased from the National Cell Bank of Pasteur Institute of Iran, Tehran, Iran) was cultured in RPMI 1640 medium, under 5% CO2 at 37°C. Then it was supplemented with 10% fetal bovine serum, 100 IU/mL of penicillin, and 100 μg/mL streptomycin.
For tumor induction, female C57BL/6J mice that were inbred, weighing 20–30 g, and aged 6–8 weeks were selected. Murine melanoma cells at a count of 106–107 were suspended in 200 μL culture medium and injected hypodermically. This examination was done in the Center of Experimental and Comparative Medicine, Shiraz University of Medical Sciences, Shiraz, Iran and was cleared by the Ethical Committee of Shiraz University of Medical Sciences generously. Mice selection, methods of care, and sacrificing were the same and adhered to the guideline of Animal Care Committee of Iran Veterinary Organization. Experiments were done under aseptic situation, and the protocol of anesthesia, postoperative care, and surgical methods were the same for all mice.
In vivo photothermal therapy (PTT) of tumors
The therapeutic effect of ablation with O-CNT-PEG and laser irradiation was evaluated by monitoring the size of tumor inoculated in mice. Two weeks after melanoma cell line injection, the tumors had grown adequately (about 1 cm3) to start hyperthermia therapy. The mice were randomized into 3 groups (n=5) and anesthetized with a combination of ketamine 10% (100 mg/kg) and xylazine 2% (10 mg/kg). After sedation, the hair on tumor was shaved and the skin was cleansed. Tumor sizes were measured using a caliper and evaluated with an ultrasonography machine (Ultrasonix SonixOP; Burnaby, BC, Canada) before the treatment and 3 days after the treatment. The tumor size was estimated with the following Equation:
where L and W represent length and width of the tumor, respectively.
The mice received treatment as follows:
Group I (O-CNT-PEG): O-CNT-PEG (1 mg/mL) was injected into the tumor at a dose of 200 μL/cm3 (tumor volume).
Group II (Laser therapy): laser therapy was done without any pretreatment with NPs.
Group III (Control): did not receive any treatment.
The tumor area in groups I and II were irradiated using an 808 nm continuous-wave NIR laser diode 808-2W with the intensity of 8 W/cm2 and spot size of 0.25 cm2 for 10 minutes. After treatment, all mice were sacrificed, the tumor size was measured, and the mass was excised for histological studies.
Data are expressed as mean ± SD. Significant differences of the values were statistically tested using paired-sample t-test in each group. Multiple comparisons at multiple time points were tested using analysis of variance with repeated measures. The statistical analyses were performed by SPSS® statistical software, version 20.0 (SPSS Inc., Chicago, IL, USA) for Windows®. A P-value of <0.05 was regarded as significant.
Preparation and characterization of O-CNT-PEG
TGA measurements and FT-IR spectroscopy were employed to determine wrapping the CNTs with PEG chains. In the FT-IR spectrum of O-CNT, the peaks observed at 3,409.36, 2,870, and 1,750 cm−1 were correlated to O-H (carboxylic acid), C-H, and C=O bonds, respectively (Figure 1). In the O-CNT-PEG, PEG-related peaks covered the peaks of O-CNT. Increase in the intensity and width of O-H peak (3,409.69 cm−1), C-H peak (2,872.13 cm−1), and C-O peak (1,108 cm−1) were due to the presence of PEG. Indeed, the peaks at 1,250, 1,298 and 1,351 cm−1 were due to C-H scissoring and bending in PEG (Figure 1).
Figure 1 FT-IR spectrum of O-CNT and O-CNT-PEG.
TGA measurements provided further evidence regarding the content of polymer on the surfaces of CNTs. Figure 2 shows the TGA thermograms of O-CNT and O-CNT-PEG. Wrapped PEG started to thermally degrade at 330°C, and at 450°C decomposed completely. The plateau in the thermogram of O-CNT-PEG trace after 450°C was attributed to the carbon nanotube. According to the weight loss region, the amount of O-CNT component in the O-CNT-PEG was approximately 20% (w/w).
Figure 2 TGA thermo grams of O-CNT and O-CNT-PEG.
Morphological changes of functionalized CNTs were assessed by FESEM (Figure 3). It was observed that a continuous layer of PEG had been formed on the surface of O-CNTs.
Figure 3 FESEM images of functionalized CNTs.
