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Back to Journals » International Journal of Nanomedicine » Volume 12
Authors Guo J, Rahme K, He Y, Li L, Holmes JD, O'Driscoll CM
Published 22 August 2017 Volume 2017:12 Pages 6131—6152
Review by Single anonymous peer review
Editor who approved publication: Professor Lei Yang
Jianfeng Guo,1 Kamil Rahme,2–4 Yan He,1 Lin-Lin Li,5 Justin D Holmes,3,4 Caitriona M O’Driscoll6 1School of Pharmaceutical Sciences, Jilin University, Changchun, China; 2Department of Sciences, Faculty of Natural and Applied Science, Notre Dame University (Louaize), Zouk Mosbeh, Lebanon; 3Department of Chemistry, Tyndall National Institute, University College Cork, Cork, 4[email protected], Trinity College Dublin, Dublin, Ireland; 5The First Hospital of Jilin University, Changchun, China; 6Pharmacodelivery Group, School of Pharmacy, University College Cork, Cork, Ireland Abstract: Development of multifunctional nanomaterials, one of the most interesting and advanced research areas in the field of nanotechnology, is anticipated to revolutionize cancer diagnosis and treatment. Gold nanoparticles (AuNPs) are now being widely utilized in bioimaging and phototherapy due to their tunable and highly sensitive optical and electronic properties (the surface plasmon resonance). As a new concept, termed “theranostics,” multifunctional AuNPs may contain diagnostic and therapeutic functions that can be integrated into one system, thereby simultaneously facilitating diagnosis and therapy and monitoring therapeutic responses. In this review, the important properties of AuNPs relevant to diagnostic and phototherapeutic applications such as structure, shape, optics, and surface chemistry are described. Barriers for translational development of theranostic AuNPs and recent advances in the application of AuNPs for cancer diagnosis, photothermal, and photodynamic therapy are discussed. Keywords: multifunctional gold nanoparticles, cancer bioimaging, cancer photothermal and photodynamic therapy
Cancer, one of the leading causes of mortality worldwide, has caused approximately 8.8 million deaths in 2015 (www.who.int). The number of people who are diagnosed with this malignancy is expected to rise to 22 million annually in the next 2 decades (www.who.int). Despite the increased knowledge about the causes of cancer and the improved interventions to prevent and manage the disease, survival rates are still low mainly due to the delay in diagnosis, lack of effective therapeutics, and high incidence of relapse.
As an emerging concept that facilitates simultaneous diagnosis and treatment, the implementation of theranostic nanomaterials (ie, metal and silica nanoparticles [NPs], liposomes, dendrimers, quantum dots, and carbon nanotubes) has great potential for improved cancer treatment and reduced side effects.1–6 Among these, gold NPs (AuNPs) exhibit favorable physical properties and tailored surface functionalization, providing a potential platform for developing cancer theranostics. This review provides a comprehensive overview of AuNPs as emerging nanomaterials for future cancer theranostics. In this regard, the key physicochemical properties of AuNPs such as structure, shape, optics, and surface chemistry are discussed. In addition, various AuNP-based diagnostic and phototherapeutic strategies under investigation are critically evaluated, with a particular emphasis on those developed to overcome delivery barriers.
Key properties of AuNPs for diagnosis and phototherapy
Colloidal AuNPs were first produced in 1857 by Faraday,7 where the “fine particles” were formed from the reduction of gold chloride by phosphorus and the stabilization of AuNPs by carbon disulfide. In 1951, Turkevich et al8 reported the formation of colloidal AuNPs using trisodium citrate (HOC(COONa)(CH2COONa)2) to reduce tetrachloroauric acid (gold [III] chloride [HAuCl4]) in water, and later Frens9 improved the formation using a slightly modified method. Recently, AuNPs have been produced with various sizes and shapes (ie, gold nanospheres, nanorods, nanocages, nanoshells, and nanostars), which are dependent upon the synthetic methods adopted for their preparation (Figure 1; a summary of synthetic approaches to obtain various gold nanostructures has been described previously).10–14
Figure 1 Development of theranostic AuNPs in the treatment of cancer. Notes: (A) Commonly used AuNPs can be categorized depending on the particle shape, including Au nanospheres, nanorods, nanoshells, and nanocages. These AuNPs with tunable optical and electronic properties and easy surface functionalizations have presented great potential for cancer bioimaging, PTT/PDT, and targeted drug delivery. (B) Functional components including stealth coating materials, bioresponsive moieties, bioactive targeting ligands, bioimaging agents, and therapeutic cargos can be integrated into one system, to achieve multifunctional AuNPs for future cancer treatment. Abbreviations: AuNPs, gold nanoparticles; EPR, enhanced penetration and retention; NIR, near-infrared; PDT, photodynamic therapy; PEG, polyethylene glycol; PTT, photothermal therapy.
Gold nanospheres (particle size 2–100 nm) are generally prepared after reducing HAuCl4 with the assistance of different reducing agents under various temperature and pressure. Trisodium citrate (sometimes referred to simply as sodium citrate), for example, is a commonly used reducing and stabilizing agent, which is capable of generating monodisperse gold nanospheres with different particle sizes by adjusting the concentration of citrate.11
The seeding growth strategy has been used to improve monodispersity and avoid the formation of large AuNPs with irregular shapes (diameter >50 nm), whereby large spherical AuNPs are produced by reducing HAuCl4 or Au (III)-surfactant complexes onto the surface of preexisting seeds using reducing agents such as hydroxylamine hydrochloride,15,16 ascorbic acid,17 2-mercaptosuccinic acid,18 hydroquinone,19 and hydrogen peroxide.20
GNRs were first synthesized by Foss et al,21 Martin,22 and Perez-Juste et al23 using the template method. They are generally synthesized with a size ranging from 10 nm to 100 nm and an aspect ratio between 1 (sphere) and 7 with a corresponding longitudinal plasmon of ~1,050 nm. However, the yield is low due to the fact that only one monolayer of nanorods is produced using the template approach.
