Houjuan
Zhu
*ab,
Nengyi
Ni
a,
Suresh
Govindarajan
a,
Xianguang
Ding
c and
David Tai
Leong
*ad
aDepartment of Chemical and Biomolecular Engineering, Faculty of Engineering, National University of Singapore, Singapore 117585, Singapore. E-mail: cheltwd@nus.edu.sg; c2dzh@nus.edu.sg
bCentre for Advanced 2D Materials, Graphene Research Centre, National University of Singapore, Singapore 117546, Singapore
cInstitute for Health Innovation and Technology, National University of Singapore, Singapore 117599, Singapore
dNUS Graduate School for Integrative Sciences and Engineering, National University of Singapore, Singapore 117456, Singapore
First published on 4th November 2019
Quantum dots (QDs) originating from two-dimensional (2D) sheets of graphitic carbon nitride (g-C3N4), graphene, hexagonal boron nitride (h-BN), monoatomic buckled crystals (phosphorene), germanene, silicene and transition metal dichalcogenides (TMDCs) are emerging zero-dimensional materials. These QDs possess diverse optical properties, are chemically stable, have surprisingly excellent biocompatibility and are relatively amenable to surface modifications. It is therefore not difficult to see that these QDs have potential in a variety of bioapplications, including biosensing, bioimaging and anticancer and antimicrobial therapy. In this review, we briefly summarize the recent progress of these exciting QD based nanoagents and strategies for phototherapy. In addition, we will discuss about the current limitations, challenges and future prospects of QDs in biomedical applications.
In recent years, a growing number of inorganic QDs derived from their larger 2D counterpart have attracted more attention, such as graphene QDs,4,5,27,28 h-BN,29,30 TMD QDs,31–37 g-C3N4 QDs.38–40 This unique class of QDs is endowed with better dispersity in both aqueous and non-aqueous solutions, larger surface-to-volume ratios, easier functionalization, doping, higher tunability in physiochemical properties and fluorescence.41–43 Due to these unique and diverse properties, QDs have been explored to widely apply in various research fields including bioimaging,44–48 cancer therapy,49–52 sensing,44,53–56 optoelectronics,57,58 catalysis and energy storage.59–61
Phototherapy is an attractive non-invasive remotely activated medical modality for the treatment of various diseases.62,63 It can be widely divided into photodynamic therapy (PDT) and photothermal therapy (PTT). During the process of phototherapy, the phototherapeutic agent has to be delivered to the diseased site and subsequently irradiated with light at a particular wavelength; PDT utilizes photosensitizers (PS) that are activated to generate reactive oxygen species (ROS) by light, consequently inducing irreversible damage of cells.64–68 In PTT, the photothermal agent absorbs near infrared (NIR) light to produce heat, directly leading to the ablation of cells.69–71 Nanomaterials driving light-triggered PDT and PTT are promising next generation agents with their excellent specificities that bring about a more defined therapeutic at a much lower applied dose with lowered systemic side effects compared to the traditional radio- and chemotherapies.72–74
To improve the therapeutic efficiency of phototherapies in tumors, a wide variety of PS and PT agents, such as semiconducting polymer quantum dots,72,74,75 gold nanostructures,76,77 metal nanoparticles,78,79 metal sulfide nanoparticles,80–82 two-dimensional materials,16,83 oxide nanoparticles84–86 and carbon derivatives,87 are explored as potential phototherapeutic agents. In comparison with these nanomaterials, QDs possess several key merits as PT agents including widely tunable fluorescence properties, good photostability and chemical stability, excellent solubility and biocompatibility.88
The studies on QDs in many fields are still at the preliminary stage due to the poor understanding and unexploited applications. Although some excellent reviews have comprehensively and comparatively summarized the synthesis, properties and applications of QDs,89,90 a review that specifically focuses on QD based phototherapy is currently missing. This review summarized the recent progress of QDs originating from two-dimensional nanomaterials for phototherapy. The phototherapeutic QD agents in recent literature are summarized (Table 1). The various strategies by which different QDs are applied in PDT and PTT together with insights into their present limitations and challenges will inspire further translation of these QD technologies into biology and medicine.