These results indicated that PEG chains were successfully wrapped onto the CNT surfaces. Therefore, the solution of O-CNT-PEG was stable in water without aggregation over long periods of storage (several months).
UV-Vis absorption spectrum of O-CNT-PEG is shown in Figure 4. According to this spectrum curve, the maximum absorption wavelength of O-CNT-PEG was in the range of 670–940 nm. Penetration of light in skin and cells in the NIR spectrum is more convenient than visible spectrum.36–38 Therefore, the wavelength of 808 nm was chosen for photoexcitation.
Figure 4 UV–Vis absorption spectrum of O-CNT-PEG.
Cell cytotoxicity of O-CNT-PEG
The cytotoxicity profile of MWNT, O-CNT, and O-CNT-PEG against the cell lines was assessed to confirm the modification of CNTs with PEG. For this purpose, the cytotoxicity of MWNT, O-CNT, and O-CNT-PEG was evaluated using the MTT assay. HeLa and HepG2 cells were exposed to that NPs at different concentrations for 24 hours and MTT assay was carried out. As shown in Figure 5A and B, at concentrations of up to 1,000 ng/mL, the O-CNT-PEG NPs showed relatively low toxicity in both cell lines. Presence of PEG around the CNTs increased the cell viability significantly. Oxidation and then coating of MWNTs with PEG increased the cell viability in HepG2 and HeLa cell lines.
Figure 5 MTT assay of MWNT. O-CNT, and O-CNT-PEG against HepG2 (A) and HeLa (B) cell lines.
PTT of tumors
The in vivo effects of O-CNT-PEG with laser irradiation on the subcutaneously implanted murine melanoma were evaluated by monitoring the tumor size.
Tumor sizes were recorded before and 3 days after the irradiation. Data were analyzed, and significant difference was seen between groups I and II. The shrinking of tumor size in O-CNT-PEG group is clearly evident in Figure 6. As can be seen from this figure, the tumor size before and after the treatment in each mouse was recorded. In the control group, it is clear that the tumor growth was faster where the initial size was greater, but in the O-CNT-PEG group the tumor size was decreased in all cases. By using O-CNT-PEG NPs in laser therapy, the large tumor (975 mm3) shrank to a small size (125 mm3), while in the control group the mouse with a tumor of 1,080 mm3 died before day 3 of the study. In the laser therapy group, the tumors grew at a slower rate, and in two cases the size of the tumors decreased. This indicates that the average size of tumor before and 3 days after the treatment was increased in the control group (from 406 mm3 to 745.31 mm3, respectively), but these values decreased in the O-CNT-PEG group (from 566.4 mm3 to 174.69 mm3, respectively). The P-value between all groups was significantly different after treatment.
Figure 6 The size of tumors before and 3 days after the treatment with PTT in different groups.
The slope of tumor size against time in the control, laser therapy, and O-CNT-PEG groups was about +113.10 mm3/d, +14.47 mm3/d, and −130.57 mm3/d, respectively (+ indicates increasing and – indicates decreasing of tumor size). The slope of tumor size reduction in O-CNT-PEG group is remarkable. Additionally, ultrasound images were taken to define the depth of tumors in different groups. The stages of tumor treatment in O-CNT-PEG group is clear in Figure 7.
Histopathologic evaluation was performed for professional scrutiny. Gross evaluation of tumors indicated severe shrinkage of tumor size in O-CNT-PEG group in comparison with control and laser therapy groups. Microscopic evaluation showed the presence of nodular subtype malignant melanoma in all cases. Necrosis was found to be the most important discriminator between the cases, and its percentage was higher in cases allocated in O-CNT-PEG group compared to control and laser therapy groups. In the O-CNT-PEG group, a direct association was seen with the site of necrosis and deposition of NPs, which is shown in Figure 8. Mitosis was higher in the control cases while compared with the other cases. There is no evidence of regressive fibrosis, lymphocytic infiltration, vascular invasion, neurotropism, ulceration, and microsatellites in cases. The results are detailed in Table 1.