Alternatively, the seed growth method is also used to synthesize GNRs.23 In this method, gold seeds are prepared by reducing the gold salt with a strong reducing agent (ie, sodium borohydride). These seeds that provide the nucleation sites are subsequently added to the aqueous surfactant media containing the gold salt and the reducing agents (ie, ascorbic acid and hexadecyltrimethylammonium bromide [CTAB]) for the growth steps.24,25 Additional nucleation during the growth stage can be inhibited by controlling the growth conditions such as 1) the rate of addition of reducing agents to the gold seed and gold salt solution and 2) the reduction potential of reducing agents. As a result, the aspect ratios of nanorods (the ratio of the longer side to the shorter side) can be controlled by using different amounts of gold seeds relative to the precursor.
Gold nanocages are hollow nanostructures (particle size ~40–50 nm) which can be prepared with controllable pores on the surface via the galvanic replacement reaction between truncated silver (Ag) nanocubes and HAuCl4.26 Silver nanostructures with controlled shapes can be generated via the polyol reduction, where AgNO3 is reduced by ethylene glycol to generate Ag atoms followed by nanocrystals or seeds. Silver nanostructures are utilized as the sacrificial template and can be transformed into AuNPs with hollow structures via the galvanic replacement.26 The molar ratio of Ag to HAuCl4 can be regulated to manipulate the diameter and wall thickness of resultant gold nanocages.26
Gold nanoshells are normally composed of dielectric core materials (ie, silica and polystyrene) coated by a thin gold layer. Core materials such as silica and polystyrene have been widely used to provide high stability and monodispersity.27 These core materials can be tailored by varying the dimensions of the core and/or the shell; normally, the core has a diameter ~100 nm and a thin shell of gold about several nanometers (~1–20 nm).28,29
Modification of the core surface with a bifunctional ligand that enhances the shell coverage is a common method for the preparation of gold nanoshells. In the case of silica, the core surface is modified by 3-aminopropyltriethoxysilane (APS) with both ethoxy and amine groups. The ethoxy group binds covalently to silica surface through the hydroxyl group, while the amine group attaches to gold seeds. In addition, bifunctional linkers such as 3-aminopropyltrimethoxysilane (APTMS) and 3-mercaptopropyltrimethoxysilane (MPTMS) have also been used to modify the silica, leading to amino- and thiol-functionalized surfaces that can efficiently attach to gold seeds. As a result, the complete shell is formed by aging the gold attached onto the silica core.30
It is known that the oscillating electromagnetic field of light induces a collective coherent oscillation of the free electrons (also known as conduction band electrons) of the metal.31 The amplitude of the oscillation that reaches a maximum at a specific frequency is termed the surface plasmon resonance (SPR).31 A strong absorption of the incident light is induced by the SPR and can be measured using an ultraviolet (UV)–visible absorption spectrometer.32 The SPR band of noble metals (ie, gold and silver) is known to be much stronger than other metals.32 The SPR wavelength of AuNPs can be tuned from the visible to the near-infrared (NIR) region by changing the size, shape, and structure of AuNPs, as theoretically described by the Mie theory.32
Two main processes, namely, absorption and scattering, occur when the light passes through matter resulting in the energy loss of electromagnetic wave.33 The scattered light has the same frequency as the incident light (it is termed as Rayleigh scattering) or a shifted frequency (it is termed as Raman scattering).33 AuNPs can significantly enhance the light scattering, ie, five- to six-fold stronger than most strongly absorbing organic dyes and higher than the emission of most strongly fluoresceins,34 which makes AuNPs very promising imaging and detection platforms for cancer, as described in the “AuNPs for cancer diagnosis” section.
The scattering properties are highly dependent on the size and shape of AuNPs, which are given in the following sections.
AuNPs with particle sizes of ~40 nm may be easily detected down to a particle concentration of 10−14 M.35,36 Moreover, the scattering of ~60 nm AuNPs is ~100-fold stronger than the emission of a fluorescein.36 Likewise, ~70 nm AuNPs can scatter orders of magnitude stronger than that of a polystyrene sphere of the same size.37 It has been reported that ~30–100 nm AuNPs can be detected under a microscope using dark-field illumination conditions (only the light scattered from indirect illumination of the sample is detected).38 Recently, Jain et al34 and Lee and El-Sayed39 have substantially studied the relationship between the optical absorption/scattering and the size of AuNPs using the Mie theory. They reported that the total extinction of ~20 nm AuNPs was mostly contributed by absorption; when the particle size of AuNPs was ~40 nm, they initiated scattering, and when the particle size was ~80 nm, the extinction of AuNPs was contributed by absorption and scattering in a very similar degree.34,39 This fact that the ratio of scattering to absorption increases significantly for larger size of particles can guide the development of AuNPs for bioimaging.
