Nanogold-albumin conjugates: transformative approaches for next-generation cancer therapy and diagnostics
Namita
Jaiswal
ab,
Nibedita
Mahata
b and
Nripen
Chanda
*a
aHuman Centered Robotics and Cybernetics Group, CSIR-Central Mechanical Engineering Research Institute, Durgapur, India. E-mail: n_chanda@cmeri.res.in
bDepartment of Biotechnology, National Institute of Technology (NIT), Durgapur, India
First published on 18th March 2025
Abstract
Nanogold-albumin conjugates have garnered significant attention as a highly adaptable theranostic platform, capable of delivering a wide range of therapeutics, from small-molecule drugs to larger biomolecules, while offering promising applications for monitoring and managing cancer. The remarkable theranostic capabilities of these conjugates stem from the combined strengths of gold and albumin, which provide low toxicity, a large surface area, customizable surface chemistry, and unique optical properties, all contributing to their potential in cancer therapy. This review delves into the design and development of two primary types of nanogold-albumin conjugate: supramolecular albumin-coated gold nanoparticles (GNP-BSA/HSA) and albumin-templated ultra-small gold nanoclusters (GNC-BSA/HSA). Each strategy offers distinct advantages, enabling the fine-tuning of conjugate properties to optimize therapeutic delivery and facilitate cancer-specific bio-sensing. The integration of gold and albumin further improves biocompatibility, extends circulation time, and enhances tumor targeting, making these conjugates an attractive option for cancer treatment. The review also focuses on the refinement of surface chemistry to achieve precise targeting of cancer cells, as well as the challenges and future prospects for advancing nanogold-albumin systems in clinical applications.
 Namita Jaiswal | Dr Namita Jaiswal is currently a Research Associate at the CSIR-Central Mechanical Engineering Research Institute (CMERI), Durgapur. She obtained her PhD from the National Institute of Technology (NIT), Durgapur, in January 2025, where her research focused on engineering nanogold-albumin conjugates for targeted cancer therapeutics. Her research interests broadly encompass nanobiotechnology, particularly in the development of delivery systems for drugs and biologics. Dr Jaiswal has authored over 15 research articles and contributed a book chapter. |
 Nibedita Mahata | Dr Nibedita Mahata is currently an Assistant Professor at the National Institute of Technology (NIT), Durgapur. She completed her PhD at Jadavpur University. Dr Mahata's research interest is in cell signalling, protein engineering, and developing drug delivery systems. She has published more than 30 research articles. |
 Nripen Chanda | Dr Nripen Chanda is currently a Senior Principal Scientist at the CSIR – Central Mechanical Engineering Research Institute (CMERI), Durgapur, and Professor of Academy of Scientific and Innovative Research (AcSIR). He obtained his PhD from the Indian Institute of Technology Bombay and carried out his post-doctoral research at the University of Missouri-Colombia, USA. Dr Chanda's research interest is in nanomaterial synthesis, nanobiotechnology, and designing and developing micro/nanoscale devices such as sensors, actuators, drug delivery systems, and processes for interdisciplinary research in biomedical/environmental engineering. His research work resulted in seven (7) granted patents, more than 100 publications, and one (1) co-edited book. |
1 Introduction
Cancer remains a global concern, with ever-increasing incidence and mortality rates worldwide, leading to approximately 10 million deaths annually.1 India ranks third globally for cancer cases after China and the United States, with GLOBOCAN predicting a 57.5% increase to 2.08 million cases by 2040 from 2020.2 Conventional chemotherapy employs a diverse array of small-molecule drugs—such as alkylating agents, anthracyclines, antimetabolites, platinum-based compounds, and various inhibitors for microtubules, topoisomerases, tyrosine kinases, and histone deacetylases—administered systemically to reach effective toxic levels. However, because these molecules are typically very small (usually under 5 nm), they are rapidly eliminated by the kidneys, which limits their presence in the bloodstream and shortens their circulation lifetime. The absence of targeting ability confers on them an undesirable bio-distribution, resulting in generic cytotoxicity to both tumor and healthy cells.3 Moreover, prolonged exposure to such agents drives rapid cellular reprogramming, including overexpression of drug efflux transporters and the development of multidrug resistance (MDR), which ultimately contributes to treatment failure in about 90% of cases.4 To advance oncology strategies for early diagnosis, improved therapeutic efficacy, reduced toxicity, and enhanced patient compliance, a key focus is the precise delivery of therapeutic agents to tumor cells while minimizing off-target distribution to healthy tissues. To this end, an integrated effort of interdisciplinary collaboration across engineering, physics, chemistry, biology, and medicine has been pursued over the past several decades. These collaborative efforts have led to rapid advancements in cancer nanomedicine research to overcome the constraints of conventional chemotherapy5—ranging from broad challenges like bio-distribution to more specific small-scale barriers, which can be mitigated by employing cell-specific targeting, molecular transport to particular organelles, and other innovative approaches.Nanotechnology plays a crucial role in this context, encompassing the development of multifunctional nanomaterials capable of diagnosis and imaging,6,7 targeted therapy,8,9 controlled drug release,10 reduced renal clearance and prolonged blood circulation,11 improved bioavailability, and precision medicine.12 Nanoparticles spanning a size spectrum from 1 to 1000 nm exhibit unique characteristics that enhance the effectiveness of anticancer drugs while minimizing adverse effects. Their comparable size enables them to readily interact with proteins (∼1–20 nm), cell surface receptors (∼10 nm), and nucleic acids (∼2 nm), which in turn modify drug pharmacokinetics and promote preferential accumulation in tumors through the enhanced permeability and retention (EPR) effect.13,14 A diverse array of nanostructures, encompassing biomolecule-based entities like liposomes,15 various polymeric nanoparticles,16,17 protein constructs,18,19 ribonucleic acid (RNA) nanoparticles,20 organic carbon-based nanoparticles (such as carbon dots,21 nanodiamonds,22 carbon nanotubes,23,24 and graphene25,26), as well as inorganic nanomaterials made of gold,7,27,28 mesoporous silica, superparamagnetic iron oxide,29 and quantum dots,30 has shown promising results in cancer therapy6 (Table 1). However, the properties of nanostructures undergo radical changes upon entering the body due to interactions occurring at the nano–bio interface in vivo, leading to instabilities like particle aggregation, decomposition, and loss of functionality, which significantly affect delivery efficiency and safety.31 Additionally, contact with physiological fluids leads to biomolecule adsorption and protein corona formation and subsequent loss of their original “synthetic identity” and the acquisition of a new “biological identity”, a significant bottleneck in their successful clinical translation.32,33 Efforts have been made to control the formation of protein coronas on nanoparticle surfaces by altering them with substances such as polyethylene glycol (PEG), carbohydrates, zwitterions, and proteins to enhance colloidal stability and prolong the circulation time in the blood.34–36 Despite these attempts, strategies aimed at conferring targeting specificity remain challenging, as the attachment of targeting ligands to nanocarriers tends to increase the likelihood of corona formation. Consequently, this accounts for the complete loss of their integrity and the failure of numerous nanoparticle-based drug delivery systems in clinical trials.37–41