Table 1 Results of histopathologic evaluation
CNTs can absorb NIR light and convert its energy into heat effectively.39 In this study, we used these NPs to evaluate their ability for tumor size reduction by PTT technique. At first, for improving the dispersibility of MWNTs in water, the hydrophilic polymer PEG was used to wrap the surface of the nanotubes. Modified MWNTs were characterized, and the formation of a thin layer of PEG around the nanotubes was established. Results of TGA showed that the amount of PEG component in the O-CNT-PEG was approximately 80% (w/w). Cell cytotoxicity study showed that O-CNT was less cytotoxic than pristine MWNTs, and O-CNT-PEG had the lowest toxicity against HeLa and HepG2 cell lines. The cell viability after exposure to different NPs in HeLa cell line at all concentrations was significantly different (P<0.05). But in the HepG2 cell line, the cytotoxicity of O-CNT-PEG and O-CNT in some concentrations (500 ng/mL and 1,000 ng/mL) was not significantly different (P>0.05). The sensitivity of different cell lines to the same materials is different, and the concentration and duration of exposure time to the materials are also important factors for toxicity evaluation.
Melanoma was induced in mice by injection of B16/F10 cell line. For evaluation the effect of ablation with O-CNT-PEG and laser irradiation, the tumor area was irradiated by an 808 nm CW NIR laser diode after the injection of O-CNT-PEG into the tumor. The average size of tumor in mice receiving O-CNT-PEG decreased sharply in comparison with the laser therapy alone.
Pristine, as-produced CNTs have hydrophobic surface and tend to bundle up. So, these NPs are insoluble in most solvents and biological medium.40 Besides, presence of residual metal catalysts and also the insolubility of pristine CNTs cause they show more toxic effects than functionalized form of them.41 Surfactants, nucleic acids, peptides, and polymers are used for functionalization of CNTs.42 Functionalization of CNTs was done through two main approaches: noncovalent and covalent functionalization. In noncovalent functionalization, the electronic structure of the nanotubes was preserved. Indeed, functionalization through this method is often simple and reproducible. So, many researchers have recommended this approach for modification the surface of CNTs.40 Our strategy in this study involved the generation of dispersed MWNTs by using PEG wrapping. After oxidation of MWNTs, carboxylic acid and hydroxyl groups formed at the side and at the end of nanotubes.30 These functional groups can interact with PEG through hydrogenic bonds, and so a thin layer of polymer was formed around the surface of MWNTs. PEG is a hydrophilic polymer which can improve water dispersibility of MWNTs. In addition, coating NPs with this biocompatible and biodegradable polymer could enhance the localization of NPs in tumor region by the enhanced permeation and retention effect.28,29 The results of cytotoxicity evaluation of MWNTs showed that oxidation and then functionalization of MWNTs with PEG reduced the cytotoxicity of the NTs against two cell lines (Figure 5). Oxidation removes residual metal catalysts, and wrapping PEG around the side of nanotubes improves the water dispersibility.
CNTs can be used as plasmonic NPs that can absorb NIR light and convert its energy to heat.43 This heat can destroy the tumor cells, which are more sensitive to elevated temperature (hyperthermia) than normal cells. Hyperthermia also increases the vascular permeability of tumor compared with normal vasculature, which can facilitate the delivery of anticancer drugs into tumors.39 Therefore, localization of plasmonic NPs in the tumor region can be an efficient strategy for treatment of solid tumors. In this in vivo ablation experiment, O-CNT-PEG was injected into the melanoma tumor, and then the solid tumor region was irradiated. The rate of decrease of tumor size was very rapid in comparison with the group that underwent only laser therapy without any pretreatment (Figure 6). Histological observation, shown in Figure 8, demonstrated tumor necrosis.
According to these excellent results, the next step is to evaluate the efficacy of O-CNT-PEG in tumor suppression by hyperthermia therapy after intravenous injection and localization of them to the tumor through passive targeting technique.
In the present study, a novel O-CNT-PEG NP was evaluated to identify its healing effect in PTT technique. Irradiation of O-CNT-PEG induced heat generation and considerable damage to melanoma in vivo. Monitoring the mice after these treatment and combination therapy with anticancer agents for decreasing the intensity of NIR wavelength is suggested for subsequent studies.
We specially thank the personnel of Animal Laboratory of Shiraz University of Medical Sciences, Shiraz, Iran.
The authors report no conflicts of interest in this work.
Peer D, Karp JM, Hong S, Farokhzad OC, Margalit R, Langer R. Nanocarriers as an emerging platform for cancer therapy. Nat Nanotechnol. 2007;2(12):751–760.
Singh R, Torti SV. Carbon nanotubes in hyperthermia therapy. Adv Drug Deliv Rev. 2013;65(15):2045–2060.