The optical properties of AuNPs can also be tuned by shape.40–42 When the shape of AuNPs is changed from sphere to rod, the SPR will be split into two bands, namely, a strong band in the NIR region and a weak band in the visible region, as predicted by the Gans theory. The strong band, also referred to as the longitudinal band, results from electron oscillations along the long axis. The weak band, also known as the transverse band, is similar to the wavelength of gold nanospheres. Tong et al43 reported that the longitudinal band of GNRs was red shifted largely by increasing the aspect ratios (length/width), which causes the color change from blue to red. In addition, Lee and El-Sayed44 have shown that when the aspect ratio of GNRs was increased, light scattering was significantly enhanced.
It is known that the SPR of gold nanocages may be tuned to the NIR region with specified wavelengths.45 For instance, the particle size of gold nanocages is generally ~50 nm edge width with several nanometer walls and holes for an SPR wavelength of ~800 nm.46
It is known that the composition of NPs (particularly semiconductor NPs such as quantum dots) is also able to affect the scattering properties;47 recently, several studies have focused on the scattering properties dependent on the composition of Au nanocomplexes.48–50 Jain et al34 have investigated the scattering properties of the core–shell composition in silica–Au nanoshells using Mie theory and discrete dipole approximation method. Results show that the thicknesses of the core and the shell and the radius ratio of core/shell significantly influenced the optical characteristics such as the resonance wavelength, the extinction cross-section, and the ratio of scattering to absorption.34 In addition, it was reported that the SPR wavelength of silica–Au nanoshells may be changed by controlling the Au shell thickness; for example, when the shell thickness was decreased from 20 to 5 nm, the SPR was red shifted ~300 nm, which most likely results from the increased coupling between the inner and outer shell surface plasmons for thinner shell particles.30
The surface chemistry of gold makes AuNPs a promising platform for biomedical applications (Figure 1).11 Brust et al51 exploited the high affinity of thiol for gold to produce AuNP-thiolates (Au-S); this was achieved using HAuCl4, thiol, tetraoctylammonium bromide, and NaBH4 in water–toluene and was stabilized via Au-S-stabilizer bonds. These NPs were dispersed in organic solvent and required further phase transfer or ligand exchange to transfer them into water. An essential purification step to remove impurities for use in biological application was also necessary.
In addition, ligands containing amine and phosphine groups, which also have high affinity with the surface of gold, have been used as efficient stabilizing agents.52 For example, cationic surfactant-free AuNPs (~2–200 nm) have been developed that were synthesized in water using a seed growth method, in the presence of L-cysteine methyl ester hydrochloride (HSCH2CH(NH2)COOCH3·HCl) as a capping agent.53 Furthermore, Chhour et al54 have functionalized AuNPs using a group of thiol and amine ligands, including 11-mercaptoundecanoic acid (11-MUDA), 16-mercaptohexadecanoic acid (16-MHDA), polyethylenimine (PEI), 4-mercapto-1-butanol (4-MB), and 11-mercaptoundecyl-tetra (ethylene glycol) (MTEG). These ligands enhanced the AuNP stability and provided different surface functionalities which can influence cell uptake and cytotoxicity.54 Among them, the 11-MUDA AuNPs were used to monitor the recruitment of monocytes into atherosclerotic plaques in a disease mouse model using X-ray computed tomography (CT), potentially allowing detection of monocyte recruitment in the presence of emerging atherosclerosis therapies.54 In addition, Liu et al55 have recently stabilized AuNPs using thiol-polyethylene glycol (SH-PEG) at two different ratios of thiol to PEG (1:1 and 1:2), significantly improving the AuNP stability in biological media. When AuNPs with higher PEG content were intravenously injected, they were found to accumulate in the liver at a lower level relative to counterparts with lower PEG content.55 These results suggest that when designing AuNPs, a rational ratio between the anchoring group (ie, thiol) and the hydrophilic group (ie, PEG) should be carefully considered, this is important for integrating the properties of NPs in certain bio-related application.
Targeting ligands56–60 may be modified onto the AuNP surface to specifically deliver therapeutic cargos into tissues and organs. Recently, tumor-targeted mesoporous silica-encapsulated GNRs ([email protected]2) for chemotherapy and photothermal therapy (PTT) have been developed by Shen et al.61 In this study, RGD peptides, a targeting ligand for αvβ3 integrin receptors that are known to overexpress on several cancer cells, were conjugated to the terminal groups of PEG on [email protected]2 (namely, [email protected]2-RGD). The [email protected]2-RGD presented significant stability in bio-environments and efficient loading of doxorubicin (DOX, an antitumor chemotherapeutics). Following the NIR irradiation, the combination of photothermal ablation and DOX-mediated cytotoxicity using [email protected]2-RGD resulted in significant tumor reduction in subcutaneous xenografted mice.61 In addition, it has been reported that PEI-capped AuNPs (Au-PEI) were conjugated with anisamide (AA, which is known to bind to the sigma receptor overexpressed on prostate cancer cells)62,63 to produce the AA-targeted AuNPs (Au-PEI-AA).59 As a result, Au-PEI-AA facilitated siRNA uptake into prostate cancer PC-3 cells via binding to the sigma receptor and achieved efficient downregulation of the targeted oncogene.59
In addition to the aforementioned stabilizing and targeting ligands, the gold surface can also be modified using several suitable imaging agents, photosensitive molecules, and bioactive/bioresponsive moieties (ie, pH-sensitive linkers, matrix metalloproteinase [MMP]-sensitive linkers, temperature-sensitive linkers, fusogenic/synthetic peptides, and endosomal membrane-disruptive materials) to achieve multifunctional AuNPs for cancer diagnosis and phototherapy, which are discussed in the following sections.