System | Light source | Application | PCE for PTT/1O2 QY for PDTa | Analyte | Ref. |
---|---|---|---|---|---|
a PCE: photothermal conversion efficiency of PTT agents; 1O2 QY: singlet oxygen quantum yield of PDT agents; N.A: not reported. | |||||
MoS2 QDs | White light, 0.1 W cm−2 | PDT | N.A. | Human endothelial cells (HMVEC), 3D tumor spheroids | 32 |
MoS2 QDs | 630 nm laser | Up-conversion and down-conversion bioimaging guided PDT | N.A. | HeLa cells | 49 |
MoS2-GSH nanodots | 808 nm laser, 0.5 W cm−2 | PTT | N.A. | 4T1 cells, 4T1 tumor-bearing mice | 102 |
MoSe2 nanodots | 785 nm laser, 2 W cm−2 | PTT | PCE of 46.5% | HeLa cells | 103 |
MoS2 QD doped disulfide-based SiO2 nanoparticles with hyaluronic acid and Ce6 | 808 nm laser, 1.5 W cm−2; | PDT/PTT | PCE of 22.34% | 4T1 cells, 4T1 tumor-bearing mice | 104 |
660 nm laser, 1 W cm−2 | |||||
MoS2 QDs@polyaniline | 808 nm laser, 1.5 W cm−2 | PA/CT image-guided PTT/RT | PCE of 31.6% | 4T1 cells, 4T1 tumor-bearing mice | 106 |
MoS2 QDs | Solar light | PDT | S. aureus, E. coli and S. aureus infected wounds | 107 | |
WS2 QDs | 808 nm laser, 1 W cm−2 | PA/CT image-guided PTT/RT | PCE of 44.3% | HepG2 cells and HeLa cells, BEL-7402 tumor-bearing mice | 50 |
WS2 nanodot based nanoplatform integrating hyaluronic acid (HA), polyaniline (PANI), and Ce6 | 808 nm laser, 1.5 W cm−2; | FL/PA/CT imaging guided triple-collaborative PTT/RT/PDT | N.A. | 4T1 cells, 4T1 tumor-bearing mice | 105 |
670 nm-laser, 1.0 W cm−2 | |||||
GQDs | White light (400–800 nm), 6.5 mW cm−2 | PDT | 1O2 QY of 1.34 | HeLa cells female, BALB/nu mice with subcutaneous breast cancer (MDA MB-231 green-fluorescent protein) xenografts | 51 |
Nitrogen doped GQDs functionalized with an amino group | 800 nm excited two-photon excitation (TPE) light, 2.3936 mW, 239.36 nJ per pixel | TPE imaging guided PDT | 0.53 | KB-50 cancer cells | 52 |
Aptamer-conjugated GQDs/porphyrin derivative | 980 nm laser, 0.72 W cm−2; | Fluorescence-guided PDT/PTT | PCE of 28.58% 1O2 QY of 1.08 | A549 cells | 110 |
635 nm laser, 0.16 W cm−2 | |||||
Folic acid (FA)-functionalized GQDs with loading IR780 iodide | 808 nm laser, 1 W cm−2 | NIR fluorescence imaging guided PTT | PCE of 87.9% | HeLa cells, BALB/c nude mice bearing HeLa tumors. | 119 |
GQDs | 808 nm laser, 0.5 W cm−2 | PTT/PDT | N.A. | MDA-MB-231 cells | 120 |
GQDs | 470 nm laser, 1 W | Autophagy-inducing PDT | N.A. | U251 human glioma cells | 121 |
Upconversion nanoparticle (UCNP) coated GQDs and loading hypocrellin A | 980 nm laser, 0.3 mW | Chemo-PDT | N.A. | HeLa cells | 122 |
GQDs | 470 nm laser, 1 W | PDT | N.A. | Methicillin-resistant Staphylococcus aureus and Escherichia coli | 123 |
GQDs | UV light | Gamma irradiated PDT | N.A. | N.A. | 124 |
GQD immobilized on Mn3O4 coated with polydopamine (PDA) | 670 nm laser, 3 mW cm−2 | MRI and NIR imaging guided PDT | N.A. | A549 cells, A549 tumor-bearing mice | 125 |
Sulphur doped GQDs and methylene blue | 660 nm LED light, 12 W | PDT | N.A. | MCF-7 cells | 126 |
GQD-PEG loading Ce6 | 650 nm laser, 20 mW cm−2 | PDT | N.A. | HeLa cells, nude mice bearing HeLa tumor | 131 |
GQD integrated in MnO2 | 810 nm femtosecond pulses | Two-photon confocal fluorescence guided PTT | N.A. | HeLa | 132 |
GQDs decorated by silver nanoparticles | 425 ± 10 nm LED light, 3 mW cm−2 | Chemo-PDT | N.A. | HeLa and DU145 cancer cells | 135 |
GQDs | 800 nm excited TPE light, 2.64 mW, 264 nJ per pixel | TPE guided PDT | N.A. | MDR bacteria | 136 |
Sulphur doped GQDs combined with methylene blue | 660 nm-LED, 12 W | PDT | N.A. | E. coli and M. Luteus colonies, IMR-90 and A549 cell lines | 137 |