Banu H, Sethi DK, Edgar A, et al. Doxorubicin loaded polymeric gold nanoparticles targeted to human folate receptor upon laser photothermal therapy potentiates chemotherapy in breast cancer cell lines. J Photochem Photobiol B. 2015;149:116–128.
Sadhukha T, Wiedmann TS, Panyam J. Inhalable magnetic nanoparticles for targeted hyperthermia in lung cancer therapy. Biomat. 2013;34(21):5163–5171.
Okhai TA, Smith CJ. Principles and Application of RF System for Hyperthermia Therapy. In: Huilgol N, editor. Hyperthermia. InTech; 2013:171–184.
Zhou F, Xing D, Ou Z, Wu B, Resasco DE, Chen WR. Cancer photothermal therapy in the near-infrared region by using single-walled carbon nanotubes. J Biomed Opt. 2014;14(2):21009.
Liu J, Wang C, Wang X, et al. Mesoporous silica coated single-walled carbon nanotubes as a multifunctional light-responsive platform for cancer combination therapy. Adv Funct Mat. 2015;25(3):384–392.
Burke A, Ding X, Singh R, et al. Long-term survival following a single treatment of kidney tumors with multiwalled carbon nanotubes and near-infrared radiation. Proc Natl Acad Sci U S A. 2009;106(31):12897–12902.
Yang K, Zhang S, Zhang G, Sun X, Lee ST, Liu Z. Graphene in mice: ultrahigh in vivo tumor uptake and efficient photothermal therapy. Nano Lett. 2010;10(9):3318–3323.
Robinson JT, Tabakman SM, Liang Y, et al. Ultrasmall reduced graphene oxide with high near-infrared absorbance for photothermal therapy. J Am Chem Soc. 2011;133(17):6825–6831.
Jordan A. Hyperthermia classic commentary: “Inductive heating of ferrimagnetic particles and magnetic fluids: Physical evaluation of their potential for hyperthermia” by Andreas Jordan et al, International Journal of Hyperthermia, 1993;9:51–68. Int J Hyperthermia. 2009;25(7):512–516.
Patino T, Mahajan U, Palankar R, et al. Multifunctional gold nanorods for selective plasmonic photothermal therapy in pancreatic cancer cells using ultra-short pulse near-infrared laser irradiation. Nanoscale. 2015;7(12):5328–5337.
Day ES, Thompson PA, Zhang L, et al. Nanoshell-mediated photothermal therapy improves survival in a murine glioma model. J Neuro-Oncol. 2011;104(1):55–63.
Ma Y, Liang X, Tong S, Bao G, Ren Q, Dai Z. Gold nanoshell nanomicelles for potential magnetic resonance imaging, light-triggered drug release, and photothermal therapy. Adv Funct Mat. 2013;23(7):815–822.
Roti Roti JL. Cellular responses to hyperthermia (40–46 degrees C): cell killing and molecular events. Int J Hyperthermia. 2008;24(1):3–15.
Shcherbakova DM, Verkhusha VV. Near-infrared fluorescent proteins for multicolor in vivo imaging. Nat Methods. 2013;10(8):751–754.
Filonov GS, Piatkevich KD, Ting LM, Zhang J, Kim K, Verkhusha VV. Bright and stable near-infrared fluorescent protein for in vivo imaging. Nat Biotechnol. 2011;29(8):757–761.
Markovic ZM, Harhaji-Trajkovic LM, Todorovic-Markovic BM, et al. In vitro comparison of the photothermal anticancer activity of graphene nanoparticles and carbon nanotubes. Biomaterials. 2011;32(4):1121–1129.
Sailor MJ, Park JH. Hybrid nanoparticles for detection and treatment of cancer. Adv Mat. 2012;24(28):3779–3802.
Iancu C, Mocan L. Advances in cancer therapy through the use of carbon nanotube-mediated targeted hyperthermia. Int J Nanomed. 2011;6:1675–1684.
Huang X, El-Sayed MA. Plasmonic photo-thermal therapy (PPTT). Alexandria J Med. 2011;47(1):1–9.
Kroemer G, Galluzzi L, Kepp O, Zitvogel L. Immunogenic cell death in cancer therapy. Ann Rev Immunol. 2013;31(1):51–72.