For wavelengths >650 and <2,000 nm, the tissue absorption is weak, so the NIR light (wavelength from 700 to 2,500 nm) is normally chosen to image tumor deeply within the body. It is worth noting that the penetration depth of NIR light into tissues is highly dependent on the tissue type, the wavelength, and the condition of the incident beam (ie, the laser power, irradiation time, and time interval).64–66 For example, it was shown that no penetration was found in the skin, skull, or brain for NIR light with low-power laser; however, 0.45%–2.90% of 810 nm NIR light at high power (10–15 W) was delivered into 3 cm of the aforementioned tissues.66
AuNPs on their own may act as an NIR-active imaging probe for cancer detection facilitating whole-body scans due to the unique optical properties. The use of targeted AuNPs as the contrast agent was demonstrated by Sokolov et al,37 where AuNPs were conjugated with an antibody against the epidermal growth factor receptor (EGFR, it is known to overexpress on many cancers). These AuNP conjugates were used for detecting cancer cells using a scanning confocal microscope in the reflectance mode with a 647 nm laser to excite the SPR of AuNPs; as a result, cells with AuNP conjugates were clearly imaged on a dark background.37 El-Sayed et al67 improved the use of AuNPs (~35 nm) as the contrast agent via dark-field microscopy. Following excitation by white light, only the wavelength of light corresponding to the maximum of the SPR of AuNPs was displayed intensely, where a bright image of cells with AuNPs could be seen on a dark background.67 Moreover, cetuximab (CET, a chimeric monoclonal antibody against the EGFR)-conjugated PEGylated GNRs (CET-pGNRs) was developed for cancer imaging in xenografted mice.68 The results of in vivo NIR absorption imaging show that specific targeting of CET-pGNRs to the tumor region was evident by a significant increase in the absorption signal. The biodistribution data also show that the amount of AuNPs in tumor tissues from mice injected with CET-pGNRs was eightfold greater than that recorded by nontargeted pGNRs, confirming the results from the NIR absorption imaging. These indicate that CET-pGNRs can specifically target tumor tissues with high specificity and provide a potential tool for NIR-based cancer diagnosis.
Recently, the photoacoustic imaging has taken advantage of plasmonic systems, such as AuNPs with various sizes and shapes.69 Plasmon resonances of AuNPs can be tuned to enhance the optical response,70,71 which can give rise to heat conversion with high efficiency and to the subsequent pressure wave generating the photoacoustic signal. Indeed, these properties have been utilized to develop AuNPs as contrast agents for the photoacoustic imaging.72 Recently, an amphiphilic GNR coated with PEG and poly(lactic-co-glycolic acid) (PLGA; AuNR·PEG·PLGA) was developed for the photoacoustic imaging in xenografted mice.73 The AuNR·PEG·PLGA could self-assemble into vesicles with the AuNRs embedded in the shell formed by the PLGA and PEG extending into the aqueous environments to stabilize the structure. Furthermore, the in vivo two-dimensional (2D) and three-dimensional (3D) photoacoustic images show that the strong plasmonic coupling of GNRs in the vesicles induced a high photothermal effect and a photoacoustic signal, which may potentially be used for image-guided phototherapy in the future.73
In addition, AuNPs have also been utilized as high-quality CT imaging agents due to better X-ray attenuation properties (atomic number Z =79; k-edge value =80.7 keV) than that of iodinated CT contrast agents.74,75 In addition, the conventional small-molecular CT contrast agents are rapidly cleared by the kidney resulting in short imaging times, whereas the gold surface can be modified with biological stabilizing groups (ie, PEG) to improve the pharmacokinetic properties,76 which is beneficial for cancer imaging. Recently, a folic acid (FA)-targeted gold nanosphere (FA-PEG-PEI-AuNPs) was developed using PEI and PEG as stabilizing ligands.77 The intravenous injection of FA-PEG-PEI-AuNPs into an overexpressed folate receptor tumor model resulted in significantly higher CT values in the tumor region compared with nontargeted PEG-PEI-AuNPs. In addition to the “enhanced penetration and retention” (EPR)-based passive tumor targeting, the FA-mediated active targeting was also able to significantly enhance the AuNP accumulation in tumor tissues, resulting in enhanced cancer CT imaging.
In addition, AuNPs are also known to enhance the Raman scattering signal of adjacent molecules, and therefore, surface-enhanced Raman spectroscopy (SERS) imaging aided by gold nanomaterials (spheres, rods, cubes, etc.) has also widely been used in the detection of viruses and cancer cells.78,79
Functionalized imaging agents for cancer detection
Hybrid dual imaging technologies, including positron emission tomography (PET)/CT, PET/magnetic resonance imaging (MRI), and ultrasound/CT, have recently become available.80 Cancer diagnosis clearly benefits from these techniques due to multimodality, as a single agent may avoid the administration of multiple doses. However, the choice of imaging modality must be carefully considered since each one has its own advantages and limitations (ie, modalities with high sensitivity may have poor resolution).
AuNPs can be easily functionalized with additional imaging agents, and improvement in AuNP-based imaging systems may allow the observation of tissues not only on its basic anatomic configuration but also on the molecular level.42,81,82 Moreover, the real-time noninvasive monitoring potentially enables a rapid decision on whether the treatment regimen is effective in a given patient.40,83
Recently, Zhao et al84 have synthesized gold nanospheres doped with 199Au atoms using a one-step procedure for single-photon emission CT (SPECT)/CT imaging in an orthotopic mouse xenograft of triple-negative breast cancer (TNBC). The high-stable radiolabeling ability resulted from the incorporation of 199Au atoms into the crystal lattice of AuNPs. In addition, the 199Au-doped AuNPs were further modified with 1) PEGylation for favorable pharmacokinetics and 2) D-Ala1-peptide T-amide (DAPTA) for targeting C–C chemokine receptor 5 (CCR5, a prognostic biomarker for breast cancer progression).84 Results demonstrate the suitability of 199Au for SPECT/CT imaging and the potential of 199Au-AuNP-PEG-DAPTA for accurately detecting CCR5 in vivo.