Nitrogen-doped GQDs | 670 nm laser, 1 W cm−2 | PDT | 1O2 QY of 0.60, 0.49 and 0.41 | E. coli bacteria | 138 |
N-GQDs integrated in mesoporous silica nanoparticles and loading DOX | 622 nm LED light, | Chemo-PDT | N.A. | MDA-MB-231 cells | 139 |
6.8 mW cm−2 | |||||
Nitrogen-doped GQDs conjugated Rose Bengal | 480 nm-xenon lamp | PDT | N.A. | MCF-7 cells, ear blood vessels of mice | 140 |
Upconversion nanoparticle (UCNP) coated GQDs and targeted TRITC | 980 nm laser, 1.5 W cm−2 | PDT | N.A. | 4T1 cells and 4T1 tumor bearing mice | 141 |
Upconversion nanoparticle (UCNP) coated GQDs and targeted folic acid, carboxybutyl triphenylphosphonium | 980 nm laser, 1 W cm−2 | PDT | N.A. | HeLa cells and HeLa tumor bearing nude mice | 142 |
N-Doped GQDs | 808 nm laser, 2 W cm−2 | PTT | PCE of 62.53% | A549 and HeLa cells | 144 |
GQDs integrated in magnetic mesoporous silica nanoparticles and loading DOX | 808 nm laser, 2.5 W cm−2 | Magnetic hyperthermia and chemo-PTT | N.A. | 4T1 cells | 145 |
GQDs integrated in mesoporous silica nanoparticles and loading DOX | 808 nm, 2.5 W cm−2 | Chemo-PTT | N.A. | 4T1 cells | 146 |
GQDs integrated in silica coated hollow magnetic nanospheres and loading DOX | 671 nm laser, 0.2 W cm−2; 808 nm laser, 0.25 W cm−2 | Magneto-mechanical, chemo-PDT/PTT | PCE of 21.9% | Eca-109 cells | 147 |
GQDs conjugated by aptamer AS1411 | 808 nm laser, 2 W cm−2 | PTT | N.A. | A549, COS-7, HEK293, HeLa, HepG2, MCF-7 | 148 |
Hyaluronic acid (HA)-modified and GQD-gated hollow mesoporous carbon nanoparticles (HMCN) and loading DOX | 808 nm laser, 1 W cm−2 | Chemo-PTT | N.A. | HeLa cells and HeLa tumor bearing nude mice | 149 |
BPQDs; PEGylated BPQDs | 808 nm laser, 1 W cm−2 | PTT | PCE of 28.4% | C6 cells and MCF7 cells | 152 |
Poly(lactic-co-glycolic acid) (PLGA) nanospheres loaded with BPQDs | 808 nm laser, 1 W cm−2 | PTT | N.A. | MCF7 cells, B16 cells, MCF7 tumor-bearing mice | 153 |
PEGylated BPQDs; rhodamine-A/PEG-BPQDs | 808 nm laser, 2 W cm−2 | Fluorescence imaging guided PDT/PTT | N.A. | HepG2 cells, 4T1 cells, 4T1 tumor-bearing mice | 155 |
BPQDs; PEGylated BPQDs | 670 nm light, 0.16 mW cm−2 | PDT | N.A. | HeLa cells, L02 cells, S180 tumor-bearing mice | 156 |
BPQD-hybridized mesoporous silica framework (BMSF) with in situ synthesized Pt nanoparticles (PtNPs), and decorated with TLS11a aptamer/Mal-PEG-NHS | 670 nm laser, 0.1 W cm−2 | Fluorescence imaging guided PDT | 1O2 QY of 0.142 for BPQD and 0.166 for BMSF | HepG2 cells and HepG2-tumor bearing mice | 157 |
g-C3N4 QDs | Microwave (MW) light, 5 W | Microwave induced PDT (MIPDT) | N.A. | UMR-106 cells | 158 |
g-C3N4 QDs: pristine QDs or modified with defects | 800 nm laser, 1.0 W cm−2 | Two-photon imaging (TPI) and TPE guided PDT | N.A. | MCF7 cells | 159 |
Antimonene quantum dots (AMQDs); PEGylated AM QDs | 808 nm, 1 W cm−2 | PTT | PCE of 45.5% | MCF7 cells, HeLa cells, MCF-7 tumor-bearing mice | 164 |
Titanium carbide MXene QDs | 808 nm laser, 0.5 W cm−2 | PA imaging guided PTT | PCE of 52.2% | HeLa cells, MCF-7 cells, U251 cells, HEK 293 cells, HeLa tumor-bearing mice | 167 |
MoO3−x QDs | 880 nm laser, 2 W cm−2 | Photoacoustic (PA) imaging-guided PDT/PTT | PCE of 25.5% | HeLa cells, L02 cells, HeLa tumor-bearing mice | 171 |
