Theranostics 2018; 8(4):955-971. doi:10.7150/thno.22325 This issue
Tianjin Key Laboratory of Drug Delivery & High-Efficiency, School of Pharmaceutical Science and Technology, Tianjin University, 300072, Tianjin, PR China.
Photodynamic therapy (PDT) kills cancer cells by converting tumor-dissolved oxygen into reactive singlet oxygen (1O2) using a photosensitizer under laser irradiation. However, pre-existing hypoxia in tumors and oxygen consumption during PDT can result in an inadequate oxygen supply, which in turn hampers PDT efficacy. Herein, an O2 self-sufficient nanotheranostic platform based on hollow MoSx nanoparticles (HMoSx) with oxygen-saturated perfluorohexane (O2@PFH) and surface-modified human serum albumin (HSA)/chloride aluminium phthalocyanine (AlPc) (O2@PFH@HMoSx-HSA/AlPc), has been designed for the imaging and oxygen self-enriched photodynamic therapy (Oxy-PDT) of cancer.
Methods: The in vitro anti-cancer activity and intracellular 1O2 generation performance of the nanoparticles were examined using 4T1 cells. We also evaluated the multimodal imaging capabilities and anti-tumor efficiency of the prepared nanoparticles in vivo using a 4T1 tumor-bearing nude mouse model.
Results: This nanoplatform could achieve the distinct in vivo fluorescence (FL)/photoacoustic (PA)/X-ray computed tomography (CT) triple-model imaging-guided photothermally-maneuvered Oxy-PDT. Interestingly, the fluorescence and Oxy-PDT properties of O2@PFH@HMoSx-HSA/AlPc were considerably quenched; however, photothermal activation by 670 nm laser irradiation induced a significant increase in temperature, which empowered the Oxy-PDT effect of the nanoparticles. In this study, O2@PFH@HMoSx-HSA/AlPc demonstrated a great potential to image and treat tumors both in vitro and in vivo, showing complete tumor-inhibition over 16 days after treatment in the 4T1 tumor model.
Conclusion: O2@PFH@HMoSx-HSA/AlPc is promising to be used as novel multifunctional theranostic nanoagent for triple-modal imaging as well as single wavelength NIR laser triggered PTT/Oxy-PDT synergistic therapy.
Keywords: Hollow structure, Theranostic nanoagent, Triple-modal imaging, Photothermally maneuvered, Oxygen self-enriched photodynamic therapy.
Photodynamic therapy (PDT), which utilizes singlet oxygen (1O2) generated from photosensitizers (PS) and tumor-dissolved oxygen (O2) under laser irradiation to kill cells, has attracted tremendous attention for cancer treatment [1, 2]. However, the effectiveness of PDT is severely impaired by the intrinsic hypoxic tumor microenvironment (pO2 ≤ 2.5 mmHg) [3, 4]. What's more, the constant O2 consumption mediated by PS during the PDT process further worsens tumor hypoxia and greatly limits PDT efficiency . To address this challenge, different strategies have been proposed to modify the hypoxic tumor microenvironment by promoting the oxygenation of tumors to achieve better PDT therapeutic outcomes [6-8]. Several studies have reported that the tumor hypoxia could be relieved by the ability of catalase or manganese dioxide (MnO2) nanoparticles to trigger the decomposition of endogenous hydrogen peroxide (H2O2) existing inside the tumor to produce O2 in situ, realizing significantly promoted treatment outcomes of PDT [9, 10]. In our recent work, it was found that the mild photothermal effect induced by near-infrared (NIR)-light-absorbing nanoparticles could be utilized to increase intratumoral blood flow and subsequently improve the oxygenation status of the tumor microenvironment . However, the tumor reoxygenation levels were still limited by either the amount of available H2O2 existing in the tumor microenvironment or the oxygen delivery capability of red blood cells reaching the tumor blood vessels. Thus, there is an urgent need to develop a smart delivery system with sufficient O2 supply to realize a highly effective oxygen self-enriched photodynamic therapy (Oxy-PDT) under the native tumor hypoxic microenvironment.
Perfluorohexane (PFH), which is a kind of liquid perfuorocarbon, can dissolve a large amount of oxygen and serve as an oxygen carrier, enabling it to be used as a blood substitute [12, 13]. To date, many formulations of liquid perfuorocarbon have been extensively used in the clinic as artificial blood substitutes due to their great biocompatibility and high oxygen-affinity [12-14]. For instance, Oxypherol (Fluosol-43) has obtained FDA approval in improving myocardial oxygenation and preventing abnormalities in ventricular function . In a recent work, it was proposed that photosensitizer-coupled PFH nanoparticles could be used as an adjuvant treatment to increase the therapeutic outcome of PDT via dragging oxygen molecules close to photosensitizers . Moreover, it has been reported that the 1O2 lifetime in PFH is much longer than in the cellular environment or in water , which results in long-lasting PDT effects. Although PFH possesses high oxygen solubility, it releases oxygen simply by diffusion through the oxygen concentration gradient, thus leading to leaking of oxygen in the blood circulation [18, 19]. Liu's group recently found that NIR laser mediated photothermal effect could be utilized to trigger the timely release of oxygen from PFH loaded nanostructures, subsequently contributing to remarkably enhanced radiotherapeutic efficacy . Thus, a well-designed NIR laser-absorbing theranostic nanocarrier is needed to simultaneously carry oxygen saturated PFH and photosensitizer for accurate and optimized Oxy-PDT treatment of tumor.
In our previous work, MoS2 nanodot@polyaniline nanohybrids, which were able to absorb NIR light and X-ray irradiation, were used for combined photothermal therapy and radiotherapy of tumors . Based on this previous study, we optimized the MoS2 nanodots into hollow MoSx nanoparticles (HMoSx) by a facile strategy using NH3 bubble as a soft template. The hollow structure could be effectively filled with PFH, which is then able to act as an oxygen reservoir. Additionally, the large surface areas of both the exterior and interior of the hollow nanostructure could increase the amount of light absorbed, thus improving the photothermal effect [22, 23]. As a typical nonstoichiometric metal chalcogenide, HMoSx nanoparticle was first proposed for use in cancer photothermal therapy (PTT) and photoacoustic (PA) imaging owing to its strong absorbance in the NIR region. In addition, MoSx is also promising for biomedical applications as an X-ray computed tomography (CT) imaging contrast agent given the high X-ray attenuation coefficient of Mo . HSA, as an endogenous protein approved by FDA for intravenous administration , was used to modify the HMoSx nanoparticles (HMoSx-HSA). What's more, HSA coated nanoparticles have been shown to possess both passive and active tumor-targeting abilities via enhanced permeability and retention (EPR) effect as well as gp60/SPARC receptor-mediated transcytosis, respectively . Next, chloride aluminium phthalocyanine (AlPc) PSs were modified to endow HMoSx-HSA (HMoSx-HSA/AlPc) with the ability to produce reactive oxygen species (ROS) when excited by NIR laser irradiation.