Moreover, He et al85 have recently synthesized novel AuNPs for magnetic and CT dual-mode imaging in a mouse xenograft of colorectal cancer. Fe2O3 was first coated with Au nanoshell (Fe2O3/AuNPs), and subsequently the surface of the Fe2O3/AuNPs was modified with lectins (sugar-binding proteins specifically bind to the carbohydrate moieties of the glycans on colorectal cancer cells) through bifunctional PEG-N-hydroxysuccinimide ester disulfide linkers (lectin–PEG–Fe2O3/AuNPs). The lectin–PEG–Fe2O3/AuNPs demonstrated long circulation time, site-specific tumor distribution, and high-quality MRI and CT contrast enhancement effects in tumor tissues, suggesting that the resultant AuNPs are a promising contrast agent for dual-mode MRI/CT colorectal cancer imaging.
Furthermore, selected examples of AuNP-based systemic cancer imaging are provided in Table 1, including the types of AuNPs, functional ligands, cancer types, in vivo animal models, imaging techniques, and end point comments.
Table 1 A summary of studies on the in vivo use of gold nanocomplexes in systemic cancer imaging Abbreviations: AIE, aggregation-induced emission; AuNPs, gold NPs; BSA, bovine serum albumin; CET, cetuximab; CT, computed tomography; DAPTA, D-Ala1-peptide T-amide; DTNB, 5,5-dithio-bis-(2-nitrobenzoic acid); FA, folic acid; GC, glycol chitosan; GNRs, gold nanorods; HA, hyaluronic acid; ICG, indocyanine green; i.v., intravenous; LbL, layer-by-layer; MMP, matrix metalloproteinase; MPNA, magnetoplasmonic nanoassembly; MRI, magnetic resonance imaging; NGAL, neutrophil gelatinase-associated lipocalin; NIR, near-infrared; NPs, nanoparticles; PAI, photoacoustic imaging; PB, Prussian blue; PEG, polyethylene glycol; PEI, polyethylenimine; PET, positron emission tomography; PLGA, poly(lactic-co-glycolic acid); PPAA, plasma-polymerized allylamine shell; PTT, photothermal therapy; SPECT, single-photon emission CT; S.C., subcutaneous; SERS, surface-enhanced Raman spectroscopy; TAT, transactivator of transcription; TNBC, triple-negative breast cancer.
In addition to the aforementioned enhanced light scattering (referred as a radiative property) useful for optical imaging, AuNPs can also convert the absorbed light into heat via a series of nonradiative processes.86,125–129 Two main processes occur based on the heat energy contents: 1) the heat from the energy transformation is passed to the surrounding medium via the phonon–phonon relaxation within ~100 ps and 2) a competitive process takes place between the heating by the electrons and the cooling by the surrounding medium, and when the heating rate is much faster than the cooling rate, AuNPs are melted in hundreds of femtoseconds.125–128 To facilitate cancer PTT, the first process has to dominate, and therefore, continuous-wave (CW) lasers that overlap maximally with the AuNP SPR absorption band need to be utilized.130,131
PTT can be achieved using gold nanospheres under the stimulation of pulsed or CW visible lasers due to the SPR absorption in the visible region, whereby such treatment is suitable for shallow tumors (ie, skin cancer).132,133 Recently, antibody-targeted gold nanospheres were developed to specifically target the EGFR on squalors carcinoma cells, and following stimulation by single 10 ns laser pulses at visible wavelengths, the resultant AuNPs generated intracellular photothermal micro bubbles and induced PTT for tumor inhibition in a subcutaneous cancer model.134
To treat tumors under the skin, NIR-active PTT is favorable as the light can penetrate more deeply due to the minimal absorption of the hemoglobin and water in tissues in this spectral region. Therefore, it is important to tune the SPR absorption of AuNPs to the NIR region by means of altering the shape, morphology, and structure, as described in the “Optical characteristics of AuNPs” section.
Recently, RGD-conjugated dendrite-modified GNRs (RGD-diners) were developed by Li et al135 for selective tumor targeting and PTT in xenografted mice. At 6 h after intravenous injection, the resultant AuNPs accumulated inside tumor tissues via targeting the αVβ3 overexpressed on cancer cells, and when it was irradiated with a NIR laser with a wavelength of 808 nm at a power density of 24 W/cm2 (~0.5 cm diameter illuminated region), tumor growth was significantly reduced by RGD-diners in comparison with the control groups.