| Nanomaterial used | Therapeutic molecule | Therapy modality | Tumour model | Status/limitations | Ref. |
|---|---|---|---|---|---|
| Pegylated liposome (Doxil) | Doxorubicin | Chemotherapy | HIV-related Kaposi sarcoma, ovarian cancer, and multiple myeloma | Approved by the FDA; approved in Europe for metastatic breast cancer | 15 and 42 |
| Liposome mifamurtide (Mepact) | Muramyl tripeptide phosphatidyl ethanolamine | Chemotherapy | Non-metastatic, resectable osteosarcoma | Approved in Europe | 6 and 42 |
| Liposomal vincristine (Marqibo) | Vincristine sulfate | Chemotherapy | Acute lymphoblastic leukaemia | Approved by the FDA | 6 and 42 |
| Polymeric methoxy-PEG-poly(D,L-lactide) paclitaxel (Genexol-PM) | Paclitaxel | Chemotherapy | Breast cancer and NSCLC | Approved in South Korea for breast cancer | 6 and 42 |
| Aminosilane-coated superparamagnetic iron oxide (SPIO) (NanoTherm) | — | Hyperthermia | Local ablation of glioblastoma multiforme; prostate and pancreatic cancers | Marketing approval in Europe for glioblastoma; Phase I/II trials in other tumor types | 6 and 42 |
| Albumin based Nab-paclitaxel (Abraxane) | Paclitaxel | Chemotherapy | Breast, lung and pancreatic cancer | Approved by the FDA | 18 and 42 |
| Pegylated liposomal cisplatin (Lipoplatin) | Cisplatin | Chemotherapy | Non-small cell lung cancer (NSCLC) | Phase III | 43 |
| Gold nanoparticle (Aurimmune, (CYT-6091)) | TNF-α bound to gold nanoparticles | Photothermal ablation of tumors | Solid tumors | Phase 1 | 44 and 45 |
| Gold nanoshells (AuroShell) | — | Near-infrared irradiation (NIR) | Head and neck cancer | Phase 0 (pilot study) | 46 |
| Liposomes or lipid-based NPs | Irinotecan and cisplatin | Combination of chemotherapies | In vivo mouse tumour models of small-cell lung cancer (SCLC) | Preclinical study | 47 |
| Poly(lactic-co-glycolic acid) NPs | 6-Thioguanine | Chemotherapy | HeLa cells | Preclinical study | 16 and 17 |
| Carbon nanotubes | Paclitaxel | Chemotherapy | Murine 4T1 breast cancer model | Preclinical study | 23 |
| Carbon nanotubes | siRNA | Combination of hyperthermia and RNAi therapy | In vivo mouse tumour models of prostate cancer | Preclinical study | 24 |
| Graphene nanodots | — | Phototherapy and imaging | MDA-MB231 cancer cells | Preclinical study | 25 |
| Iron oxide NPs | Doxorubicin and curcumin | Combination of chemotherapies | In vivo mouse tumour models of glioma | Preclinical study | 48 |
| Gold nanorods | Doxorubicin | Combination of hyperthermia and chemotherapy | In vivo mouse tumour models of cervical cancer (HeLa) or KB cells | Preclinical study | 49 |
In this context, gold nanoparticles possess precisely regulated geometrical, optical, and surface chemical properties, which are the subject of intensive studies, as evidenced by the growing array of published research on their applications in cancer management. However, despite decades of research, only a handful of gold nanoparticles have advanced into Phase-0 (e.g., AuroShell for head and neck cancers46) or Phase-I (e.g., Aurimmune for solid tumours44) clinical trials for cancer therapy. This limited progress may primarily be attributed to unclear pharmacokinetics, including various aspects such as biocompatibility, bio-distribution, retention, biodegradation, excretion, and immune responses. Furthermore, the inadequate colloidal stability requires the employment of stabilizing agents like PEG, which consequently have adverse effects, including hypersensitivity resulting from complement activation and shortened bio-circulation time upon repeated dosing.32 To overcome the pharmacokinetic limitations and improve the overall pharmacodynamics, serum albumin with a half-life of ∼19 days has garnered significant attention owing to its outstanding properties, including superior biocompatibility, biodegradability, non-immunogenicity, higher drug loading capacity, extended circulation lifetime, and safety for its clinical applications.50,51
A notable example of albumin-based nanotechnology in cancer therapy is Nab-paclitaxel (Abraxane), a first-line paclitaxel (PTX)-loaded albumin nanoformulation-based anti-cancer drug, which has been approved by the US Food and Drug Administration (FDA) for the treatment of several different cancers.50,51 Building on this success, nanogold-albumin conjugates that synergistically combine the unique properties of gold nanoparticles and albumin have garnered significant attention as a hybrid platform for the systematic development of novel cancer therapeutic modalities.33,52 The development of nanogold-albumin for cancer therapeutics primarily follows two key strategies: (1) the supramolecular coating of gold nanoparticles with albumin via active or passive adsorption (GNP-BSA/HSA) and (2) the utilization of albumin as a biological template for the in situ synthesis of ultrasmall gold nanoclusters (GNC-BSA/HSA). These hybrid nanostructures leverage the optical, electronic, and biocompatible features of gold with the natural bioavailability, stability, longer circulation time and drug-binding capabilities of albumin. The integration of these two components in nanogold-albumin conjugates offers several benefits, including enhanced drug loading efficiency, improved target specificity through active and passive targeting mechanisms, and reduced systemic toxicity. The protein coating also mitigates potential immunogenicity and facilitates receptor-mediated uptake in tumors or diseased tissues, making these conjugates particularly valuable in cancer therapy and other precision medicine applications. Ongoing research highlights their utility across a wide range of biomedical applications including vehicles for drug delivery,53 gene editing, protein delivery,54 immunotherapy, metabolism targeting,55,56 photothermal and photodynamic therapy,7 radiation and electromagnetic therapy, imaging and theranostic applications, and many more52 (Fig. 1). The ability to functionalize their surfaces further expands their applicability, enabling the conjugates to be tailored for specific therapeutic or diagnostic purposes. Like albumin, the unique combinations of nanogold with other proteins are extensively explored as a versatile tool in advancing modern cancer nanomedicine (Table 2).