Owing to their near infrared (NIR) absorbance, some TMD QDs have been developed as PPT nanoagents to treat cancer. For example, bio-clearable and ultra-small MoS2 nanodots modified by glutathione (GSH) were developed to be a theranostic agent.102 These MoS2 nanodots not only could remarkably photothermally kill cancer cells, but also served as novel photoacoustic (PA) imaging agents for observing efficient tumor accumulation after intravenous (i.v.) injection. Because of their smaller sizes when compared to MoS2 nanosheets, these MoS2 nanodots showed more efficient clearance via urine. The photothermal treatment of tumors using MoS2 nanodots achieved excellent therapeutic efficacy. Similarly, Wang et al. obtained MoSe2 nanodots (NDs) with an ultrasmall size of 2–3 nm through ultrasonication-assisted liquid exfoliation from bulk MoSe2.103 These nanodots absorbed strongly at NIR wavelengths with a PCE of about 46.5% with efficient HeLa cell ablation under NIR laser (785 nm) irradiation and yet induced negligible cytotoxicity without irradiation.
Since MoS2 QDs on their own have limited blood circulation time and are rapidly cleared from the body, Li et al. designed an amino-modified biodegradable agent composed of MoS2 QD doped disulfide-based silica (SiO2) nanoparticles (denoted as MoS2@ssSiO2).104 This MoS2@ssSiO2 obtained by inserting the MoS2 QDs into SiO2 nanoparticles not only could be degraded and excreted through the redox reaction of glutathione (GSH), but also increased the blood circulation time, in turn inducing a high tumor uptake compared with separate MoS2 QDs. Through adsorption of both chlorin e6 (Ce6) and hyaluronic acid (HA) on the outer shell, MoS2@ssSiO2 has a corresponding photodynamic and tumor-targeting effect, and is guided by fluorescence/CT/multispectral optoacoustic tomography (MSOT) combined PTT/PDT of the tumor. Besides, this group further integrated HA, polyaniline (PANI), Ce6, and tungsten sulfide (WS2) nanodots into a single platform (HA-WS2@PANI/Ce6) for fluorescence/PA/X-ray computed tomography (CT) imaging-guided combinational radiation therapy/PTT/PDT of tumors.105 In another study, the same group fabricated versatile MoS2 QDs@polyaniline (MoS2@PANI) based inorganic−organic nanohybrids for PA/CT image guided combinational PTT/radiotherapy (RT) of tumors, achieving better anticancer efficiency.106 Another similar dual-modal PA/CT imaging guided synergetic PTT/RT theranostic nanoagent, which was only composed of WS2 QDs, was reported to achieve better therapeutic efficacy by Zhao and Gu's group.50
Besides exerting the photothermal effect, some TMD QDs such as MoS2 QDs were demonstrated to be better photosensitizers, which could realize the efficient PDT of tumors through producing ROS under light irradiation. Recently, Leong's group developed a general bottom-up synthesis reaction to synthesize TMD QDs with variable defect states (Ding–Leong reaction). They showed the versatility of this synthesis method by preparing a wider library of TMD QDs (Fig. 1a).32 The reactions were very fast (10–20 s) with very mild conditions such as room temperature, aqueous and atmospheric conditions. As the protocol was bottom-up, the reaction stoichiometric ratio of the precursors can be easily controlled to engineer defects at room temperature. With these defect-variable TMD QDs, it was shown experimentally that on increasing crystallinity defects there was a significant increase in 1O2 QY (Fig. 1b). The positive correlation between the defect degree and photodynamic properties was also verified at the cellular level (Fig. 1c). With these discoveries, MoS2 QDs with more defects showed higher photodynamic killing in cancer cells and in 3D tumor spheroids (Fig. 1d and e). This research provides a simple synthetic strategy to expand the existing TMD QD library and a tool for researchers to investigate the defect effects on their properties for applications in many different fields.