In addition, polymeric per fluorocarbon Nan capsules were prepared using the oil-in-water emulsion method, followed by the addition of PEGylated gold nanoshells on the surface.136 These resultant Nan capsules could not only enhance the contrast for ultrasound/CT imaging but also function as photo-absorbers for NIR-active PTT in xenografted mice.136
Recently, Ayala-Orozco et al137 have developed novel gold nanomatryoshkas composed of concentric gold–silica–gold layers and PEG-stabilizing ligands, for PTT of TNBC. In comparison with ~150 nm conventional silica–Au nanoshells, the resultant gold nanomatryoshkas (<100 nm) facilitated higher accumulation in tumors due to better penetration of smaller AuNPs into tissue via the EPR effect. Under irradiation with a CW laser emitting 3 W/cm2 at a wavelength of 808 nm (~1.2 cm diameter illuminated region), the survival rate of an advanced TNBC model with >1,000 mm3 tumors was significantly improved by gold nanomatryoshkas relative to conventional silica–Au nanoshells.137
When photosensitizers are stimulated under the light of specific wavelengths, they convert the surrounding oxygen into toxic reactive oxygen species (ie, singlet oxygen) that may destroy malignant cells in surrounding proximity, which is now known as cancer PDT.138 However, most of the organic photosensitizers are only activated by UV and visible lights, which have poor tissue penetration and therefore are limited to the treatment of surface tumors.139 In addition, organic photosensitizers possess low molar extinction coefficients and therefore can undergo photobleaching and enzymatic degradation.139 In contrast, metal nanostructures (ie, gold, silver, and platinum) can overcome these limitations, as they possess 5–6 orders of molar extinction coefficients, better photostability, and enhanced resistant to enzymatic degradation.140
To tackle the treatment of deeply buried tumors, AuNPs that are able to exert PDT upon NIR light activation have recently been developed. For example, lipid-coated gold nanocages were produced to activate PTT and PDT simultaneously in melanoma-xenografted mice.141 Following direct injection of lipid-coated gold nanocages into the tumor site, a 980 nm CW laser (150 mW/cm2; 10 min) was used to stimulate AuNPs, which raised temperature (~10°C) and generated the singlet oxygen. As a result, this treatment significantly inhibited tumor growth in comparison with an irradiation of the 808 nm diode laser (150 mW/cm2; 12 min; only PTT was induced in this wavelength).
In addition, a variety of organic photosensitizers with NIR-active property can also be incorporated into AuNPs for PDT with a low dose of organic photosensitizers and short exposure of laser irradiation. For example, indocyanine green (ICG, a medical diagnostic agent) is used to produce singlet oxygen for PDT.142 Recently, GNR/ICG-loaded chitosan nanospheres (CS-AuNR-ICG NSs) were prepared by the non-solvent counterion complexation method and electrostatic interaction.142 The CS-AuNR-ICG NSs could effectively load ICG and protect it from rapid hydrolysis. Results of in vivo NIR fluorescence imaging and biodistribution showed that these Au-chitosan NPs could be specifically delivered to the tumor site. Under an 808 nm laser, CS-AuNR-ICG NSs simultaneously produced hyperthermia and reactive oxygen species, which achieved complete inhibition of tumor growth in xenografted mice. Compared with PTT (GNRs) or PDT (ICG) alone, the combined therapy showed a significantly improved therapeutic efficacy.142
In addition, selected examples of AuNP-based cancer phototherapy are provided in Table 2, including the types of AuNPs, functional ligands, cancer types, in vivo animal models, laser types, and end point comments.
Table 2 A summary of studies on the in vivo use of gold nanocomplexes in systemic cancer PTT and PDT Abbreviations: ALG, alginate; AuNPs, gold NPs; C. difficile, Clostridium difficile; Ce6, chlorin e6; CHI, chitosan; DOX, doxorubicin; FA, folic acid; GNRs, gold nanorods; HA, hyaluronic acid; HPPH, 3-devinyl-3-(1′-hexyloxyethyl)pyropheophorbide; ICG, indocyanine green; iPS, Induced pluripotent stem; i.v., intravenous; LED, light-emitting diode; MPCMs, macrophage cell membranes; MSCs, mesenchymal stem cells; NIR, near-infrared; NPs, nanoparticles; PDT, photodynamic therapy; PEG, polyethylene glycol; PEI, polyethylenimine; PEI-PAsp (DIP/MEA), polyethylenimine-b-poly(2-diisopropylamino/2-mercaptoethylamine) ethyl aspartate; PhA, pheophorbide a; PLGA, poly(lactic-co-glycolic acid); PPIX, protoporphyrin IX; PTT, photothermal therapy; PVP, polyvinylpyrrolidone; RB, Rose Bengal; RBC, red blood cell; ROS, reactive oxygen species; S.C., subcutaneous; SERS, surface-enhanced Raman spectroscopy; SPR, surface plasmon resonance.
Barriers to the translation of AuNPs for cancer theranostics
Although local administration of therapeutics has demonstrated significant potential for the treatment of shallow cancers (ie, skin cancer and head and neck cancer) due to the ease of access, many diseases (eg, metastatic cancers) still require systemic administration of therapeutic agents into the bloodstream. In this section, major challenges, namely, 1) instability in the blood circulation, 2) targeting to specific cells of interest, and 3) activation in response to the tumor microenvironment (TME),174 for systemic AuNP delivery in terms of cancer diagnosis and phototherapeutics are discussed (Figure 2).
Figure 2 Systemic delivery of multifunctional AuNPs for cancer bioimaging and phototherapeutics. Notes: (1) Following intravenous injection into the blood, AuNPs with a particle size of <6 nm are prone to glomerular filtration. (2 and 3) When blood proteins bind to AuNPs nonspecifically, the resultant complexes tend to be taken up by MPS for opsonization (a means of identifying the invading particle to the phagocyte). (4) Multifunctional AuNPs (~100 nm) with stealth coating materials, bioresponsive moieties, bioactive targeting ligands, and/or bioimaging agents can efficiently accumulate inside tumor tissues via the “EPR” effect and specifically target cancer cells via ligand–receptor pathway. (5) As a result, theranostic AuNPs can sensitively image the tumors and effectively induce PTT and/or PDT under the irradiation of the NIR light. Abbreviations: AuNPs, gold nanoparticles; EPR, enhanced penetration and retention; MPS, mononuclear phagocyte system; NIR, near-infrared; PDT, photodynamic therapy; PTT, photothermal therapy; ROS, reactive oxygen species.