 | ||
| Fig. 1 Schematic illustration of nanogold-albumin conjugates for application in next-generation cancer therapy and diagnostics. Portions of this figure have been adapted/reproduced from Choi et al. with permission from RSC, Copyright © 2015 and Wu et al. with permission from Elsevier, Copyright © 2022. Portions of this figure were also produced using Servier Medical Art (https://smart.servier.com). Servier Medical Art by Servier is licensed under a CC BY 4.0 Licence (https://creativecommons.org/licenses/by/4.0/). | ||
| Nanomaterial used | Protein/drug/targeting agent | Therapy/diagnostics | Tumour model/s | Remarks/limitations | Ref. |
|---|---|---|---|---|---|
| Gold nanoparticles | Anti-epidermal growth factor receptor (anti-EGFR) antibodies for targeting | SPR-based imaging diagnosis of oral epithelial living cancer cells in vivo and in vitro | HOC 313 clone 8 and HSC 3 cells | Specific binding to the cancerous cells with six times greater affinity than the noncancerous cells; impact of nanoparticles on the tumor immune microenvironment needs to be studied. | 57 |
| Gold nanorods | Mouse serum, chlorin e6 (Ce6) | Combination of PDT and PTT therapy | OSCC cells, female NCr OSCC xenograft nude mice | Significant PTT heating-induced tumor ablation, coupled with PDT-induced cell killing by oxidative stress, and subsequently complete tumor elimination with no regrowth; only short-term biocompatibility studies were conducted. | 58 |
| Gold nanorods | CRISPR/Cas9-ribonucleoprotein, nuclear targeting peptide (TAT) for targeting | Combination of targeted gene editing and PTT therapy | MCF-7 cells | Enhanced antitumor effect through the combination of gene editing from the loaded sgRNA/Cas9 complex and photothermal effect from gold nanorods; further studies are needed on biological performance, stability, and bio-distribution in vivo. | 59 |
| Gold nanorods | Apolipoprotein E, chlorin e6 (Ce6) | Combination of PTT and PDT therapy | Cal 27 cells | Enhanced death in Cal 27 cells and increased intracellular generation of ROS; the bio-distribution characteristics and therapeutic performance in vivo need to be evaluated. | 60 |
| Gold nanorods | Human serum, chlorin e6, doxorubicin | Multimodal cancer therapy: PDT, PTT and chemotherapy | Cal 27 cells | Enhanced uptake by Cal 27 cells followed by a near complete eradication of cancer cells; the bio-distribution characteristics and therapeutic performance in vivo need to be evaluated. | 61 |
| Gold nanorods | Anti-epidermal growth factor receptor (anti-EGFR) antibodies for targeting | Photoacoustic imaging (PAI)-guided near-infrared photothermal therapy | MDA-MB-231, MCF-7, BT-474 cells; female BALB/c nude mice injected with MDA-MB-231-Luc cells | Synergistic anti-proliferative and apoptotic actions in triple negative breast cancer (TNBC) through upregulation of HSP70 and cleaved caspase-3; further animal and clinical trials are required to assess distribution characteristics and safety. | 62 |
| Gold nanorods | Anti-carbonic anhydrase IX (CAIX) antibody | Photothermal therapy | HT29 cells, Swiss Nu/Nu mice were xenografted with HT29 tumors | Selective internalization in CAIX-overexpressing hypoxic cells, highly effective in eliminating cancer cells; further animal and clinical trials are required to assess safety and efficacy. | 63 |
| Gold nanoclusters | Keratin, doxorubicin | Chemotherapy, NIR fluorescence imaging, MRI | 4T1 cells | Significant reduction in tumor growth, enhanced NIR fluorescence imaging, high colloid stability; studies are needed on biological performance, bio-distribution, and therapeutic performance in vivo. | 64 |
| Gold nanoclusters | Ribonuclease-A, vitamin B12 for targeting | Imaging and diagnostics | Caco-2 cells | Suitable for simultaneous targeting and imaging of cancer at the cellular level; detailed studies are needed on imaging and diagnostic potential in vivo. | 65 |
| Gold nanoclusters | Ribonuclease-A | Imaging and diagnostics | Caco-2, and HCT116 cells, C57BL/6 mice | Could successfully distinguish intestinal tumor mice from healthy mice, indicating a potential utility for early diagnosis of intestinal tumors; further clinical trials are required to assess safety and efficacy. | 66 |
This review highlights recent advancements in the development of nanogold-albumin conjugates for the delivery of small-molecule drugs, proteins, and other biologics aimed at achieving tumor-suppressive effects. By offering a comprehensive overview of the current research landscape, this work aims to provide critical insights that support the rational design and clinical translation of nanogold-albumin platforms, ultimately advancing their application in enhancing cancer therapeutics.
2 Synthesis and unique properties of nanogold-albumin conjugates toward cancer management
The synthetic techniques employed for formulation of nanogold-albumin conjugates are dictated by their intended application and the specific drug molecules or biologics they are designed to encapsulate. Several established and advanced fabrication techniques, including passive adsorption, active adsorption, self-assembly, desolvation and cross-linking, emulsification and thermal gelation have been explored for the development of nanogold-albumin systems. Each of these methods is based on fundamental chemical and physical principles and offers distinct advantages in optimizing nanoparticle size, morphology, colloidal stability, encapsulation efficiency and surface characteristics for efficient loading, and release behaviour. Owing to the integrated properties of gold and albumin, the nanogold-albumin-derived structures exhibit variations in size, shape, biophysical and optical properties, and biocompatibility. These platforms further benefit from albumin's ability to interact with receptors overexpressed in many diseased tissues and cells, enabling targeted delivery to disease sites without requiring additional specific ligands.19 Different methods of nanogold-albumin synthesis are discussed in subsequent sections.2.1 Synthesis techniques of nanogold-albumin conjugates
The existing synthesis methodologies can broadly be classified into two categories: (1) supramolecular coating of gold nanoparticles (GNPs) with albumin via active or passive adsorption and (2) utilizing albumin as a template for the in situ synthesis of ultra-small gold nanoclusters (GNCs) (Fig. 2). Supramolecular capping of GNPs with albumin is achieved through electrostatic or hydrophobic interactions between the gold nanoparticles and albumin or through the chemisorption of thiols on the gold surface. On the other hand, the albumin-templated approach enables the formation of GNCs through either bottom-up or top-down methodologies, resulting in unique fluorescence properties driven by discrete electronic transitions distinct from those observed in GNPs.67 The bottom-up approach, known as the atoms-to-clusters synthesis pathway, involves assembling GNCs from individual ions and atoms. In contrast, the top-down method is a traditional technique where GNPs are fabricated first and subsequently etched with excess ligands to generate GNCs.67 | ||
| Fig. 2 Schematic for synthesis and modification of nanogold-albumin types. The development of nanogold-albumin conjugates primarily follows two strategies: (A) supramolecular coating of gold nanoparticles with albumin via active or passive adsorption (GNP-BSA/HSA), and (B) utilizing albumin as a template for the in situ synthesis of ultrasmall gold nanoclusters (GNC-BSA/HSA). This figure has been adapted/reproduced from Jaiswal et al. with permission from Elsevier, Copyright © 2024.56 | ||
Furthermore, recent advancements in nanogold-albumin conjugate synthesis have focused on rapid, eco-friendly methodologies that enhance efficiency and control over nanoparticle formation. One such approach involves microwave (MW) irradiation, which significantly accelerates the synthesis of bovine serum albumin-gold nanoclusters (GNC-BSA), reducing the reaction time from several hours to just a few minutes.67 Yan et al. demonstrated the MW-assisted synthesis of red-emitting GNC-BSA, wherein a BSA solution was mixed with an Au3+ salt solution, followed by NaOH addition and MW irradiation for 6 minutes. This process resulted in a colour change from light yellow to dark brown, indicating successful nanocluster formation.76
Alternatively, ultrasonic irradiation, or sonochemical synthesis, has been explored as a rapid method for fabricating GNC-BSA with near-infrared (NIR) emission. Liu et al. introduced this approach by adding an aqueous Au3+ solution to a BSA solution, adjusting the pH to 12, and subjecting the mixture to ultrasonic irradiation under ambient conditions, producing a light brown colloidal solution.77 More recently, a photocatalytic strategy has been employed for the controlled synthesis of GNC-BSA with tunable fluorescence.78 In this method, silver nanoclusters were initially generated via UV light-induced reduction of silver ions. These pre-formed silver nanoclusters subsequently facilitated the reduction of HAuCl4 to GNCs, which were stabilized within BSA molecules. The resulting fluorescence emission of the GNC-BSA was adjustable, ranging from 570 to 620 nm, depending on the synthesis conditions. These innovative approaches demonstrate the potential for the rapid, scalable, and environmentally friendly synthesis of nanogold-albumin conjugates, making them promising candidates for biomedical applications such as drug delivery, bioimaging, and theranostics.