Additionally, Dong and Zhang's group prepared small sized MoS2 QDs of approximately 15 nm with a layered thickness of 2 nm, which presented remarkable down- and up-conversion photoluminescence behaviors. These MoS2 QDs were prepared by ultrasonication of bulk MoS2 powder in tetrabutylammonia through breaking of Mo–S bonds.49 These optical properties make these quantum dots good candidates for imaging probes. Besides, MoS2 QDs demonstrated superior 1O2 generation over protoporphyin (PpIX). In addition to cancer therapy, MoS2 QDs may also have promising antimicrobial application under environmental conditions. Yin's group reported that MoS2 QDs could produce multiple ROS species types under simulated solar light irradiation, leading to remarkably enhanced antibacterial activity. In vivo experiments showed that MoS2 QDs significantly enhanced wound healing.107
The outstanding properties of GQDs have inspired surging interest in some fields for example in electronics,111,112 optics,113,114 sensors,115,116 drug delivery,117 bioimaging,118 and photothermal119,120 and photodynamic therapy.121–126 Even though cadmium based semiconductor quantum dots have exploitable optical properties for bioimaging applications, they still suffers from low biocompatibility and high intrinsic toxicity.127,128 The GQDs might be a viable alternative to cadmium based semiconductor quantum dots with their excellent biocompatibility, chemical inertness, wavelength dependent luminescence and easy scalability traits.129
The clinical use of photosensitizer porphyrin derivatives such as Ce6 and verteporfin is hampered by their hydrophobic nature.130 To overcome these solubility issues, GQDs hidden within redox-triggered cleavable PEG shells have been used as a conjugated platform to anchor down the photosensitizer molecules, without affecting their photodynamic efficiency whilst improving their hydrophilicity and therefore avoiding rapid clearance from the system. The planar π conjugated structure of GQDs quenches photoactive Ce6's fluorescence and 1O2 generation in a non-tumor environment. However, when exposed to tumor relevant GSH, the PEG shell undergoes reductive cleavage for a responsive burst release of Ce6. This system showed excellent in vivo/ex vivo imaging coupled with high PDT efficacy and superior biocompatibility.131 Besides this combination, another GQD-based multifunctional two-photon nanoprobe composed of GQD and MnO2 nanosheets was designed for intracellular tumor-related GSH detection (triggered release) and amplified PDT in cancer cells.132 A porphyrin derivative (P) was conjugated with GQDs coated with polyethylene glycol (PEG) to form GQDs-PEG-P which showed good stability, low cytotoxicity and excellent biocompatibility when tested on A549 and MCF-7 cancer cells. Importantly, the nanomaterial displayed a PCE of 28.58% and high QY of 1O2 generation.110
Another nanoassembly of polydopamine stabilized GQDs-Ce6 was developed which effectively induced tumor cell ablation through enhancing photodynamic effects by delivering the nanoassembly to the targeted Toll-like receptor 9 on the cell surface, continuously stimulating to enhance T lymphocyte infiltration.133
Ge et al.51 reported a GQD based PDT nanoagent which can generate 1O2 through a multistate sensitization process with a high 1O2 QY of ∼1.3, highest among the PDT agents. A new 1O2-generating mechanism increases the QY of GQDs through multistage sensitization. Such a phenomenon is not observed in conventional photosensitizers such as PpIX or phthalocyanines (Fig. 2a). The 1O2 generated by GQDs in the presence of 2,2,6,6-tetramethylpiperidine (TEMP) and 5-tert-butoxycarbonyl 5-methyl-1-pyrroline N-oxide (BMPO) under 532 nm laser irradiation is shown by the Electron Spin Resonance (ESR) spectrum (Fig. 2b). Also, the ability of GQDs to generate 1O2 has been verified through a chemical trapping method using Rose Bengal (RB) as a photosensitizer and disodium 9,10-anthracendipropionic acid (Na2-ADPA) as a trapping agent. This comparison showed that the degradation of Na2-ADPA was larger than that of RB resulting from GQDs under light irradiation (Fig. 2c). The results in HeLa cells showed that the GQDs have low cytotoxicity and biocompatibility in the dark even at 1.8 μM (Fig. 2d). The in vivo experiments in mouse models showed the fluorescence imaging capability of GQDs (Fig. 2e). The mouse group treated with GQDs under light irradiation destroyed tumors and no tumor was observed to regrow after 17 days in the group with GQDs under light irradiation (Fig. 2e).