Herein, we demonstrated the potential of O2@PFH@HMoSx-HSA/AlPc as a theranostic nanoplatform for fluorescence (FL)/PA/CT multi-modal imaging and NIR laser triggered PTT/Oxy-PDT synergistic therapy (Scheme 1). Under the single wavelength NIR laser irradiation (670 nm), photothermal effect induced by HMoSx could produce significant increases in local temperature. Then, the soaring heat, which could reach the boiling point of PFH, markedly accelerated AlPc and O2 release from O2@PFH@HMoSx-HSA/AlPc and thus promptly activated the Oxy-PDT effect (Figure 2A). The smart O2@PFH@HMoSx-HSA/AlPc nanoparticles possess multiple unique advantages. (1) Oxygen self-enriched property: O2@PFH@HMoSx-HSA/AlPc could carry oxygen into the tumor site, allowing activatable oxygen release in the hypoxic tumor environment to enhance the PDT effect. (2) Stimuli response: AlPc/O2 release and the subsequent Oxy-PDT could be photothermally maneuvered under single wavelength NIR laser irradiation. (3) Multifunction: O2@PFH@HMoSx-HSA/AlPc could serve as a multifunctional platform to integrate complementary imaging modalities and synergistic PTT/Oxy-PDT therapeutic strategies together. Thus, our O2@PFH@HMoSx-HSA/AlPc would be a promising agent for tumor hypoxia modulation and triple-modality imaging-guided PTT/Oxy-PDT synergistic cancer treatment with enhanced tumor inhibition efficacy.
Ammonium tetrathiomolybdate ((NH4)2MoS4) and 1,3-Diphenylisobenzofuran (DPBF) were purchased from Heowns Biochem Technologies LLC (Tianjin, China). Hydrazine hydrate (N2H4.H2O) was obtained from Adamas Reagent Co., Ltd. (Shanghai, China). Perfuorohexane was purchased from Xianding Biological Technology co., Ltd. (Shanghai, China). Human serum albumin (HSA) and calcein-AM/PI double stain kit were received from Sigma-Aldrich (USA). Lipoic acid (LA) and 1-ethyl-3(3-(dimethylamino)-propyl) carbodiimide·hydrochloride (EDC·HCl) were purchased from Shanghai Macklin Biochemical Co., Ltd. Chloride aluminium phthalocyanine (AlPc) was obtained from Shanghai Meryer Co., Ltd. All other chemicals were analytical grade and used as received.
Firstly, HMoSx nanoparticles were prepared by the hydrothermal process, as previously reported . In a typical procedure, 0.5 mmol of (NH4)2MoS4 was added to a 200 mL beaker with 80 mL of NMP. After sonicating for 3 h, the obtained clear solution was poured into a 250 mL three-necked flask. Then, 5.0 mL of N2H4·H2O was added to the flask dropwise under magnetic stirring. Afterwards, the reaction mixture was heated to 80 °C in an oil bath and constantly stirred for 12 h under gentle reflux. After being naturally cooled, the black-brown precipitates were collected by centrifugation at 7200 × g, washed sequentially with ethanol and deionized water 3 times. Then, the obtained precipitates were dried in a vacuum chamber overnight. Finally, the as-prepared hollow MoSx nanosphere (HMoSx) powder was collected for further use.
Secondly, to enhance the water-soluble property of the synthesized HMoSx, the HSA protein was coated on the surface of HMoSx. In a typical synthesis, HMoSx sample was firstly coated with lipoic acid (LA) according to the following process: 80 mg of LA was added into 4 mL of HMoSx (2 mg/mL) by sonication for 5 h. Then, the obtained LA-coated HMoSx nanoparticles were collected by centrifuging at 7200 × g for 10 min. Next, to conjugate HSA to LA-coated HMoSx, 80 mg HSA was mixed with 4 mL aqueous solution of LA-coated HMoSx (2 mg/mL) and then 4 mg of EDC was added. The solution was then stirred at room temperature for 2 h, added with another 4 mg of EDC, and then further stirred for 6 h. The obtained HMoSx-HSA nanoparticles were collected by centrifuging at 7200 × g for 10 min. Then, the obtained precipitate was re-dispersed in deionized water and stored at 4 °C for further use.
Thirdly, for AlPc loading, a predetermined amount of AlPc in 1 mL of DMSO/distilled water (1:1, v/v) was slowly added to HMoSx-HSA solution (10 mg in 10mL DMSO/distilled water). Afterward, the solution was sonicated for 5 min and stirred at room temperature for 24 h. After centrifuging (7200 × g, 10 min) and washing with water 3 times to remove unloaded AlPc, the product was lyophilized to obtain green powder (HMoSx-HSA/AlPc).
Schematic illustration of O2@PFH@HMoSx-HSA/AlPc theranostic nanoagents for in vivo FL/PA/CT imaging and NIR laser triggered PTT/Oxy-PDT synergistic therapy of tumors.
The PFH loading process was conducted according to a reported method . After freeze-drying, the HMoSx-HSA/AlPc sample (5 mg) was transferred into a 50 mL sealed bottle with rubber plug. After the air in the bottle was evacuated, 50 μL of PFH was injected. Then the bottle was sonicated in ice water for 5 min. 1 mL of PBS was injected into the bottle and further sonicated for 10 min. Next, 1 mL of PFH loaded HMoSx-HSA/AlPc dispersed in PBS was placed in a 50 mL sample tube and stored in an aseptic oxygen chamber (O2 flow rate = 5 L/min) for 15 min to achieve oxygen saturation. Finally, the oxygen-saturated, PFH-loaded HMoSx-HSA/AlPc (O2@PFH@HMoSx-HSA/AlPc) was obtained.
The oxygen concentrations in aqueous solutions were measured using a portable dissolved oxygen meter (Rex, JPB-607A, China). For measurement of O2 release, 15 mL of deoxygenated water placed in a 50 mL flask was filled with nitrogen. The oxygen electrode probe was inserted into the flask to measure the oxygen concentration of the solution in real time. Then, 5 mL of O2@PFH@HMoSx-HSA/AlPc or O2@HMoSx-HSA/AlPc solution (5 mg/mL) was injected into the flask. The oxygen concentration was recorded during all processes for 20 min (one measurement every 30 s). For the measurement of O2 release triggered by NIR laser, the solution was irradiated by a 670 nm laser (1 W/cm2) for 10 min.
TEM images of the HMoSx were obtained by the JEM-100 CX (Jeol Ltd., Tokyo, Japan) instrument. Element mapping images and EDS line scanning results were obtained using a JEM-2100F (Jeol Ltd., Tokyo, Japan) transmission electron microscope. The XPS measurements were performed using a PHI-5000 CESCA system (PerkinElmer) with radiation from an Al Kα (1486.6 eV) X-ray source. The CD spectra of pure HSA and HMoSx-HSA were collected using a spectropolarimeter system (BioLogic, MOS-450). The surface area and pore size of the nanoparticles were determined by Brunauer-Emmett-Teller (BET), nitrogen adsorption-desorption and Barrett-Joyner-Halenda (BJH) methods (Micromeritics, ASAP2020), respectively. UV-Vis spectra were measured by a Cary 60 UV-Vis spectrophotometer (Agilent, USA) using quartz cuvettes with an optical path of 1 cm. Fluorescence spectra of different samples were investigated by an LS-55 fluorescence spectrophotometer (Perkin-Elmer). Photothermal images were captured by a Ti32 infrared camera (Fluke TiR, USA) and analyzed by SmartView software. The excitation source was a 670 nm diode-pumped solid-state laser system (LASERGLOW Technologies, Shanghai, China). The in vitro CT images of various concentrations of HMoSx-HSA/AlPc solution were acquired using a Gamma Medica-Ideas instrument. Meanwhile, different concentrations of HMoSx-HSA/AlPc dissolved in purified water were used for in vitro PA signal detection.