Pradeep et al. reported the use of bovine serum albumin (BSA) as an etching ligand to synthesize red-fluorescent GNC-BSA.79 Initially, mercaptosuccinic acid (MSA)-stabilized GNPs were synthesized, which then underwent BSA-mediated core etching under alkaline conditions (pH 12). This process resulted in GNC-BSA consisting of 38 Au atoms (Au38) with a photoluminescence quantum yield of approximately 4%. The reaction progress was monitored by tracking the gradual increase in photoluminescence (PL) intensity, corresponding to the formation of smaller, highly fluorescent nanoclusters. Despite its widespread application in the synthesis of ligand-capped GNCs, the top-down approach remains underexplored for protein-based nanoclusters. This limitation arises from the harsh chemical conditions required for core-etching, which can destabilize proteins, leading to structural denaturation and broad size distributions in the resulting nanoclusters. Further research is needed to elucidate the dynamics of nanocluster formation via this method and to optimize BSA-mediated etching strategies, ensuring higher stability and uniformity of the protein-stabilized gold nanoclusters.
2.2 Bio-physico-chemical properties
The physico-chemical characteristics of nanoparticles, such as size, shape, chemical composition, crystal structure, surface area, surface energy, surface roughness, and stability, impact the unique properties of nanostructures, which in turn play a crucial role in determining their effectiveness as drug delivery and theranostics platforms. The rapid advancement of synthetic procedures has enabled precise control over these properties, allowing the fabrication of nanogold-albumin conjugates with customizable attributes even in basic laboratory setups. By employing GNPs of different shapes—such as nanospheres, nanorods, nanocages, nanoshells, nanostars, nanoprisms, nanovesicles, nanoflowers, nanocubes, and ultrasmall nanoclusters (GNCs)—researchers can tailor the properties and functionalities of nanogold-albumin conjugates to address specific biomedical needs.28 These diverse geometries influence the biophysical interactions at the nano–bio interface, and a precise understanding of these interactions is helpful for drug encapsulation, specific targeting, stimulus-responsive drug delivery, theranostics, and enzymatic mimetic applications.72,83The nanogold-albumin platform offers versatile surface chemistry, combining the functional attributes of the GNP core with the albumin's surface, comprising both hydrophobic and hydrophilic domains and abundant charged amino acids. This provides numerous chemically active groups for surface functionalization for anchoring targeting moieties and also serves as a platform for loading drug molecules for cancer therapy.19 In a recent study by Jaiswal et al., a ground state complex formation was reported between cisplatin (CPT) bound BSA and GNP. Spectroscopic analysis revealed a stronger binding affinity of the BSA-CPT conjugate to GNP compared with BSA alone, indicating a greater apparent association constant, suggesting CPT-induced conformational changes in the BSA, leading to stronger adsorption of the BSA-CPT conjugate onto GNP.90
By altering the synthesis parameters to alkaline conditions (pH ∼12), albumin serves as a template for synthesizing fluorescent quantum-sized nanogold-albumin conjugates (GNC-BSA, typically below 2 nm).67 Recent research by Zhong et al. highlights the strong correlation between the ultrasmall size and size-tunable physicochemical properties of fluorescent GNC-BSA and the number of charged groups on the BSA surface.91 To achieve BSA variants with more positive net charges (cBSA, +13.9 ± 0.9 mV) and more negative charges (aBSA, −31.4 ± 1.2 mV), ethylenediamine and succinic anhydride are employed to react with the carboxyl and amino groups of BSA (nBSA, −9.7 ± 1.1 mV), respectively. The mean core diameters of GNC-cBSA, GNC-nBSA, and GNC-aBSA thus obtained are 1.91 ± 0.11, 2.54 ± 0.23, and 2.97 ± 0.2 nm, respectively. These differences in GNC-BSA size likely stem from variations in the number of amino groups between native and modified BSA.
The influence of nanoparticle shape on albumin interactions has also been explored through MD simulations. Studies comparing the binding of nanocubes and nanospheres with HSA showed that nanocubes induce greater protein unfolding compared with nanospheres. These interactions alter albumin angles and bond lengths, with nanocube interactions significantly modifying the helix length and polarity, while nanosphere interactions predominantly affect the psi (Ψ) and phi (Φ) angles.94 Ramezani et al. investigated the docking interactions between HSA and GNPs, employing MD simulations and the GOLP force field to analyze protein structural changes.95 Their findings demonstrate that HSA undergoes denaturation upon GNP adsorption, with a marked decrease in alpha-helix content. Domain III, known for its fatty acid binding sites, plays a key role in the adsorption process. Critical amino acids involved in HSA-GNP interactions include Lys464, Thr504, Phe505, and Leu581. Additionally, increased fluctuations in certain protein domains indicate structural destabilization following nanoparticle adsorption.
In another significant study, Rajan et al. examined the binding interactions of BSA and HSA with gold nanorods (AuNRs) to determine the nature and extent of contact between serum albumins and nanorod surfaces.84 Computational studies revealed that the planar surface of AuNRs interacts with cysteine (Cys) residues (Cys-316 and Cys-368) from BSA and HSA, forming Au–thiol coordination bonds with bond lengths of 3.722 Å and 3.442 Å, respectively. The presence of a sulfide linkage facilitates stable nanogold-albumin conjugate formation, as confirmed by MD simulation results, indicating high stability and strong protein–nanoparticle interactions. These molecular simulation findings collectively highlight the significant role of nanoparticle size, shape, and surface chemistry in determining albumin conformational stability and interaction dynamics, which is indispensable for predicting protein corona formation, assessing drug delivery potential, and optimizing the nanogold-albumin conjugates for biomedical applications.