Thakur et al.120 prepared GQDs from eco-friendly withered leaves of fig trees. The GQDs were tested for in situ labelling probes on cancer cells. When GQDs were taken up by cancer cells and irradiated with an IR laser (808 nm), concentration dependent ROS was generated. These GQDs maintained high photoluminescence stability despite continuous irradiation up to 30 minutes. Passivating nanomaterials with PEG improved their circulation time in vivo and reduced the interaction with macrophages and monocytes in vivo.134
Through PEGylation, a new form of Ag-GQD was prepared and loaded with a chemotherapeutic drug doxorubicin (DOX).135 This nanomaterial system was tested in vitro on HeLa and DU145 cancer cells. When combining the photodynamic effect through the addition of QDs, the combined drug–photosensitizer treatment synergistically increased cell death when irradiated with a 425 nm radiation source. Doping of GQDs could tune their PDT capability. Kuo et al.52 reported amino group functionalized GQDs doped with nitrogen (amino-N-GQDs) with an absorption wavelength of ∼800 nm which had a quantum yield of 33% with strong photoluminescence. The nitrogen doping improved ROS generation and eliminated methicillin-resistant bacteria, Staphylococcus aureus. Their studies revealed that nitrogen doped GQDs exhibited stronger PDT compared with undoped GQDs, which is similar to the photodynamically anti-microbial properties of other GQDs that had been successfully used to kill bacteria.136,137
In another study, it has been reported that increasing nitrogen doping further to 5.1% from 2.9% could increase ROS generation considerably when photo-excited with 670 nm light. This trend can be seen in the quantum yield decreases of N-GQD (5.1% N), N-GQD (2.9% N) and GQD with decreasing defects (0.259, 0.165, and 0.137 respectively).138 Additionally, an efficiency controllable PDT was designed through varying the doping amount of nitrogen atoms.139 Furthermore, dual chemo-photodynamic therapy was achieved by loading a nucleus-targeting drug. Sun et al.140 prepared nitrogen doped GQDs coupled with photosensitizers RB for two photon induced PDT. The material had good photo-stability and biocompatibility. The N-GQDS-RB exhibited high cytotoxicity through irradiation with a one- or two-photon laser. Up-conversion nanoparticles (UCNP) have also been reported to combine with GQDs to enhance the highly efficacious PDT through emitting UV-vis light under NIR excitation to active GQDs for producing 1O2 efficiently.141,142
GQDs have an interesting ability to convert NIR light waves strongly into heat which can kill cancer cells.143 GQDs doped with N increased the PCE to 62.53%.144 GQD capped magnetic mesoporous silica nanoparticles (MMSN) generated heat under a magnetic field or NIR irradiation and concurrently released doxorubicin.145 A multimodal therapeutic system of magneto-mechanical, photothermal, photodynamic and chemo therapies (DOX) was designed for cancer therapy through integrating GQDs into silica coated hollow magnetic nanospheres; similarly DOX loaded mesoporous silica nanoparticle (MSN) capped GQDs (GQDs-MSNs) exhibited pH and temperature responsive drug release behavior, and when irradiated with near-infrared light, the heat generated killed cancer cells.146,147 A multifunctional zeolite imidazolate framework-8 (ZIF-8) was used as a drug carrier with embedded GQDs as photothermal seeds, and the DOX was released under acidic conditions.143
The nature of the photodynamic effect is that it is non-specific and cells within the immediate vicinity at the point of excitement are subjected to the same oxidative damage regardless of whether the cells are the targeted cells or merely spectators. Therefore, targeting becomes an important consideration especially when developing a highly potent photodynamic agent. Wang et al.148 developed active targeting theranostic GQDs based on aptamer AS1411. This specific aptamer acts as a bio-targeting moiety against tumor cells with high specificity and induces cell death even at low dosage. The small size, biocompatibility, stable fluorescence, and NIR responsiveness of GQDs complement the targeting aptamer. Similarly, HA-modified and GQD-integrated hollow mesoporous carbon nanoparticles (HMCN) were used to encapsulate drugs for targeting of CD44 cell surface receptors, overexpressed on cancer cells.149
Yu's group further examined the potential of BPQDs as photothermal agents through the synthesis of biodegradable nanospheres from poly(lactic-co-glycolic acid) (PLGA) loaded with black BPQDs for PTT applications.153 The nanospheres (NS), which were ∼100 nm in size, were rationally designed to allow for high PTT efficiency and more precise control of the biodegradation rate (Fig. 3a). Under physiological conditions, the external PLGA shell of the BPQDs/PLGA NS would gradually degrade through hydrolysis into lower molecular weight fragments without (Fig. 3b) or with light excitation (Fig. 3c). The in vivo photothermal killing effect with the NS was studied with MCF7 and B16 cells, where a steady decline in cell viability was dose-dependent on BPQD loading (Fig. 3d). The in vivo biodistribution of the NS was studied through Cyanine 5.5 (Cy5.5) fluorescence imaging of tumors in mice, with observations that the fluorescence intensity increased up to the 24 h timepoint, revealing continuous accumulation of the NS within tumors. The intensity could also be maintained till 48 h (Fig. 3e). Quantitative biodistribution in mice revealed a high concentration of BPQDs/PLGA NS in the tumor, in addition to the liver, spleen and kidneys (Fig. 3f). In vivo photothermal cancer therapy was conducted in mice injected with different treatment agents and their tumor volumes were tracked across time. Mice with the BPQD/PLGA NS treatment revealed gradual shrinking of the tumors, which were eliminated after ∼16 days (Fig. 3g).