To measure the photothermal conversion efficiency (η), the aqueous dispersion samples were exposed to 670 nm NIR laser (1.0 W/cm2) for 600 s, and then the laser was shut off. The photothermal conversion efficency was calculated according to the following equation:
η = [hS(Tmax - Tsurr) - Q0] / [I(1 - 10-A670)] (1)
Where h is the heat transfer coefficient, S is the sample container surface area, Tmax is the steady state maximum temperature, Tsurr is the ambient room temperature, Q0 is the heat associated with the light absorbance of the solvent, which is measured using pure water, I is the laser power, and A670 is the absorbance of our nanoparticles at the wavelength of 670 nm.
In order to get the value of hS, θ herein is introduced, which is defined as the ratio of (T - Tsurr) to (Tmax - Tsurr):
θ = (T - Tsurr) / (Tmax - Tsurr) (2)
Thus, the value of hS is determined by Equation 3:
τs = Cdmd / hS (3)
Where τs is the characteristic thermal time constant, the mass of the nanoparticle solution (md) is in g, and its heat capacity (Cd) is ~4.2 J g-1 k-1 (the heat capacity of pure water).
The AlPc release behavior from HMoSx-HSA/AlPc was investigated using a dialysis method. 1 mL of HMoSx-HSA/AlPc was placed in a dialysis bag (MWCO = 14 kDa) and exposed with or without a 670 nm PTT laser at 0 and 0.5 h, respectively. At different time intervals, 2 mL of the receiving solution was collected and measured by the absorbance spectrometer to determine the concentrations of released drugs, and then poured back to ensure a constant volume. To quantitatively evaluate the generation of singlet oxygen, 1,3-diphenyl isobenzofuran (DPBF) was used in this study. A certain amount of O2@PFH@HMoSx-HSA/AlPc was mixed with DPBF (10 μM) in acetonitrile, followed by irradiaton with an NIR laser (670 nm, 1 W/cm2). The absorbance of the solution at 410 nm was monitored at different time points using a UV-vis spectrometer.
4T1 cells were cultured in a DMEM medium in an atmosphere of 21% O2 and 5% CO2 at 37 °C to mimic the normoxic environment. For comparison, 1% O2 and 5% CO2 at 37 °C was used to mimic the hypoxic tumor microenvironment.
For cell cytotoxicity assay, 4T1 cells were seeded into 96-well plates (1 × 104 per well) until adherent and then incubated with different samples. After 6 h incubation, the cells were treated with or without 670 nm (1 W/cm2, 3 min) irradiation. After another 18 h of incubation, the standard thiazolyl tetrazolium (MTT, Sigma-Aldrich) test was conducted to measure the cell viabilities relative to the untreated cells.
The synergistic PDT/PTT effects of O2@PFH@HMoSx-HSA/AlPc on 4T1 cells in the hypoxic tumor microenvironment were further verified using Calcein AM and propidium iodide (PI) co-staining. 4T1 cells (5 × 105 cells per well) were seeded in 6-well plates and incubated overnight at 37 °C in a humidified 1% O2 and 5% CO2 atmosphere. After being rinsed with PBS (pH 7.4), the cells were incubated with HMoSx-HSA, HMoSx-HSA/AlPc or O2@PFH@HMoSx-HSA/AlPc for 6 h under the same conditions, respectively. Afterward, the cells of the experimental group were rinsed again with PBS and immersed in 200 μL of fresh culture medium, and subsequently irradiated by a 670 nm laser (1 W/cm2, 5 min). Then the cells were incubated for another 18 h. According to the manufacturer's suggested protocol, cells were digested and stained with calcein-AM and PI for visualization of live and dead/late apoptotic cells, respectively. Afterward, the cells of all groups were rinsed again with PBS and were observed by confocal fluorescence microscopy (Leica).
To determine the apoptotic and necrotic cell distributions, 4T1 cells were planted in 6-well plates at a concentration of 2 × 105 cells/well and incubated under the hypoxia conditions for 24 h. They were then incubated with 200 µg/mL HMoSx-HSA, HMoSx-HSA/AlPc and O2@PFH@HMoSx-HSA/AlPc for 24 h with or without 670 nm laser irradiation. After 24 h incubation, the cells were collected and stained with Annexin V/PI following the protocol of the kit, and then analyzed with flow cytometry.
Intracellular ROS and hypoxia were explored using the ROS-ID Hypoxia/Oxidative stress detection kit (Enzo Life Sciences). 4T1 cells were cultured in a confocal dish (5 × 104 cells/dish) and grown in hypoxic or normoxic environment for 24 h. Then, cells were treated with HMoSx-HSA/AlPc or O2@PFH@HMoSx-HSA/AlPc for 6 h and then administrated with the kit reagent mix according to the manufacturer's instructions. After 30 min, the cells were washed twice and exposed to 670 nm laser irradiation for 3 min. After that, cells were washed with PBS, stained by DAPI, and observed by confocal fluorescence microscopy (Leica).
All animals including female nude mice and Kunming mice were purchased from Huafukang Biological Technology Co. Ltd (Beijing, China). All animals were maintained in accordance with the guidelines of Tianjin University. Nude mice bearing 4T1 tumors were used for fluorescence imaging, infrared thermal imaging, and PA imaging. Kunming mice were used for histocompatibility investigation, biodistribution, and simultaneous PTT/PDT study. All animals in this work received humane care in compliance with the institution's guidelines for maintenance and use of laboratory animals in research. The 4T1 tumors were produced by subcutaneous injection of 4T1 cells (2 × 106) in about 50 μL PBS into the oxter of each mouse. Tumor size was measured periodically using a slide caliper. When tumor volumes approached ~100 mm3, the mice were anaesthetized and then i.v. injected with PBS and HMoSx-HSA/AlPc for infrared thermal imaging. Afterwards, the mice were imaged under NIR 670-nm laser irradiation for 5 min.
For in vivo fluorescence imaging, HMoSx-HSA/AlPc (200 μL, 2 mg/mL) were i.v. injected into the tail vein of 4T1 tumor bearing Balb/c nude mice. The fluorescence images were acquired on an ex/in vivo imaging system (CRi, Woburn, MA). After the 24 h in vivo imaging, all mice were euthanized. Major organs including tumors were collected and subjected to ex vivo imaging.
For in vivo PA imaging, 4T1 tumor-bearing Balb/c nude mice were intravenously injected with 200 μL of HMoSx-HSA/AlPc with a dose of 20 mg/kg. Next, the in vivo photoacoustic imaging was acquired on a Vevo LAZR PAI System.