2.3 Optical properties
The optical properties of gold nanoparticles (GNPs) differ markedly from those of bulk gold due to variations in electron behaviour at the nanoscale. While bulk gold exhibits a characteristic yellow colour, GNPs in solution display a striking red appearance.67,96 In bulk gold, the energy levels of electrons are compressed, forming a continuous spectrum without a clear band gap between the valence and conduction bands. However, GNPs, typically sized between 2–100 nm, are comparable to, or smaller than, the mean free path of electrons, facilitating interactions with electromagnetic waves and leading to collective oscillations of surface electrons – a phenomenon famously referred to as the surface plasmon resonance (SPR) effect. The SPR is the source of the ruby red colour of conventional GNPs.97 The dependence of the resonant wavelength on the nanostructures’ size, shape, and geometry provides opportunities to manipulate the optical properties as needed.In nanogold-albumin conjugates, the optical properties are closely related to their structures, including the morphology of the nanostructures and the molecular interactions present. For instance, the different structures of GNPs (sphere, rod, shell, cage, star, flower), together with the nature of the chemical interaction between GNPs and albumin (adsorption or covalent binding), contribute to the unique optical properties and characteristics of nanogold-albumin, which further decide their subsequent applications in imaging, therapy, and theranostics (Table 3).96 The variation in SPR absorbance in nanogold-albumin conjugates might arise due to the subtle differences in surface electrostatic interactions and structural differences of albumin from different sources.51 Furthermore, albumins, such as ovalbumin, bovine serum albumin (BSA), or human serum albumin (HSA), vary in molecular weight, size, structure, S–S bridges, and SH groups. These variations significantly affect the binding abilities, surface modifications, and the formation of nanogold-albumin conjugates.51 Of note, the optical properties of nanogold-albumin could easily be tailored for the desired absorption/scattering ratios and wavelengths based on the sizes and shapes of the GNPs used for synthesis. For instance, HSA-conjugated GNPs show increased SPR absorbance with a 2–3 nm red shift, while the BSA-conjugated ones attenuate slightly with a 1 nm red shift and broader baseline.98 A change in pH from alkaline to acidic results in a broadening and red shift of the SPR band for the BSA-conjugated gold nanospheres.87 Interestingly, BSA-stabilized gold nanorods exhibit optical and colloidal properties similar to the CTAB-stabilized ones with no significant changes in their LSPRs characteristic peaks.69 The absorption/scattering wavelength of nanogold-albumin formed by gold nanocages or nanostars could easily be tailored by adjusting the thickness of the wall, the lengths of the outer edges of the nanocage, and the number of tips in the plane, respectively.99
| Type of nanogold-albumin NP | Mechanism of interaction | UV-Visible | Fluorescence | Lifetime (ns) | QY (%) | Ref. | ||
|---|---|---|---|---|---|---|---|---|
| λ max (nm) | Shift (nm) | λ ex (nm) | λ em (nm) | |||||
| GNP-BSAFA-EGFP | Hydrophobic | λ T = 510 | λ L = 846 | — | — | — | — | 54 |
| GNP-BSAFA-RNaseA | λ L = 819 | λ L = 842 | ||||||
| GNC-BSA-TG | Hydrophobic, hydrogen bonding, Au–S interaction | — | — | 520 | 645 | — | — | 56 |
| GNP-HSA, GNP-BSA | Hydrophobic | λ T = 521 | λ T = 524 | — | — | — | — | 98 |
| λ T = 522 | ||||||||
| GNC-BSA (Au25) | Au–S bonding | — | — | 480 | 640 | — | 6 | 73 |
| GNC-BSA (Au16) | Au–S bonding | — | — | 500 | 608 | 170 | — | 102 |
| GNC-BSA (Au8), GNC-BSA (Au25) | Au–S bonding | — | — | 370 | 450 | 0.8 ± 0.2 | 6.07 | 103 |
| 370, 530 | 685 | 3.0 ± 0.3 | 5.53 | |||||
| 1.78 ± 0.3 | ||||||||
| 184 ± 7.0 | ||||||||
| GNC-BSA (Au25) | Au–S bonding | — | — | 470 | 660 | 1880 | ∼6 | 104 |
| 440 | ||||||||
| 9 | ||||||||
| GNC-cBSA, GNC-nBSA, GNC-aBSA | Au–S bonding | — | — | 500 | 673 | 2150 | — | 91 |
| 684 | 1930 | |||||||
| 691 | 1820 | |||||||
| GNC-BSA-FA | Au–S bonding | — | — | 530, 569 | 674 | — | 5.7 | 105 |
Further reduction in the size of gold nanoparticles (GNPs) to the scale of a few to several hundred atoms—approaching the Fermi wavelength of electrons (∼0.5 nm for gold)—leads to the formation of extremely small gold nanoclusters (GNCs). These GNCs typically range in size from 1–3 nm and exhibit unique, molecule-like properties due to discrete electronic transitions, in contrast to the continuous plasmonic behavior observed in larger GNPs. These quantum-sized GNCs stabilized by albumin, first reported by Xie et al. via a ‘green’ synthetic process where BSA was both a reducing agent and a stabilizer, yielded bright red-emitting GNC-BSA (λem max = 640 nm) with a quantum yield (QY) of ∼6%.73 The red fluorescence of GNC-BSA stems from the 25 Au atoms (Au25) stabilized by the BSA.100 These newer nanogold-albumin conjugates exhibit remarkable photostability, biocompatibility, high emission rates, and large Stokes shifts. Their photoluminescence could be effectively tuned over broad wavelengths ranging from near-infrared (NIR) to ultraviolet (UV) regions by tuning their core size.67 Tuning synthesis parameters is essential for controlling the number of metal atoms or ions, which in turn significantly affects the size and optical properties of gold nanoclusters (GNCs). Microwave-assisted synthesis at135 °C for 4 min results in small-sized (3.1 ± 0.4 nm) blue-emitting GNC-BSA, whereas synthesis at 80 °C for 4 min yields larger (4.2 ± 0.5 nm) red-emitting GNC-BSA.101 This variation in synthesis temperature leads to increased luminescence intensity at 436 nm (at 135 °C) and 676 nm (at 80 °C), corresponding to red and blue GNC-BSA, respectively.101 Notably, the optical properties of GNC-BSA are also influenced by the number of charged groups on the surface of the BSA.91 The fluorescence emission and luminescence lifetime of GNC-BSA is highest for positively charged albumin, followed by neutral, and least for negatively charged. The findings above strongly indicate that nanogold-albumin synthesized from GNP/GNC and different albumin variants exhibits markedly different photophysical properties including size-dependent emission and surface-enhanced fluorescence, making it ideal for high-sensitivity imaging in cellular and deep-tissue applications.
2.4 Biocompatibility
Biocompatibility is the ability of a material to perform with an appropriate host response in a specific application.106 The majority of the biocompatible nanomedicines, upon contact with physiological fluids, gets coated with various biomolecules (corona formation), making them susceptible to clearance by the mononuclear phagocytic system (MPS).107 The corona formation process, driven by the need to reduce energy, involves the entropy-driven displacement of water molecules, particle surface charge compensation, and shielding of hydrophobic regions. The nature of the binding proteins present in biological fluids controls the phagocytosis of nanoparticles, governing their time in the systemic circulation. Previous research suggests that the retention and biocompatibility of nanoparticles in the systemic circulation are significantly enhanced in the presence of albumin (dysopsonins protein), which inhibits the complement activation, thus reducing the susceptibility of nanoparticles to phagocytosis and prolonging the circulation time in the bloodstream. In this regard, extensive research has been undertaken to study nanogold-albumin's biocompatibility and potential toxicity by employing both in vitro and in vivo approaches.52 Tebbe et al. have demonstrated that gold nanorod-BSA, synthesized after the complete replacement of CTAB with BSA in a large range of aspect ratios and sizes, is highly stable at pH values above, as well as below, the isoelectric point of BSA (pI = 4.8). These nanostructures exhibited remarkable colloidal stability in aqueous solutions at different conditions with or without 10% bovine calf serum.69 Khullar et al. showed that GNP-BSA formed by unfolding BSA to passivate the GNP surface showed negligible hemolysis and cytotoxic responses to cells compared with cationic surfactant-coated GNP controls.108 Similarly, positively charged GNP-BSA, synthesized using a green synthesis method with various diameters (80–1500 nm), was efficiently internalized by MG-63 osteosarcoma cells and showed minimal toxicity to the cells.109 Additionally, GNP-BSA were found to exhibit high colloidal stability and extreme compatibility at high concentrations (100 μg ml−1) towards normal (L929) and cancerous (KB) cells without the generation of reactive oxygen species (ROS) and hemolytic responses towards red blood cells.110 Overall, the collective evidence suggests that nanogold-albumin exhibits diminished hemolytic activity and low toxicity, making it suitable for drug delivery applications at targeted sites.52 Compared with in vitro studies, in vivo and ex vivo biocompatibility evaluation in animal models is a better measure to analyze the potential impact of nanogold-albumin platforms on human health. One notable ex vivo study by Mocan et al. focused on using GNP-BSA as an active vector to target liver cells.111 GNP-BSA administered intra-arterially into the ex vivo-perfused liver specimens obtained from hepatocellular carcinoma patients showed selective accumulation of GNP-BSA punctuate structures mainly spread into the malignant tissue and most predominant inside the tumour core. Furthermore, tissue obtained from adjacent liver parenchyma was not seriously affected, indicating the biocompatibility of the nanostructures toward healthy tissues. Another notable study in mice with GNP stably conjugated with HSA (GNP-HSA) showed massively reduced liver retention (52%) compared with apolipoprotein E (GNP-apoE, 72%) or citrate-stabilized GNPs (>95%).112 The authors also observed an increased blood circulation time of GNP-HSA. Additionally, higher retention of GNP-HSA in the lungs and brain was observed compared with GNS-apoE and citrate-stabilized GNPs. The ability of this nanogold-albumin platform to cross the blood–brain barrier and target the lungs may be beneficial in overcoming some of the existing obstacles in brain- and lung-related cancer therapies.The interaction with the immune system presents a major challenge to the success of cancer nanomedicine, with concerns about potential toxicity, as well as the risk of triggering allergic reactions and inflammation, remaining key considerations for nanomaterials in biomedical applications. Nanogold-albumin-based carriers show promise in overcoming phagocytosis by monocytic and dendritic cells, as well as macrophages, by reducing particle adhesion to cell membranes.32 Li et al. demonstrated that the dispersion and stabilization of gold nanorods coated with BSA (GNP-BSA) depends on the BSA to GNP ratio; lower ratios show agglomeration, while higher ratios support colloidal stability.113 Interestingly, the authors observed a significantly reduced uptake of GNP-BSA (2 μg mL−1) by RAW 264.7 macrophages, demonstrating the stealth effect and the potential of these nanogold-albumin platforms to escape clearance by the MPS.