In addition to PTT applications, BPQDs are also gaining prominence for their potential role in PDT. BP nanosheets have been reported to allow for efficient generation of 1O2.154 For instance, Liu and colleagues designed a multifunctional BPQD-based system for both bioimaging and combinatory PTT/PDT application.155 The PEGylated BPQDs exhibited strong NIR photothermal performance and yielded cytotoxic 1O2 for PDT. In vitro and in vivo investigations revealed that the combined phototherapy was more effective for cancer cell ablation than either therapy employed on their own. BPQDs also demonstrated high loading of organic fluorescent dyes for tumor imaging purposes. Additionally, Huang's group synthesized BPQDs with a hydrodynamic diameter of 5.4 nm that could be renally cleared as intact particles.156 Recently, Liu's group designed a hepatocellular carcinoma (HCC)-specific targeting aptamer “TLS11a”-modified BPQD-hybridized nanocatalyst to enhance its PDT performance.157 The nanocatalyst was constructed with a BPQD-hybridized mesoporous silica framework (BMSF) with in situ synthesized Pt nanoparticles (Pt NPs), which respectively acted as a photosensitizer to produce ROS and hence served as a catalyst to react with H2O2 to produce O2 that could amplify the PDT effect through positive feedback mechanisms in the hypoxic tumor microenvironment (TME). Thereafter, modification by TLS11a aptamer/Mal-PEG-NHS targets HCC cells. In vivo and in vitro experiments further demonstrated the nanoagent's active targeting property and excellent photodynamic effects in hypoxic TME with minimal side effects.
In general, BP nanosheet- and BPQD-based phototherapy platforms and systems are attractive as phosphorus is a common element within the human body, essential to life at the cellular level158 and hence regarded as likely benign at worst.153 Moreover, ultrasmall BP is expected to yield nontoxic degradation products that exist in the body.158 Like most nanomaterials in consideration for phototherapy, real clinical applications would depend on successful optimization of biocompatibility, bodily clearance and other necessary safety requirements.
In 2017, Chu et al. used 5 nm g-C3N4 for microwave induced PDT.161 Nanomaterial mediated microwave-induced PDT (MIPDT) was previously developed by the research group as a potential method of addressing deep-seated cancers.162 In the paper by Chu et al., in vitro studies showed the entry of g-C3N4 into UMR-106 osteosarcoma cells with an increase in singlet oxygen generation under microwave induction. Analysis of cell viability revealed the performance of g-C3N4 as a potential agent for MIPDT. In another example, Wu et al. used g-C3N4 QDs with defects as a dual-functional platform that could perform two-photon excited photodynamic therapy (TPE-PDT) and two-photon imaging (TPI).163 Three forms of g-C3N4 QDs were designed. The CN-DPT QDs, synthesized by copolymerizing melamine with a phenyl monomer, showed high performing TPI coupled with efficient generation of ROS for TPE-PDT. Overall, the work demonstrated the emerging potential of g-C3N4 as part of a dual-functional TPI and TPE-PDT therapeutic system.
Antimonene (AM) is an emerging 2D material derived through exfoliating bulk antimony, with certain advantageous physical properties over other notable 2D materials, such as BP and graphene.164 Although AM is yet to be explored in detail for therapeutic applications, its similarity to other 2D materials made exploring its potential use in phototherapy a possibility to examine. Recently, Tao et al. synthesized ultrasmall AM quantum dots (AMQDs) and examined their potential as a photothermal agent, obtaining a PCE of 45.5% for the PEG-coated AMQDs, which was higher than that of BP.165 AMQDs were synthesized through liquid exfoliation with a combined sonication method involving an ultrasound probe in an ice-bath, followed by coating with 1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy(poly ethylene glycol)] (DSPE-PEG) to yield PEG-coated AMQDs that were stable in aqueous medium without aggregation (Fig. 4a). After 808 nm laser irradiation, PEG-coated AMQDs generated photothermal heating curves that are concentration-dependent (Fig. 4b). NIR irradiation was further used to investigate the killing effect on MCF7 cancer cells, where the decline in cell viability was also concentration-dependent on PEG-coated AMQDs (Fig. 4c). MCF7 tumor-bearing mice were treated and temperature changes were monitored using IR thermal imaging (Fig. 4d). Growth curves of tumors revealed that only when PEG-coated AMQDs were irradiated with an NIR laser could there be an observable decline in tumors (Fig. 4e). Overall, AM remains a very recent material to be applied in phototherapy and clinical applications will depend on further in vivo characterization. However, the outstanding photothermal conversion efficiency will make AM an important material to consider for phototherapeutics.