For in vivo CT imaging, 4T1 tumor-bearing Balb/c nude mice were intratumorally injected with 50 μL of HMoSx-HSA/AlPc (10 mg/mL). Before and after the injection, the mice were set on a small X-ray CT (Gamma Medica-Ideas) for imaging. The images were scanned in the accurate mode using full angle, 3 frame averaging, 270 μA tube current, and 80 kV tube voltage. To measure the biodistribution of nanoparticles, tumors and major organs including heart, liver, spleen, lung and kidney from HMoSx-HSA/AlPc solution treated mice were solubilized for ICP-MS measurement to determine tungsten levels after 4, 8, 12 and 24 h.
To evaluate the phototherapy effects of O2@PFH@HMoSx-HSA/AlPc, 4T1 tumor-bearing mice were randomly divided into six groups: (1) PBS, (2) O2@PFH@HMoSx-HSA/AlPc, (3) HMoSx-HSA with 670 nm laser, (4) HMoSx-HSA/AlPc with 670 nm laser, (5) O2 @HMoSx-HSA/AlPc with 670 nm laser, and (6) O2@PFH@HMoSx-HSA/AlPc with 670 nm laser. Each treatment was conducted at day 0 via tail-vein injection. Subsequently, phototherapy treatment (5 min, 670 nm, 1 W/cm2) was performed 8 h-postinjection. Tumor volumes were measured once per day for 16 days. The values are presented as the mean with standard deviation for groups of three animals. On day 16, tumors and major organs were collected, weighed and processed for routine H&E staining. Finally, the images were taken by a Nikon light microscope (Nikon).
Tumor-bearing mice with i.v. injection of PBS, HMoSx-HSA or O2@PFH@HMoSx-HSA were treated with or without NIR laser irradiation (670 nm, 1 W/cm2, 5 min), respectively. After i.v. injection with pimonidazole hydrochloride (60 mg/kg) (Hypoxyprobe-1 plus kit, Hypoxyprobe Inc) for 30 min, the tumors were surgically excised. The pimonidazole hydrochloride could be reductively activated in hypoxic cells and formed stable adducts with thiol (sulphydryl) groups in proteins, peptides and amino acids. To explore the pimonidazole, frozen tumor sections were subsequently incubated with mouse anti-pimonidazole primary antibody (dilution 1:200, Hypoxyprobe Inc.) and FITC-conjugated goat anti-mouse secondary antibody (dilution 1:200, Beyotime). Moreover, cell nuclei were stained using DAPI. The images were obtained using a confocal microscope (Leica).
In this study, we developed a facile strategy for the preparation of hierarchical hollow MoSx nanoparticles (HMoSx) using NH3 bubbles as soft template, which were produced under the solution-phase reaction. The procedure for the synthesis of HMoSx-HSA is illustrated in Figure 1A. As shown in the transmission electron microscopy (TEM) image (Figure 1B), hollow nanospheres were observed with uniform size and shell thickness of ~140 nm and ~20 nm, respectively. In addition, the detailed morphology characteristics of all steps during the preparation are displayed in Figure S1, indicating the formation process of the hollow structure of the MoSx. The high-resolution transmission electron microscopy (HRTEM) image of a partial enlargement of the shell (Figure S2A) indicated the amorphous state of HMoSx, which was consistent with the X-ray diffraction (XRD) pattern (no obvious diffraction peak was observed) (Figure S2B). The prepared hollow MoSx nanoparticles exhibited typical IV type of nitrogen adsorption-desorption isotherm (Figure 1C). In addition, the pore-size distribution (inset of Figure 1C) indicated that a maximum peak pore diameter was ~2.3 nm, further confirming their mesoporous nanoshell structure. From the isotherms curve, the specific surface area of those nanoparticles was calculated to be 72.5 cm2g-1, allowing the effective loading of guest molecules in the inner cavity of such hollow nanostructure.
In the second step, we firstly used lipoic acid (LA) containing a disulfide group and a carboxyl group on the two terminals, respectively, to functionalize the HMoSx. The two sulfur atoms in the LA moiety enabled much stronger binding to HMoSx compared to the single thiol. Then the HSA protein was covalently conjugated to lipoic acid-coated HMoSx to enhance their stability and solubility via the formation of amide bonds between carboxylic groups in the lipoic acid and amino groups of HSA with the help of 1-ethyl-3-(3-dimethylaminopropyl) carbodimide (EDC). Fourier transform infrared spectroscopy (FTIR) and circular dichroism (CD) characterizations were adopted to examine the conformation of HSA and HMoSx-HSA, respectively. As displayed in Figure S3A, the characteristic bands of HMoSx-HSA were consistent with pure HSA, suggesting the presence of HSA on the surface of HMoSx. As shown in Figure S3B, compared to the CD spectra of pure HSA, the peak at 221 nm in the CD spectra of HMoSx-HSA remarkably vanished, demonstrating an increase in random coil structures .
(A) A scheme showing the synthesis and surface modification of HMoSx. (B) TEM images of the as-prepared HMoSx nanoparticles. (C) N2 adsorption/desorption isotherm and corresponding pore-size distribution curves (inset) of HMoSx nanoparticles. (D) Temperature elevation curves of aqueous solutions containing HMoSx-HSA with different concentrations under the irradiation of a 670 nm laser (1 W/cm2). (E) Photothermal images of HMoSx-HSA dispersion at different concentrations over a period of 6 min following exposure to NIR laser (670 nm, 1 W/cm2). (F-H) XPS spectrum of the as-prepared HMoSx nanoparticles: (F) survey spectra, and high-resolution of (G) Mo 3d and (H) S 2p.
Interestingly, the as-prepared HMoSx-HSA had a broad absorption in the NIR region from 600 nm to 1000 nm (Figure S4), which fitted well with the most common lasers used to investigate photothermal effects, e.g., 670 nm, 808 nm, and 980 nm. Under irradiation at 670 nm, the temperature of HMoSx-HSA solutions reached 67.8 °C after 300 s, while the temperatures were 60.3 °C and 64.0 °C when exposed to 808 nm and 980 nm, respectively (Figure S5). This result showed that the 670 nm laser exhibited the highest photothermal efficiency for irradiating HMoSx-HSA solution. Although the longer wavelengths (e.g., 808 nm, 980 nm) have a greater depth of penetration through body tissues than the shorter ones (e.g., 670 nm) , most photosensitizers, such as AlPc or Chlorin e6, can produce the PDT effect only under the irradiation of a 670 nm NIR laser. In addition, a single laser wavelength used for PTT and PDT simultaneously could avoid a relatively complicated treatment procedure and long therapeutic time . In this case, a 670 nm laser was explored to provide both photothermal and photodynamic therapy for HMoSx-HSA. To examine the photothermal effect of HMoSx-HSA, we measured temperature trends in aqueous solutions of different concentrations of HMoSx-HSA (0, 50, 100, 150, and 200 μg/mL) under the irradiation of a 670 nm NIR laser with a power density of 1 W/cm2 (Figure 1D). The solution temperature rose rapidly and strongly depended on the concentration of HMoSx-HSA, e.g., the temperature of HMoSx-HSA solution (200 μg/mL) dramatically increased from 25.0 °C to 67.8 °C after laser irradiation for 300 s. Figure 1E presents photographs of different concentrations of HMoSx-HSA captured by an infrared camera at 300 s. This result indicated their high photothermal conversion efficiency, which was calculated to be 39.6% (Figure S6).