3 Nanogold-albumin conjugates as delivery and imaging agents
3.1 Drug delivery: EPR effect and release mechanism
The development of next-generation nanocarriers for drug delivery relies on the selective targeting of cancer cells by overcoming the limitations of conventional delivery methods. These limitations range from large-scale challenges like bio-distribution to small-scale barriers like intracellular trafficking. Critical factors, including nanoparticle size, geometry, surface charge, and modifications, are pivotal in determining their hemodynamic behaviour and interaction with the tumor microenvironment (TME). These properties influence the enhanced permeability and retention (EPR) effect, which governs the systemic delivery of drugs and subsequent therapeutic outcomes.12 The tumour microenvironment (TME) significantly influences the fate of nanoparticles and, consequently, the efficacy of cancer nanomedicine. The hallmark features of the TME—heterogeneous and abnormally leaky vasculature—facilitate nanoparticle extravasation and preferential accumulation at tumor sites, a phenomenon known as the EPR effect.12 Studies indicate that the neo-vascularization in cancers, defective angiogenesis, and impaired lymphatic drainage contribute to the increased retention of up to 10–15% of administered nanomedicine, compared with 0.1% of free drugs.114 The EPR effect constitutes “passively targeted” nanoparticles relying on their nanometric size (∼100 to ∼200 nm) for preferential accumulation in the tumour.115 The effectiveness of several nanoparticles currently utilized in clinical settings, such as Doxil™, Abraxane™, Marqibo™, DaunoXome™, and Onivyde™ in the US; Myocet™ and Mepact™ in Europe; Genexol-PM™ in Korea; and SMANCS™ in Japan, provides additional evidence supporting the significance of the EPR effect in cancer nanomedicine.116However, interpreting EPR as a product of leaky tumour vasculature and poor lymphatic drainage in complex biological systems may be an oversimplified interpretation. The systemic administration of nanoparticles must navigate multiple physiological barriers, including nanoparticle-protein interactions, blood circulation dynamics, clearance by the mononuclear phagocyte system (MPS) or reticuloendothelial system (RES), extravasation into the perivascular tumor microenvironment (TME), tumor tissue penetration, and cellular internalization. These factors collectively and significantly influence the manifestation and effectiveness of the EPR effect.6 In this regard, the nanogold-albumin-based carriers, with albumin acting in stealth fashion towards the MPS, provide a means of precisely controlling the interactions at the nano–bio interface, facilitating the delivery of encapsulated drugs, genes, or other large molecules, offering a method for tailored therapeutic interventions (Table 4). Moreover, the ability to fine-tune the size, geometry, charge, and surface modifications of nanogold-albumin conjugates makes them well-suited for EPR-based cancer nanomedicine.
| Nanogold-albumin platform | Drug molecule | Type of modification/mechanism of drug loading | Tumor model | Ref. |
|---|---|---|---|---|
| Gold nanorods stabilized with serum albumin | Doxorubicin (DOX) | Glutaraldehyde cross-linking/alcohol denaturation of albumin DOX loading by electrostatic interaction | Tramp-C1, and RAW 264.7 cells | 117 |
| Gold nanorods encapsulated in HSA nanoparticles | Paclitaxel (PTX) | Glutaraldehyde cross-linking of albumin PTX loading by hydrophobic interaction | 4T1 cells | 120 |
| Gold nanospheres stabilized with BSA | Gemcitabine | BSA acts as a reducing and stabilizing agent for GEM loading by electrostatic layer-by-layer assembly | A549 cells | 122 |
| Gold nanoclusters stabilized with BSA | GNC-BSA concentration-dependent cytotoxicity | BSA acts as a reducing and stabilizing agent | HepG-2 cells; nude BALB/c mice injected subcutaneously with HepG-2 cells | 123 |
| Gold nanoclusters stabilized with BSA | Curcumin | BSA and Cur act as reducing and stabilizing agents | HeLa and COS-7 cells | 53 |
| Gold nanoclusters stabilized with BSA in oil–water based nanocapsules | Curcumin | Self-assembled core–shell structure at oil–water interface stabilized by GNC-BSA and encapsulated with Cur in oil phase | SH-SY5Y cells | 124 |
| Gold nanoclusters stabilized with BSA | Kaempferol | BSA and kaempferol as reducing and stabilizing agents | A549 cells | 125 |
| Gold nanoclusters stabilized with BSA | DOX and SN-38 (camptothecin analogue) | Conjugation to BSA by disulphide and melamide linkers which are pH and redox sensitive | MCF-7, MDA-MB-231, and Panc-1 cells | 126 |
| Gold nanoclusters stabilized with BSA | Quercetin | Quercetin bound to GNC-BSA through Au-OH interactions | A549 cells | 127 |
| Gold nanoclusters stabilized with BSA | Paclitaxel and curcumin | PTX and Cur binds GNC-BSA through a hydrophobic interactions | KYSE150 cells | 128 |
Striking a balance between the MPS and RES systems and precise control over drug release is critical for enhancing EPR-based targeting to ensure optimal delivery of therapeutic agents with nanogold-albumin conjugates. With this objective, Chiu et al. recently developed homogeneous core–shell gold nanorod/serum albumin (GNP@SA) co-loaded with doxorubicin (DOX) using glutaraldehyde (GTA) crosslinking (GNP@DOX:SAs (GTA)) or a denaturing method using methanol/ethanol (EM) (GNP@DOX:SAs (EM)).117 The GTA cross-linked GNP@DOX:SAs show high colloidal stability and considerably low protein corona formation. The system exhibits reduced macrophage phagocytosis and increased interaction with cancer cells, resulting in higher cellular uptake. This GTA cross-linked nanogold-albumin could accommodate very high DOX loading of ∼45% with <1% drug leakage in biological fluids and exhibits prolonged stability over a week in aqueous dispersions. Furthermore, GNP@DOX:SAs exert superior therapeutic efficacy and produced in vivo tumour growth inhibition upon NIR laser exposure as assessed by tail vein injections in prostrate tumour-bearing mice through combinatorial photothermal, photoacoustic, and chemotherapy approaches. Notably, the GNP@DOX:SAs (GTA) show greater accumulation at the tumour site than those produced with EM while reducing accumulation in RES clearance organs like the spleen, probably due to the EPR effect (Fig. 3A and B). The desolvation and glutaraldehyde cross-linking approach can be used for higher loading of the chemotherapeutic drug in albumin-stabilized gold nanorod conjugate (GNP@HSA-PTX).118,119 Peralta et al. investigated the influence of cross-linking on the loading efficiency of the chemotherapeutic drug paclitaxel (PTX) in a nanogold-albumin conjugate developed using gold nanorods and HAS (GNP@HSA-PTX). Their findings revealed that the presence of nanorods resulted in a significant enhancement of drug-loading capacity, with an approximately 45% increase compared with albumin-only nanoparticles. Specifically, the nanogold-albumin carrier achieved a PTX loading of 91.8 ± 9 μg, compared with 63.3 ± 14 μg for the albumin-only system.120 Furthermore, cross-linking with 20% and 40% of glutaraldehyde shows a variation in PTX loading capacity of 53 ± 49 μg and 92 ± 14 μg, respectively. GNP@HSA-PTX shows simultaneous chemotherapeutic and photothermal therapy on 4T1 breast cancer cells, with the bulk particle solution reaching temperatures of up to 46 °C following 15 minutes of NIR laser exposure. Treatment of 4T1 mouse breast cancer cells with GNP@HSA-PTX nanoparticles at a concentration of 20 μg PTX per mL causes approximately 82% cell death without irradiation and nearly 94% achieved after a single irradiation session. This hybrid nanogold-albumin system offers significant potential for integration with targeting ligands such as antibodies, enabling the development of a versatile and multimodal treatment platform for effective cancer management.