Robinson JT, Welsher K, Tabakman SM, et al. High performance in vivo near-IR (>1 μm) imaging and photothermal cancer therapy with carbon nanotubes. Nano Res. 2010;3(11):779–793.
Murphy FA, Poland CA, Duffin R, et al. Length-dependent retention of carbon nanotubes in the pleural space of mice initiates sustained inflammation and progressive fibrosis on the parietal pleura. Am J Pathol. 2011;178(6):2587–2600.
Xu H, Cheng X, Zhong J, et al. Characterization of multiwalled carbon nanotubes dispersing in water and association with biological effects. J Nanomat. 2011;2011.
Ling X, Wei Y, Zou L, Xu S. The effect of different order of purification treatments on the purity of multiwalled carbon nanotubes. App Surf Sci. 2013;276:159–166.
Liu Z, Tabakman S, Welsher K, Dai H. Carbon nanotubes in biology and medicine: In vitro and in vivo detection, imaging and drug delivery. Nano Res. 2009;2:85–120.
Gong H, Peng R, Liu Z. Carbon nanotubes for biomedical imaging: the recent advances. Adv Drug Deliv Rev. 2013;65(15):1951–1963.
Shen C, Brozena AH, Wang Y. Double-walled carbon nanotubes: challenges and opportunities. Nanoscale. 2011;3(2):503–518.
Sobhani Z, Dinarvand R, Atyabi F, Ghahremani M, Adeli M. Increased paclitaxel cytotoxicity against cancer cell lines using a novel functionalized carbon nanotube. Int J Nanomed. 2011;6:705–719.
Pifferi V, Cappelletti G, Bari C Di, Meroni D, Spadavecchia F, Falciola L. Multi-Walled Carbon Nanotubes (MWCNTs) modified electrodes: effect of purification and functionalization on the electroanalytical performances. Electrochim Acta. 2014;146:403–410.
Tsai PA, Kuo HY, Chiu WM, Wu JH. Purification and functionalization of single-walled carbon nanotubes through different treatment procedures. J Nanomat. 2013;2013:1–9.
Jahanbakhsh R, Atyabi F, Shanehsazzadeh S, Sobhani Z, Adeli M, Dinarvand R. Modified gadonanotubes as a promising novel MRI contrasting agent. DARU J Pharm Sciences. 2013;21(1):53.
Jensen MM, Jørgensen JT, Binderup T, Kjaer A. Tumor volume in subcutaneous mouse xenografts measured by microCT is more accurate and reproducible than determined by 18F-FDG-microPET or external caliper. BMC Med Imag. 2008;8(1):16.
Yan D, Teng Z, Sun S, et al. Foot-and-mouth disease virus-like particles as integrin-based drug delivery system achieve targeting anti-tumor efficacy. Nanomedicine. 2017;13(3):1061–1070.
Shan G, Weissleder R, Hilderbrand SA. Upconverting organic dye doped core-shell nano-composites for dual-modality NIR imaging and photo-thermal therapy. Theranostics. 2013;3(4):267–274.
Luo S, Zhang E, Su Y, Cheng T, Shi C. A review of NIR dyes in cancer targeting and imaging. Biomaterials. 2011;32(29):7127–7138.
Sowa P, Rutkowska-Talipska J, Rutkowski K, Kosztyła-Hojna B, Rutkowski R. Optical radiation in modern medicine. Adv Dermatol Allergol. 2013;4(4):246–251.
Hashida Y, Tanaka H, Zhou S, et al. Photothermal ablation of tumor cells using a single-walled carbon nanotube-peptide composite. J Control Release. 2014;173(1):58–66.
Klumpp C, Kostarelos K, Prato M, Bianco A. Functionalized carbon nanotubes as emerging nanovectors for the delivery of therapeutics. Biochim Biophys Acta. 2006;1758(3):404–412.
Firme CP 3rd, Bandaru PR. Toxicity issues in the application of carbon nanotubes to biological systems. Nanomedicine. 2010;6(2):245–256.
Foldvari M, Bagonluri M. Carbon nanotubes as functional excipients for nanomedicines: I. pharmaceutical properties. Nanomedicine. 2008;4(3):173–182.
Chakravarty P, Marches R, Zimmerman NS, et al. Thermal ablation of tumor cells with antibody-functionalized single-walled carbon nanotubes. Proc Natl Acad Sci. 2008;105(25):8697–8702.
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