To further determine the surface chemical composition and the valence state of Mo in the HMoSx-HSA sample, X-ray photoelectron spectra (XPS) analysis was carried out. As shown in the XPS survey spectrum (Figure 1F), Mo, S, O, and C elements were detected respectively. As evident in Figure 1G, the high-resolution XPS spectrum of Mo contained Mo 3d3/2 peak and 3d5/2 peak at 231.80 eV and 228.78 eV as two rough peaks, respectively. These peaks were deconvoluted into several fine peaks of Mo(IV), Mo(V) and Mo(VI), which reflected the oxidation state of various Mo species in the HMoSx-HSA sample. The two peaks centered at 229.5 eV and 231.8 eV could be attributed to the bonding energies of Mo3d5/2 and Mo3d3/2 of Mo(IV), respectively, which matched with the spectra of MoS2 . The peaks at 235.15 eV and 228.9 eV were separately characteristic for Mo3d3/2 and Mo3d5/2 of Mo(V) . In addition, binding energy values at 234.5 eV for Mo3d3/2 level and 232.8 eV for Mo3d5/2 level were observed, which corresponded to the standard values of Mo(VI) reported in literature . Moreover, in the XPS spectrum of the S (Figure 1H), the two peaks at 162.70 eV and 161.30 eV corresponded to S 2p1/2 and S 2p3/2. By estimating the area ratio of Mo(IV), Mo(V) to Mo(VI) from XPS spectrum, we could conclude the x value in the HMoSx-HSA sample was greater than 2 but less than 3 (2<x<3).
In this work, we aimed to prepare a potent nanoplatform that can act as a robust photosensitizer delivery carrier as well as an oxygen reservoir, allowing oxygen release in an oxygen deficient environment to enhance the photothermally activated PDT effect. Due to the large specific surface area and mesoporous shell structure of HMoSx, the water-insoluble photosensitizer AlPc was loaded into the HMoSx-HSA (HMoSx-HSA/AlPc, Figure 2A). In this nanoparticle, both HMoSx and HSA could be used for drug loading. On one hand, the AlPc could be loaded on the surface of the HMoSx by π-π stacking . On the other hand, the AlPc was able to be bound by the HSA via hydrophobic interaction between the drug molecule and the hydrophobic domain of the protein . In addition, the AlPc could also enter into the mesoporous shell structure of the HMoSx-HSA. The HMoSx-HSA/AlPc nanoparticles were composed of C, N, Al, Mo, and S elements with an average size of ~145 nm (Figure S7 and S8). In addition, elemental mapping images (Figure 2B) and line scanning data of HMoSx-HSA/AlPc nanoparticles further indicated the existence of Al, Mo, and S elements (Figure S9), suggesting the successful loading of AlPc. Besides, the UV-vis-NIR absorption spectrum of HMoSx-HSA/AlPc showed an AlPc characteristic peak at ~670 nm, further indicating the existence of AlPc in the HMoSx-HSA/AlPc nanospheres (Figure 2D). To investigate the possible drug loading ability of HMoSx-HSA nanospheres, the HMoSx-HSA solution (0.5 mg/mL) was impregnated with different amounts of AlPc (inset of Figure 2C). After removal of excess free AlPc molecules by centrifugal filtration, the UV-vis-NIR spectrum was recorded to examine the AlPc loading ratio (Figure 2C). It was found that the loading capacities of AlPc on HMoSx-HSA increased as a function of drug amounts. The highest drug-loading ratio (weight ratios between the AlPc and HMoSx-HSA) was determined to be ∼74%. To investigate the photophysical and photochemical properties of HMoSx-HSA/AlPc, the fluorescence intensity was observed using a fluorescence spectrophotometer (Figure 2E). Notably, when AlPc was loaded in HMoSx-HSA, its intrinsic fluorescence signals were highly quenched owing to fluorescence resonance energy transfer (FRET) from AlPc to MoSx. Moreover, perfuorohexane (PFH) can dissolve a large amount of oxygen due to the van der waals interaction between PFH and oxygen . Due to the empty space in their hollow structure, the as-prepared HMoSx-HSA nanoparticles can also be employed as carriers for loading PFH using the reported method . A large number of bubbles emerged in the PFH-loaded HMoSx-HSA/AlPc dispersion after heating over 60 °C (higher than the boiling point of perfuorohexane), indicating the potential oxygen-providing capability (Figure S10). In addition, the photothermal effect of O2@PFH@HMoSx-HSA/AlPc aqueous solutions with different concentrations of HMoSx-HSA (0, 50, 100, 150, and 200 μg/mL) was also investigated under the irradiation of a 670 nm NIR laser with a power density of 1 W/cm2 (Figure S11). The temperature of O2@PFH@HMoSx-HSA/AlPc solution (200 μg/mL) increased from 25.0 °C to 69.0 °C after the laser irradiation for 300 s, compared to 67.8 °C for HMoSx-HSA solution with the same concentration (Figure 1D), which was ascribed to the presence of AlPc.
To be a potent nanomedicine, O2@PFH@HMoSx-HSA/AlPc should release O2 and generate toxic reactive oxygen species at the tumor site rather than in the normal organs or bloodstream. Thus, we demonstrated a further therapeutic application of O2@PFH@HMoSx-HSA/AlPc that enabled activatable, on-site enhanced and oxygen self-enriched photodynamic therapeutics. First, AlPc-release behaviors were investigated with HMoSx-HSA/AlPc incubated in 20% DMSO/PBS at 37 °C. As shown in Figure 2F, only 38.1% of AlPc was released within 24 h. However, the AlPc release from HMoSx-HSA/AlPc under the 670 nm laser irradiation at 0 h and 1 h dramatically accelerated. More than 70.3% of loaded AlPc was released under irradiation by 670 nm laser at 24 h. Next, in order to examine the oxygen release, the nanoparticles with or without PFH loading were saturated with oxygen, and then added into deoxygenated water in a nitrogen-filled flask. Considering the fact that the oxygen could be consumed in the presence of AlPc under 670 nm laser irradiation, the O2@HMoSx-HSA or O2@PFH@HMoSx-HSA sample without AlPc was used in this experiment. The dissolved oxygen concentrations in those solutions were monitored by a portable oxygen meter in real time (Figure 2G). After addition of O2@HMoSx-HSA and O2@PFH@HMoSx-HSA, sharply increased oxygen concentrations were observed for both solutions (initial peak in the blue and green line). Thereafter, since the two samples were placed in the oxygen-free solutions, the dissolved oxygen concentrations decreased overtime. Thus, PFH@HMoSx-HSA was able to store more oxygen than HMoSx-HSA alone, and could ensure gradual oxygen release to the surrounding hypoxic environment. In addition, after O2@PFH@HMoSx-HSA or O2@HMoSx-HSA was added into deoxygenated water, we used a 670 nm laser to irradiate the solution to investigate the influence of photothermal effect on oxygen release. Notably, when exposed to the laser, the O2@PFH@HMoSx-HSA solution displayed a sharp increase in oxygen concentration, indicating a burst release of oxygen from the nanoparticles. Considering the fact that HMoSx-HSA showed no obvious shape or size changes after 670 nm irradiation (Figure S12), this burst release should be attributed to the increased temperature triggered by NIR-induced photothermal effect. For comparison, O2@HMoSx-HSA added solution presented less increase of oxygen concentration after the same laser irradiation. Since the released oxygen would be quickly diffused out under the nitrogen atmosphere, the oxygen concentrations might decrease at the later stage of continuous NIR irradiation. In fact, the real tumor is a relatively closed system, which is different from the solution sample tested here. Thus, the oxygen released from the nanosystem may probably stay in the tumor site for a much longer period of time to enhance the tumor oxygen status and the following PDT effect.