 | ||
| Fig. 3 Nanogold-albumin in passive targeting. (A) Dark-field images for uptake of GNP@SAs (GTA) and NR@SAs (EM) by RAW 264.7 macrophages and Tramp-C1 cancer cells with and without cytochalasin D pre-treatment; (B) evaluation of in vitro DOX penetration by GNP@DOX:SAs (GTA), GNP@DOX:SAs (EM), or free DOX in 3D tumor spheroids as observed using confocal microscopy; This figure has been adapted/reproduced from Chiu et al. with permission from the American Chemical Society, Copyright © 2018;117 (C) TEM images of A549 cells with and without GNP@BSA-Gem treatment at different magnifications. This figure has been adapted/reproduced from Wang et al. with permission from Elsevier, Copyright © 2018.122 | ||
It is well established that positively charged nanoparticles exhibit improved cellular uptake due to ionic interactions with the negatively charged cell membrane.121 In this regard, positively charged nanogold-albumin conjugates are promising platforms for loading negatively charged drug molecules through electrostatic interaction. Wang et al. developed BSA-stabilized gold nanospheres (GNP@BSA) with an approximate diameter of 10 nm through a facile one-pot synthesis method, utilizing the reduction of chloroauric acid (HAuCl4) with BSA as the stabilizer and hydrazine monohydrate as the reducing agent. These nanoparticles exhibited a positive surface charge of 28.73 ± 0.92 mV. Gemcitabine, a chemotherapeutic agent with a net negative charge of −10.42 ± 1.44 mV, was then attached to the GNP@BSA through electrostatic layer-by-layer assembly, resulting in a final nanoconjugate (GNP@BSA-gemcitabine) with a positive surface charge of 5.07 ± 2.93 mV. In vitro assays in pulmonary carcinoma cells showed that the GNP@BSA system demonstrated high biocompatibility, while GNP@BSA-gemcitabine exhibited very high cell death compared with pristine gemcitabine (Fig. 3C).122
Nanogold-albumin derived from GNCs is extensively investigated as a drug delivery system, primarily without light activation. A pioneering study by Dong et al. reveals that BSA-stabilized GNCs could elicit a dose- and time-dependent decline in cell viabilities, and HUVECs (umbilical vein endothelial cells), which had a higher intake of GNC-BSA than A875 (melanoma cells), exhibited more toxicity. Furthermore, their research highlighted the significant inhibition of tumour growth in mouse models with subcutaneous HepG-2 liver tumours by GNC-BSA alone, suggesting its potential as a standalone anti-cancer agent. Interestingly, their findings indicated that GNC-BSA concentrations of 5 and 20 nM demonstrated substantial toxicity on tumour cells, impeding tumor growth and safeguarding the liver from tumour-induced effects.123
The nanogold-albumin conjugate can effectively deliver flavonoid-based drugs such as curcumin,53,124 kaempferol,125 and quercetin127 for cancer therapy. Curcumin can directly be conjugated to BSA-capped GNCs (GNC-BSA-curcumin), which exhibit bright fluorescence (λex/λem = 550/650 nm) and show minimal toxicity in the normal kidney fibroblast cell line COS-7 (∼100% cell survival) while displaying considerable cytotoxicity and morphological damage in human cervical cancer cells HeLa (∼15% cell survival) at a concentration of 100 μg mL−1.53 Curcumin can also be loaded in GNC-BSA nanocapsules by dissolving curcumin in the oil phase (composed of undecylenic acid) and mixing with the water phase consisting of GNC-BSA.124 These nanocapsules demonstrate more significant growth inhibition of SH-SY5Y (neuroblastoma tumor cells, IC50 = 14.3 ± 0.35 nM) growth compared with free curcumin (IC50 = 115.6 ± 2.28 nM) or GNC-BSA (IC50 = 63.85 ± 2.79 nM) alone, probably due to a synergistic induction of cellular apoptosis for this particular nanocarrier system.124 The natural flavonoid drug kaempferol can also be delivered by GNC-BSA conjugate (GNC-BSA-kaempferol), where the drug is stabilized via physical interactions with the nanogold-albumin.125 The GNC-BSA-kaempferol conjugate demonstrates minimal to no toxicity toward HK-2 (normal human kidney cells), yet it successfully killed over 70% of A549 (lung cancer) cells at a concentration of 25 μg mL−1. Furthermore, the GNC-BSA-kaempferol effectively reduced the migration rate of HeLa cells. Similarly, Lakshmi et al. developed a GNC-BSA platform to deliver the flavonoid quercetin.127 Quercetin was bound to GNC-BSA through Au–OH interactions, and exhibits stable fluorescence (λex/λem = 360/568 nm) over a period of one month. This nanogold-albumin conjugate demonstrates efficient cellular uptake, and shows significant cytotoxicity against A549 (lung cancer) cells, with minimal toxicity towards HDFa (healthy fibroblast) cells.