It has been reported, following intravenous administration, that rapid glomerular filtration occurs in the case of NPs with a hydrodynamic size of <6 nm, while those with particle sizes of >8 nm are able to avoid kidney removal.175 While NPs with >10 nm diameter may reduce renal filtration, larger particles (ie, >100 nm) can evoke the reticuloendothelial system (RES).176 The RES, also known as the mononuclear phagocyte system (MPS), is part of the immune system, which primarily involves the liver, spleen, and lymph nodes.176,177 Foreign materials will be removed out of the blood circulation by the immune cells in MPS, thus dramatically reducing the circulatory half-time (t1/2) of NPs.177 In addition, nonspecific adsorption of blood proteins onto the surface of NPs (ie, hydrophobic interactions between hydrophobic patches on proteins and hydrophobic ligands on NPs, and electrostatic interactions between anionic albumin and cationic NPs) may inhibit NPs’ targeting capabilities or increase the overall particle size of NPs, and eventually the resultant large complexes are either trapped in the capillary endothelium of the lung or taken up by MPS.176
The modification of stabilizing ligands (ie, PEG, block copolymers, and hyaluronic acid [HA]) onto the gold surface, forming the so-called “stealth” particles capable of improving pharmacokinetic profiles, has been substantially reviewed previously.76,178,179 In addition to these stabilizing components, long-circulating NPs have also been developed where the NP surface is coated with the cellular membrane of red blood cells (RBCs) and leukocytes.150,154,174,175 As an alternative stealth coating material, the membrane of these cells completely covers the NP surface with their “self-markers” (ie, proteins, glycans, and acidic sialyl moieties), and the resultant NPs, recognized as the host’s own cells, can actively evade the immune system. For example, Piao et al160 reported that the RBC-coated gold nanocages exhibited longer blood retention compared with the PEGylated counterparts. In addition, the fusion of RBC membranes over gold surface did not alter the unique porous and hollow structures of gold nanocages. Following systemic administration, the RBC-coated gold nanocages demonstrated enhanced tumor accumulation, induced NIR-active PTT, and eventually achieved 100% survival of tumor-bearing mice over a span of 45 days.160
Targeting to specific cells of interest
It is known that tumor grows rapidly via a process termed angiogenesis (new blood vessels are developed from the preexisting vasculature).177,180 The porous vasculature of a tumor is known to provide access to blood-circulating particles with sizes <500 nm, usually <150 nm.176 In addition, the lymphatic drainage system of tumor tissues is normally underdeveloped, and thus, NPs may not be removed. This EPR effect will facilitate “passive” accumulation of NPs in tumor tissues. In addition, targeting ligands (ie, antibodies and peptides) can be functionalized on NPs for “active” cancer targeting. Taking advantage of the “passive” and “active” targeting, recent advances in the design of AuNPs have offered great potential for accurate diagnosis and targeted therapy. For example, targeted gold nanocages were developed by coating with HA (a targeting ligand for CD44) on the gold surface to specifically recognize cancer cells overexpressing CD44.159 The HA–Au nanocages containing DOX could be efficiently uptaken by a receptor-mediated process, and subsequently, the coated HA molecules were degraded in lysosomes, resulting in the release of DOX. Biodistribution results demonstrate that targeted gold nanocages achieved significantly higher tumor accumulation relative to nontargeted counterparts in tumor-bearing mice. As a result, HA-coated gold nanocages containing DOX significantly slowed down the tumor growth, and more importantly, complete tumor inhibition was achieved when combined with PTT under the NIR stimulation.159
Activation in response to TME
TME is specifically adapted to support the growth, invasion, and metastasis of primary tumor tissues; this has been substantially reviewed previously.181 “Smart” bioresponsive NPs have been developed for targeted delivery and controlled drug release by exploiting the TME, where a slightly acidic environment, a low oxygen (hypoxia) niche, and overexpression of extracellular matrix (ECM) components (ie, MMPs) are evident.181
It is now known that the hypoxia region in solid tumors is a complex microenvironment with a low oxygen concentration and deficient nutrients.182 The hypoxic environment can not only lower the susceptibility of cancer cells to anticancer drugs but also reduce the response of cancer cells to free radicals.182 Although the hypoxia of solid tumors causes a hurdle in therapy, the low level of oxygen microenvironment serves as an ideal habitat for a number of anaerobic bacteria. Recently, Luo et al149 reported a tumor-targeted AuNP delivery using two anaerobic bacterial strains, namely, Bifidobacterium breve UCC2003 and Clostridium difficile CCUG 37780. In this study, two approaches were designed for the active NP delivery: 1) a direct conjugation of GNRs on the surface of the vegetative B. breve for intravenous delivery into hypoxic region (a cargo-carrying approach) and 2) the injection of the C. difficile spores first, followed by the intravenous administration of the antibody–GNR conjugates to specifically target the germination of the C. difficile spores (an antibody-guiding approach). Under NIR excitation, the antibody-directed strategy showed stronger imaging and achieved effective PTT to completely inhibit tumor growth in a subcutaneous mouse cancer model.149