Transition metal oxide (TMO) nanomaterials refer to the group of inorganic particles that commonly include iron oxides and molybdenum oxides. The suboxide (oxygen deficient) phase of molybdenum oxide (MoO3−x) is one example of such materials with growing research into their phototherapy applications. MoO3−x QDs were discovered to display high optical absorbance in the NIR region due to a strong localized surface plasmon resonance (LSPR) effect.166 For instance, Ding et al. developed MoO3−x QDs with good bioimaging and combined PDT-PTT capabilities.167 These QDs exhibited a PCE of 25.5% and could simultaneously generate ROS, suggesting their potential as an agent for combined PDT-PTT. The QDs demonstrated killing of cancer cells both in vitro and in vivo, without localized irradiation with an 808 nm laser, and there is no apparent damage to major organs. Liu and Hu's groups synthesized MoO3−x QDs at room temperature under ultraviolet irradiation, deriving QDs with a PCE as high as 40.01%.168 The cytotoxicity and photothermal performance of the QDs were tested in vitro with encouraging results but have yet to progress to in vivo testing.
MXenes are a class of 2D transition metal materials consisting of their carbides, carbonitrides and nitrides, with a hydrophilic nature and high volumetric capacitance that can exceed those of carbon electrodes, resulting in notable interest in their energy storage device applications.169 However, in 2017, MXenes were first reported for their potential in the PTT technology space, where Ti3C2 nanosheets possessed a PCE of 30.3% with ablation of tumors in in vivo studies.170 However, like within the former paper, hydrofluoric acid (HF) was almost always used as the etching agent to yield MXenes from the bulk phase. In an effort to avoid using the strongly corrosive and potentially difficult to fully remove HF, Liu and Yu's group designed a HF-free synthesis method, yielding MXene QDs with aluminum oxoanions on the surface, which possessed a large extinction coefficient of 52.8 L g−1 cm−1 at 808 nm and a high PCE of up to 52.2%.171 The MXene QDs were capable of tumor ablation under irradiation and had no observable toxicities when examined both in vitro and in vivo.
Despite this excellent characterization, QDs also have some limitations and challenges that we have reported in this review. To address these issues, novel synthetic methods for QDs should be developed: (I) with an easy procedure, high production yield, and large-scale and low-cost production and (II) to find a way to control the sizes, thicknesses, defects and edges, in turn regulating the optical and chemicophysical features. For example, surface modifications on the QDs could be applied to adjust the PL properties, such as enhancing the quantum yield and forming green, even red fluorescent TMD QDs, h-BN, phosphorene, MXenes, germanene and silicone. Additionally, a better understanding of the mechanism of PL from QDs is one main goal to be pursued in the future, which is beneficial for deepening application potential. In particular, novel QDs with strong absorbance in the second NIR region (>950 nm) or high photoluminescence in the NIR region (>700 nm) and high photostability and biocompatibility should be synthesized and developed into QD based nanotheranostics (PDT/PTT based theranostics) to achieve enhanced tissue penetration. To enhance their deep tumor penetrance, total reliance on the EPR may not be wise as the EPR effect is determined by the tumor.172–174 Instead, inducing endothelial leakiness with nanomaterials (NanoEL) at the tumor vasculature could be a more controllable strategy to increase access to the interior of the tumor.172 The various QDs reviewed here are highly suited for inducing Type II (indirect) NanoEL through photoactivatable oxidative stress at the tumor vasculature.172 Moreover with greater control of basic nanomaterials physicochemical parameters such as size, surface charge and density, further fine tuning of both Type I (direct) and Type II (indirect) NanoEL effects can bring about tunability of the degree of accessibility for both nanomedicine and conventional drugs or quick restoration of the endothelial barrier.175–178
Although the development of QDs is essential and still in the early stage, they have proven to be promising for understanding fundamental biology, early diagnosis and theranostics. As the field of 2D QDs expands, more efforts are expected to be dedicated to the design and development of new QDs for future biomedical applications beyond photodynamic and photothermal agents. Successful development for further biological applications can be aided by a better understanding and mitigation of potential toxic effects that could occur.179
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