(A) Schematic illustration of the AlPc and O2 release mechanism from O2@PFH@HMoSx-HSA/AlPc by sequential PTT/Oxy-PDT treatment. (B) HRTEM image of HMoSx-HSA/AlPc nanoparticles. The element maps shown the distribution of S (yellow), Mo (green), and Al (red). (C) UV-vis-NIR spectra and photographs (inset) of HMoSx-HSA/AlPc obtained at various AlPc loading concentrations after removal of excess free AlPc molecules. (D) UV-vis-NIR spectra and (E) Fluorescence spectra of free AlPc, HMoSx-HSA and HMoSx-HSA/AlPc in the aqueous solution. (F) In vitro release profiles of HMoSx-HSA/AlPc in the absence or presence of 670 nm laser irradiation. (G) O2 concentration change in different samples as indicated with or without NIR laser irradiation. (H) UV-vis-NIR spectra of mixture of O2@PFH@HMoSx-HSA/AlPc and DPBF exposure to 670 nm laser irradiation (1 W/cm2) for each time interval. (I) Singlet oxygen generation from different formulations in the presence of 670 nm laser.
Hypoxia (lack of oxygen) is usually considered as a characteristic of the tumor microenvironment, which contributes to the resistance to PDT since oxygen is an essential requirement in the process of PDT . We then explored whether oxygen released from O2@PFH@HMoSx-HSA/AlPc would be favorable for laser-induced singlet oxygen generation by AlPc. Thus, the nanoparticles in an aqueous solution were irradiated with a 670 nm PDT laser. The singlet oxygen generation was monitored using 1,3-diphenyl isobenzofuran (DPBF) as a singlet oxygen indicator . As shown in Figure 2H, the O2@PFH@HMoSx-HSA/AlPc sample exhibited a sharp decrease in DPBF absorbance at about 400 nm under 670 nm laser irradiation for 10 min. In addition, the singlet oxygen levels produced by different samples were also investigated (Figure 2I). Owing to the quenching effect of AlPc by HMoSx nanoparticles (Figure 2E), the singlet oxygen level produced by HMoSx-HSA/AlPc (without O2) was lower than free AlPc. Notably, after addition of O2@PFH@HMoSx-HSA/AlPc nanoparticles, sufficient O2 could be quickly released, resulting in a remarkable enhancement of light-induced singlet oxygen generation by HMoSx-HSA/AlPc. In contrast, no obvious change in singlet oxygen generation by HMoSx-HSA was observed. Thus, it was expected that the Oxy-PDT effect of O2@PFH@HMoSx-HSA/AlPc would be significantly enhanced after exposure to the NIR laser.
In vitro experiments were then carried out to determine whether our nanoparticles would be an effective agent for synergistic PTT and Oxy-PDT. Considering the oxygen-dependent nature of PDT and the tumor microenvironment oxygen levels, 21% (normoxia) and 1% (hypoxia) oxygen levels were used in this experiment respectively. Firstly, the viabilities of the 4T1 cells treated with different samples with or without laser irradiation were determined by the methyl thiazolyl tetrazolium (MTT) assay. As shown in Figure 3A, the cell viability persisted more than 90% after treatment with O2@PFH@HMoSx-HSA/AlPc or NIR laser alone, suggesting their low cytotoxicity. After treatment with HMoSx-HSA plus NIR laser irradiation (1 W/cm2, 5 min), however, 40% of the cells were ruined due to the HMoSx-induced PTT efficacy. Interestingly, HMoSx-HSA/AlPc nanoparticles displayed a similar cytotoxicity to HMoSx-HSA in the hypoxic condition after NIR laser exposure. While in the normoxic condition, the cytotoxicity of HMoSx-HSA/AlPc nanoparticles with NIR laser was obviously increased, which indicated that the ROS generation depended on the oxygen concentration during the PDT treatment. When the O2 was loaded into the HMoSx-HSA/AlPc nanoparticles (O2@PFH@HMoSx-HSA/AlPc), the cytotoxicity was greatly enhanced regardless of the oxygen levels, suggesting that our optimal nanoparticles could successfully enrich oxygen to accelerate ROS generation even in the hypoxic environment. As presented in Figure 3C after laser irradiation, HMoSx-HSA/AlPc nanoparticles showed a significant cytotoxicity in normoxic environment (21% O2), while limited cytotoxicity in hypoxic incubator (<1% O2) was detected even after exposure to the highest concentration, which was mainly attribute to the decreased ROS generation in the hypoxic medium. However, O2@PFH@HMoSx-HSA/AlPc nanoparticles displayed a similar cytotoxicity toward 4T1 cells in both hypoxic and normoxic medium after irradiation (Figure 3B), indicating successful acceleration of ROS generation in a hypoxic environment during oxygen enhanced PDT treatment.
Correspondingly, the PTT/Oxy-PDT efficacy was also evaluated in a visualized manner by live/dead staining, where live and dead cells were differentiated by co-staining with calcein AM (green fluorescence; living cells) and propidium iodide (PI) (red fluorescence; dead cells) in the hypoxic environment, respectively. As presented in Figure 3D, in the PBS or O2@PFH@HMoSx-HSA/AlPc alone treated groups, all of the cells exhibited green fluorescence, suggesting negligible damage effect from O2@PFH@HMoSx-HSA/AlPc alone. Under the NIR laser irradiation, a similar fluorescence distribution was observed in the HMoSx-HSA/AlPc and HMoSx-HSA treated group. Meanwhile, almost all of the cells incubated with O2@PFH@HMoSx-HSA/AlPc were killed and stained with red fluorescence after NIR laser irradiation. Taken together, these lines of evidence suggested the superior in vitro performance of O2@PFH@HMoSx-HSA/AlPc nanoparticles for combined PTT and Oxy-PDT treatment in vitro even in the hypoxic environment.
To further clarify the mechanism of cell death induced by our nanoparticles under laser irradiation, both early and late apoptotic cells were examined by flow cytometry  using Annexin-V-FITC/PI staining (Figure 3E). After treatment with O2@PFH@HMoSx-HSA/AlPc in the hypoxic condition, the population of apoptotic or dead cells was 83.2% after irradiation for 5 min (670 nm, 1 W/cm2), which was much higher than HMoSx-HSA/AlPc or HMoSx-HSA treated groups. Moreover, in the control group of PBS or O2@PFH@HMoSx-HSA/AlPc without irradiation, negligible apoptotic or dead cells were found. The above results indicated that O2 played an important role in the PDT process combining O2@PFH@HMoSx-HSA/AlPc and laser irradiation.