In addition, Sun et al93 developed novel AuNPs for dual CT/optical imaging of cancer. First, AuNPs were modified with glycol chitosan (GC) polymers (GC-AuNPs) for excellent stability and enhanced EPR effect. Second, fluorescent probes were chemically modified to GC-AuNPs via MMP-active peptides (MMP-GC-AuNPs). The NIR fluorescent probes were strongly quenched by the combinational quenching effects between the organic black hole quencher and the gold surface, but the quenched probes were reactivated upon exposure to MPPs in the TME. As a result, CT images with high spatial resolution and optical images with high sensitivity were simultaneously achieved using these AuNP-based CT/optical dual imaging probes.93
In addition to tumor accumulation via the EPR effect, a majority of intravenously administrated NPs are nonspecifically distributed into healthy tissues (ie, phagocytic cell-rich organs such as the liver and spleen) before the renal clearance.183 Although the gold core is generally inert, nontoxic, and biocompatible, significant toxicity of AuNPs can be induced by the synthesis method of gold nanostructures, physicochemical properties (ie, size, morphology, and surface charge), surface conjugates and ligands, the doses, and the administration routes.173 Recently, numerous studies have described AuNPs designed to investigate whether their in vivo behaviors such as accumulation in healthy tissues and renal clearance cause unwanted effects.184–187
For example, the glomerular filtration, biodistribution, and toxicity of glutathione (GSH)- and bovine serum albumin (BSA)-capped AuNPs were evaluated using mice.188 As a result, smaller AuNPs (GSH-coated, ~2 nm) caused highly efficient kidney removal and were more readily metabolized relative to the larger AuNPs (BSA-coated, ~8 nm), suggesting that the toxicity was related to the size of AuNPs. In addition, although both AuNPs caused acute infection, inflammation, and kidney function damage after 24 h, these effects were eliminated for ~2 nm AuNPs after 28 days; in contrast, ~8 nm AuNPs further accumulated in the liver and spleen causing irreparable toxicity.188
It has been difficult to substantially evaluate the biodistribution, clearance, and toxicity of AuNPs, due to the fact that experimental designs are diverse, including the particle size, charge and shape, functionalization methods, types of animal models, delivery doses, and administration routes. Therefore, standard approaches are urgently needed in the future to facilitate development and approval of AuNPs for cancer theranostics.189
The newly emerging concept termed theranostics is well established as the development of novel strategies to combine diagnostic and therapeutic capabilities into a single agent facilitating specific and personalized therapies for diseases.190 The rationale behind the concept is that diseases, such as cancers, are extremely heterogeneous, and all existing treatments are effective for only certain patients and at selective stages of disease development.191 Therefore, a combined approach of diagnostics and therapeutics may provide promising treatment protocols that are more specific to individuals, ie, personalized medicines, and therefore more likely to offer improved prognoses.
Recent advances in understanding the optical and chemical properties of gold have enabled the design of novel AuNPs containing diagnostic and therapeutic functions that can be integrated into one system.40,42,192 Au-nanocomplex-based cancer imaging and phototherapy are reviewed in the “AuNPs for cancer diagnosis” and “AuNPs for cancer phototherapy” sections, respectively (Tables 1 and 2); many of these Au nanocomplexes, by tuning the size, shape, and structure, and by using different functional ligands, are capable of improving sensitive cancer diagnosis and targeted phototherapy simultaneously, under the stimulation of the appropriate light resources (NIR light is preferred in most cases). In addition, a number of AuNP-based theranostics have advanced into clinical trials (NCT03020017, NCT01270139 NCT02755870, NCT01420588, and NCT02782026). For example, the safety evaluation of a drug named NU-0129 is now undertaking an early Phase I trial (NCT03020017). NU-0129 is composed of siRNA arranged on the surface of Au nanospheres, and when infused in patients with recurrent glioblastoma multiforme or gliosarcoma, the Au nanocomplexes can penetrate the blood–brain barrier and deliver siRNA into tumor cells knocking down the expression of oncoprotein Bcl2Like12, which may result in significant inhibition of tumor growth (NCT03020017). Furthermore, CNM-Au8 (a drug candidate now being tested in clinical trial), an Au nanocrystal suspension drug, has recently been developed by Clene Nanomedicine (Salt Lake City, UT, USA) using Clean-Surface Nanosuspension™ (CSN) technology (it produces atomically clean-surface elemental nanocrystals, free of any residual surface chemicals, or surface-capping agents) (www.clene.com). The oral administration of CNM-Au8 has demonstrated efficient immunomodulation in established demyelination animal models (www.clene.com). The safety, tolerability, and pharmacokinetics of CNM-Au8 are now under evaluation in healthy volunteers, with a hope of facilitating the application of the drug for the demyelinating disorder neuromyelitis optica (NMO) in the future (NCT02755870).
To overcome in vivo delivery barriers, Au nanocomplexes are normally modified with functional moieties such as stabilizing materials, targeting ligands, and bioresponsive linkers. However, it should be borne in mind that extensive functional modifications may cause unwanted toxic side effects, and therefore, further investigation is required to quantify the benefit of a treatment versus the risk of toxicity before theranostic Au nanocomplexes can be translated into clinically accepted strategies for cancer therapy.
We acknowledge the funding provided by the Outstanding Youth Foundation from the Department of Science and Technology, Jilin Province (Project Number: 20170520046JH); the Start-Up Research Grant Program from Jilin University (Project Number: 451160102052); the HAI-Novartis Fellowship Award from the Haematology Association of Ireland and Novartis Oncology; and the CNRS Lebanon GRP2015.
The authors report no conflicts of interest in this work.
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