(A) Cell viability assay of 4T1 cells treated with different samples with or without NIR laser in hypoxic and normoxic environments. (B) Cell viability assay of O2@PFH@HMoSx-HSA/AlPc plus NIR treated 4T1 cells in hypoxic and normoxic environments. (C) Cell viability assay of HMoSx-HSA/AlPc plus NIR treated cells in hypoxic and normoxic environments (D) Live-dead staining images of 4T1 cells treated with PBS, O2@PFH@HMoSx-HSA/AlPc, HMoSx-HSA+NIR, HMoSx-HSA/AlPc+NIR, or O2@PFH@HMoSx-HSA/AlPc+NIR, respectively, under a hypoxic condition. Scale bar: 500 μm. (E) Flow cytometry analysis of 4T1 cells after treatment with different samples under a hypoxic condition. Positive PI and Annexin V-Alexa Fluor 488 cells were defined as late apoptotic/necrotic cells.
ROS-ID, a fluorogenic probe for intracellular hypoxia and ROS detection, was used to confirm the light-driven O2 release and PDT enhancement of O2@PFH@HMoSx-HSA/AlPc nanoparticles. In this experiment, we analyzed ROS and hypoxia following laser irradiation by treating 4T1 cells with nanoparticles in the hypoxic and normoxic conditions respectively. As shown in Figure 4, in the normoxic environment, both O2@PFH@HMoSx-HSA/AlPc and HMoSx-HSA/AlPc treated cells exhibited greatly enhanced ROS generation (green) upon NIR irradiation. Whereas in the hypoxic environment, low ROS production along with remarkable AlPc fluorescence (red) and pronounced hypoxia (magenta) were observed in HMoSx-HSA/AlPc treated 4T1 cells after light irradiation. In contrast, O2@PFH@HMoSx-HSA/AlPc treated cells displayed a satisfactory ROS generation ability after light irradiation in hypoxic environment, indicating that O2@PFH@HMoSx-HSA/AlPc nanoparticles could overcome PDT-induced hypoxia.
Multimodal imaging that combines the advantages of different imaging modalities can achieve more accurate detection of tumors . Recently, considerable effort has been devoted to constructing functional nanoparticles with multimodal imaging capability . Due to the loaded AlPc in our nanoparticles, the FL imaging capability of HMoSx-HSA/AlPc nanoparticles was introduced using a 4T1 tumor-bearing nude mice model. After intravenous (i.v.) injection of free AlPc or HMoSx-HSA/AlPc, fluorescence signal was recorded at 0, 4, 8, 12, and 24 h time points, respectively (Figure 5A). While a widely distributed fluorescence profile throughout the body was observed at the early stage post-injection. Sustained tumor accumulation of the HMoSx-HSA/AlPc nanoparticles over time was discerned and reached a maximum at 8 h compared to other parts of the body (Figure 5A, top panel). At the same conditions, by contrast, the fluorescence images of mice with injection of free AlPc did not show tumor contrast obviously. To obtain clearer insight into the biodistribution of the HMoSx-HSA/AlPc nanoparticles, major organs (heart, liver, spleen, lung, and kidney) and tumors were excised at 24 h post-injection. Notably, the HMoSx-HSA/AlPc nanoparticles were primarily accumulated in the tumor while the free AlPc was mainly in the liver and kidney (Figure 5B, bottom panel). Semi-quantitative analyses based on ex vivo imaging of various tissues further confirmed the high tumor retention of HMoSx-HSA/AlPc nanoparticle compared to other major organs (Figure S13A).
ROS and hypoxia generation following incubation of the cells with nanoparticles and laser irradiation. Confocal images of the cells stained with ROS and hypoxia probes. Cell nuclei were stained by DAPI, scale bar: 20 μm.
(A) Fluorescence images of Balb/c nude mice at different time points after administration of free AlPc and HMoSx-HSA/AlPc; the bottom panel shows the ex vivo images examined at 24 h post-injection. (B) Photoacoustic intensity linearly fit to the concentration of HMoSx-HSA/AlPc aqueous solutions; inset: the corresponding PA images. (C) CT signal intensity linearly fit to the concentration of HMoSx-HSA/AlPc aqueous solutions; inset: the corresponding CT images. (D) Ultrasound (US) images and PA images of 4T1 tumor-bearing mice after being intravenously injected with HMoSx-HSA/AlPc at different time points. (E) In vivo CT images of tumors in mice before and after intratumor injection with HMoSx-HSA/AlPc. (F) The biodistribution of HMoSx-HSA/AlPc measured at 4, 8, 12 and 24 h post i.v. injection.
Given the high tumor uptake of the HMoSx-HSA/AlPc as revealed by FL imaging, we anticipated that the nanoparticles with strong NIR absorption would be excellent contrast agents for both in vivo and in vitro PA imaging. To verify this, we first investigated the potential of the HMoSx-HSA/AlPc nanoparticles for in vitro PA imaging. As shown in Figure 5B, the HMoSx-HSA/AlPc nanoparticles could induce intense optoacoustic signals, strictly following a concentration-dependent manner. For in vivo PA imaging, the mice were i.v. injected with the HMoSx-HSA/AlPc nanoparticles (4 mg/mL, 200 μL) and imaged by a PA system at different time intervals. No obvious signal in the tumor region was observed before injection, while high PA contrast of the tumor was shown 8 h after injection (Figure 5D), suggesting the promising potential of HMoSx-HSA/AlPc for real-time PA imaging for tumor diagnosis. In addition, the quantification of the PA signal intensity also showed that the maximal tumor uptake of HMoSx-HSA/AlPc nanoparticles occurred at 8 h post-injection (Figure S13B), which was in good agreement with the FL imaging results. This time-dependent PA contrast indicated the gradual and efficient passively targeted accumulation of the HMoSx-HSA/AlPc nanoparticles at the tumor site after systemic administration, making it possible to precisely track the agent's accumulation and evaluate the therapeutic efficacy.
Due to the large attenuation of X-rays by Mo , we also investigated the potential of the HMoSx-HSA/AlPc for CT imaging. The CT contrast of the HMoSx-HSA/AlPc nanoparticles was evaluated by acquiring phantom images of the nanoparticle dispersions with various concentrations in vitro (Figure 5C). It was found that the CT images became gradually brighter along with the increasing concentrations. Moreover, the calculated CT value (Figure 5C) revealed a linear increase with the concentration of nanoparticles. To confirm the performance of in vivo CT imaging, 4T1 tumor-bearing nude mice were intratumorally injected with the HMoSx-HSA/AlPc nanoparticles (10 mg/mL, 50 μL), and then imaged using a small animal X-ray CT imaging system 1 h after injection. Compared with the images before injection, a strong tumor contrast was observed after injection (Figure 5E), confirming the excellent CT imaging capacity of the HMoSx-HSA/AlPc nanoparticles. These results demonstrated the great potential of HMoSx-HSA/AlPc nanoparticles as multifunctional contrast agents for in vivo imaging, which could be utilized to guide the laser irradiation in NIR light-driven therapy.
In order to quantitatively gain insight into the biodistribution of HMoSx-HSA/AlPc nanoparticles in the mouse body, Mo content in tumors and major organs, including heart, liver, spleen, lung, and kidney, were determined via inductively coupled plasma mass spectrometry (ICP-MS). As shown in Figure 5F, high Mo content was found in tumor tissue at all tested time points, also indicating that HMoSx-HSA/AlPc nanoparticles could be circulated to, and reside in the tumor. After 8 h injection, the Mo content in the tumor reached a maximum, which was in agreement with the FL and PA imaging data, suggesting the obvious tumor-homing effect of our nanoparticles.
Encouraged by the photothermally triggered AlPc and O2 release behavior of the O2@PFH@HMoSx-HSA/AlPc nanoparticles, we then investigated their feasibility for in vivo NIR laser-induced PTT/Oxy-PDT combination therapy. First, the photothermal effect of HMoSx-HSA/AlPc nanoparticles was examined by using an infrared thermal camera. 4T1 tumor-bearing mice were intravenously injected with HMoSx-HSA/AlPc nanoparticles (200 μL, 1 mg/mL) and exposed to a 670 nm laser at 8 h post-injection. It could be observed in Figure 6A that the temperature of the tumor rapidly increased to 60 °C within 5 min upon laser irradiation. To further assess the efficacy for laser-triggered synergistic therapy, O2@PFH@HMoSx-HSA/AlPc nanoparticles (200 μL, 1 mg/mL) were intravenously injected into 4T1 tumor-bearing mice. After being irradiated by the NIR laser (670 nm, 1 W/cm2, 5 min) at 8 h post-injection, the tumor sizes were measured with calipers every two days (Figure 6C, bottom). On day 16, mice were sacrificed, and all tumors from different groups were collected and weighed (Figure 6C, top). Remarkably, tumors in the combination therapy group were completely eliminated on day 16 (Figure 6B and D). In contrast, solo photothermal therapy (HMoSx-HSA+NIR group) had only moderate tumor growth inhibition. In addition, the survive ratio of the mice with the various treatments was also investigated. As shown in Figure S14, the control groups (PBS and O2@PFH@HMoSx-HSA/AlPc) exhibited early death as a function of time. Compared with control groups, HMoSx-HSA+NIR and HMoSx-HSA/AlPc+NIR treatment prolonged survival time to some extent (20% and 60%, respectively), which were still not satisfactory. As expected, O2@PFH@HMoSx-HSA/AlPc plus NIR laser performed the best antitumor efficiency with 100% survival rate up to 40 days. These observations indicated that the integration of photothermally activated Oxy-PDT into hyperthermia had the potential to effectively inhibit the tumor growth and prolong the survival time through the synergistic therapeutic effect. Furthermore, hematoxylin and eosin (H&E)-stained images of collected tumor sections showed that the tumor cells in O2@PFH@HMoSx-HSA/AlPc+NIR group were severely destroyed, while no damage was detectable in PBS or O2@PFH@HMoSx-HSA/AlPc alone treated mice groups (Figure 6E). As shown in Figure S15, no noticeable damage was observed in main organs including heart, liver, spleen, lung and kidneys of O2@PFH@HMoSx-HSA/AlPc-injected mice after synergetic PTT/Oxy-PDT, suggesting that the optimal nanoparticles with excellent biocompatibility would be promising agents for NIR light-triggered synergistic PTT/Oxy-PDT tumor therapy.
To confirm the ability of oxygen release from O2@PFH@HMoSx-HSA nanoparticles to overcome hypoxia in vivo, a hypoxia-probe (pimonidazole) immuno-histochemical assay was performed by 4T1 tumors with different treatments. Immunofluorescence staining assay was carried out by staining the cell nuclei and hypoxic areas with DAPI (blue) and anti-pimonidazole antibody (green), respectively (Figure 7A, B). The 4T1 murine breast cancer tumors treated with HMoSx-HSA+NIR showed weakened pimonidazole-stained (green) hypoxic signals compared with the control group, indicating that the tumor hypoxia could be partially reduced by the photothermal heating. More interestingly, the tumor treated with O2@PFH@HMoSx-HSA+NIR showed the lowest hypoxic signals among all different groups, demonstrating the remarkably enhanced tumor oxygenation owing to the combined effect of the photothermal heating as well as the NIR-triggered burst release of O2 from PFH-loaded hollow nanoparticles.
(A) Photothermal images of 4T1 tumor-bearing mice exposed to the NIR laser (670 nm, 1 W cm-2, 5 min) after intravenous injection with PBS and HMoSx-HSA/AlPc nanoparticles, respectively. (B) Photos of tumors collected from each group of the 4T1 tumor-bearing mice after various treatments. (C) Growth of 4T1 tumors in different groups of mice after treatment. The relative tumor volumes were normalized to their initial sizes. *P < 0.05, **P < 0.01. (D) Representative photos of mice 16 days after various treatments. (E) H&E-stained tumor slices collected from mice after treatment with different samples.
(A) Representative immunofluorescence images of tumor slices stained by the hypoxia-probe. The nuclei and hypoxic areas were stained with DAPI (blue), and anti-pimonidazole antibody (green), respectively. Scale bar: 200 μm. (B) Quantification of tumor hypoxia for different groups shown in (a). P values: *P < 0.05, **P < 0.01.
In this study, HMoSx nanoshells with hollow structure and mesoporous shells have been successfully fabricated via a rather simple, one-pot method, with HSA-modified on the surface. The strong NIR absorbance and high X-ray attenuation ability endow the HMoSx-HSA nanoparticles with powerful capabilities for high-contrast PA and CT imaging. Meanwhile, the special hollow structure and mesoporous shell of HMoSx-HSA can be utilized for efficient loading of O2@PFH and AlPc. Under the single wavelength NIR laser irradiation (670 nm), HMoSx as a photothermal agent could concentrate absorbed light energy into heat and accelerate the AlPc and O2 release from O2@PFH@HMoSx-HSA/AlPc, thus promptly activating the Oxy-PDT effect. The prepared HMoSx-HSA nanoshell as an all-in-one nanoparticle formulation could thus serve as a multifunctional platform to integrate complementary imaging modalities and single wavelength laser maneuvered synergistic PTT/Oxy-PDT therapeutic strategies.
HMoSx: hollow MoSx nanoparticles; PDT: photodynamic therapy; HSA: human serum albumin; PFH: perfluorohexane; AlPc: chloride aluminium phthalocyanine; FL: fluorescence; PA: photoacoustic; CT: X-ray computed tomography; Oxy-PDT: oxygen self-enriched photodynamic therapy; PTT: photothermal therapy; ROS: reactive oxygen species; PS: photosensitizers; NIR: near-infrared; EPR: enhanced permeability and retention; LA: lipoic acid; DPBF: 1,3-diphenyl isobenzofuran; PI: propidium iodide; TEM: transmission electron microscopy; HRTEM: high-resolution transmission electron microscopy; XRD: X-ray diffraction; EDC: 1-ethyl-3-(3-dimethylaminopropyl) carbodimide; FTIR: Fourier transform infrared spectroscopy; CD: circular dichroism; XPS: X-ray photoelectron spectra; FRET: fluorescence resonance energy transfer; MTT: methyl thiazolyl tetrazolium; ICP-MS: inductively coupled plasma mass spectrometry; H&E: hematoxylin and eosin staining.
This work was supported by the National Natural Science Foundation of China (81503016), Application Foundation and Cutting-edge Technologies Research Project of Tianjin (Young Program) (15JCQNJC13800), National Basic Research Project (973 Program) of China (2014CB932200), and Peiyang Young Talent Fund of Tianjin University (1701).
The authors have declared that no competing interest exists.
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