Intracellular activation and controlled drug release are preferred strategies for effective chemotherapy in oncology. In this context, glutathione (GSH) offers a non-enzymatic mechanism for drug release. This approach leverages the significant disparity between intracellular GSH concentrations (1–10 mM) and extracellular thiol levels (2 μM glutathione and 8 μM cysteine).129 Latorre et al. explored the potential of GNC-BSA as a nanocarrier for combined chemotherapy, primarily targeting cancer stem cells.126 They functionalized the GNC-BSA with DOX and SN-38 (camptothecin analogue) to inhibit topoisomerase II and I in target cells. While clinical trials involving the combination of free DOX and SN-38 have shown limited success, previous studies indicated that this combination exhibits strong synergy when injected as a polymer–drug conjugate.130 Thiol groups are introduced to the BSA with 2-iminothiolane. SN-38 is conjugated to the BSA using a redox-sensitive linker cleavable in reducing environments, such as those with high GSH or cysteine concentrations. Meanwhile, DOX was linked with a pH-sensitive linker susceptible to acidic environments, like those in endosomes and lysosomes. In vitro toxicity studies in MCF7, MDA-MB-231, and Panc-1 cell lines revealed that GNC-BSA loaded with DOX and SN-38 drugs displayed greater cytotoxicity than those loaded with only one of the drugs. These nanogold-albumin conjugates show good cellular uptake and bioimaging properties. Furthermore, therapy was achieved by significant DNA damage and antineoplastic activity against mammospheres even at very low concentrations of 0.08 μM, leading to an efficient reduction of the number of oncospheres and their size.126
3.2 Targeted delivery of therapeutic molecules
Successful delivery of therapeutics to disease sites poses a significant challenge in biomedicine. Two primary strategies for targeted therapeutics are: ‘passive’ targeting which relies on the EPR effect and active targeting which is achieved through tumor-avid functional moities. Despite the advantages, the significant limitation associated with passive targeting is suboptimal bio-distribution because of being trapped in the liver, spleen, or lung due to RES function. Additionally, heterogeneity and differences in vascular permeability lead to varied extents of the EPR effect even within the same tumour.6 Furthermore, passive targeting is ineffective where tissue accumulation is not contingent upon EPR, such as vascular targeting, or when delivering therapeutic agents, which requires active transcytosis across physiological barriers like the intestinal mucosa or the blood–brain barrier. This holds specific importance for biomacromolecule payloads involving the RNAi pathway (including siRNA and miRNA), wherein cytosolic delivery is essential for bioactivity (Table 5).131 In such situations, active targeting, achieved by conjugation of ligands or functional moieties including small molecules such as folic acid (FA), peptides, antibodies, or aptamers, that target overexpressed cell receptors or metabolic pathways, plays a vital role in directing nanoparticles specifically to malignant tissues. This targeted approach is especially beneficial in cancer therapy as it enhances the accumulation of the therapeutic agent in malignant tissues while minimizing off-target effects, thus increasing the efficacy and selectivity of the treatment.| Nanogold-albumin platform | Therapeutic molecule | Targeting moiety/targeted receptor | Tumor model/cell lines | Ref. |
|---|---|---|---|---|
| Gold nanorods supramolecularly coated with biomimetic folic acid-modified BSA | EGFP and RNase A proteins | Folic acid (FA) for targeting folate receptor (FR) | HT29, and A549 cells | 54 |
| Gold nanoclusters stabilized with BSA and conjugated with methionine (Met) | Indocyanine green derivative (MPA) and DOX | Methionine (Met) metabolism targeting through LAT1 and LAT2 amino acid transporters | L02, Bel 7402, A549 and MCF-7 cells; MDA-MB-231, A549 and S180 tumor-bearing mice | 55 |
| Gold nanoclusters stabilized with BSA and conjugated with 6-thioguanine (6-TG) | Thioguanine (6-TG) | Albumin metabolism targeting in KRAS mutant cancer cells | HCT116 and A549 cells | 56 |
| Gold nanoclusters stabilized with BSA and modified with PEG-folic acid (FA-PEG5k-COOH) | Hydrophilic cisplatin prodrug (MDDP) | Folic acid (FA) for targeting folate receptor (FR-α) | 4T1 cells; 4T1 tumor-bearing nude mouse model | 133 |
| Gold nanorods encapsulated in BSA shells | Bcl-2 specific SiRNA | Functionalization with anti-ErbB-2 via avidin-biotin chemistry for targeting ErbB-2 receptor | SK-BR-3, MCF-7, and HMEC cells | 135 |
| Gold nanospheres modified with BSA/HSA, anti-EGFR D-11 antibody and a Co(II) coordination compound [CoCl(H2O)(phendione)2][BF4] (TS265) | Co(II) coordination compound [CoCl(H2O) (phendione)2][BF4] (TS265) with proven anti-proliferative activity towards cancer cells | Anti-EGFR D-11 antibody | A549 and HCT116 cells; severe combined immunodeficient (NOD/SCID) male mice with HCT116-derived xenografts | 137 |
The nanogold-albumin platform presents adaptable surface chemistry stemming from the GNP/GNC core and the albumin coating, including hydrophobic and hydrophilic regions and a high density of charged amino acids. This composition offers various chemically active groups for surface modification, allowing attachment of targeting agents and facilitating drug loading for cancer treatment applications.19 Furthermore, the inherent ability of albumin to specifically bind to glycoprotein 60 (gp60) receptors and secreted protein acidic and rich in cysteine (SPARC) receptors on the cell surface endows nanogold-albumin conjugates with intrinsic targeting capabilities.132 The gp60 receptor, found on vascular endothelial cells, facilitates the transport of albumin across the endothelial cell layer, while SPARC is highly expressed in various tumor cells and minimally present in normal tissues.132 Spectroscopic studies of cisplatin-loaded albumin–GNP by Jaiswal et al. show that it could interact with glycans of the gp60 receptor and could effectively be used for in vivo or in vitro targeted drug delivery applications to cure cancer.90 The interaction of nanogold-albumin with gp60 or SPARC receptors mainly depends on the structural integrity of surface albumin. Zhou et al. present a GNC-BSA-based theranostic nanoplatform designed for folate receptor (FR) targeted fluorescence imaging and chemotherapy of metastatic breast cancer. The GNC-BSA nanoparticles are covalently functionalized with modified PEG–folic acid (FA-PEG5k-COOH) as a targeting ligand and the hydrophilic cisplatin prodrug (MDDP). Upon intracellular activation of the cisplatin prodrug, the nanoparticles effectively induce significant cellular apoptosis. In vivo distribution analysis reveals that the nanoparticles efficiently evade reticuloendothelial system (RES) capture and preferentially accumulate in orthotopically implanted breast tumors. Additionally, the nanoparticles demonstrate high efficacy in simultaneously suppressing tumor growth and preventing lung metastasis in the 4T1 breast cancer model.133
One of the earliest hallmarks of cancer progression is the increased demand for amino acids or albumin, which can be exploited for active targeting of dysregulated metabolic pathways in cancer.55 Chen et al. developed a GNC-BSA-based nanocomplex conjugated with methionine (Met) and indocyanine green (ICG) derivative (MPA) or DOX (GNC-BSA-Met-MPA and GNC-BSA-Met-DOX respectively) to target the L-type amino acid transporters LAT1 and LAT2, overexpressed in cancers, and responsible for trafficking methionine across the cell membrane.55 The in vitro and in vivo studies showed excellent methionine metabolism targeting capability (Fig. 4A). Cellular studies in normal and cancer cells show a higher accumulation of GNC-BSA-Met-MPA in MCF-7 and GNC-BSA-Met-DOX in Bel-7402 (liver cancer) cells, respectively, which is consistent with the highly expressed LAT1 and LAT2 receptors on the two cell lines.55,134 Furthermore, the in vivo studies also confirmed higher tumor-targeting and a greater distribution of GNC-BSA-Met-MPA in LAT1- and LAT2-positive tumor-bearing mouse models (MDA-MB-231) when compared with those of relatively low LAT1- and LAT2-expressing tumor models (A549).
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| Fig. 4 Nanogold-albumin in active targeting. (A) The fluorescence microscopy images of GNC-BSA- and GNC-BSA-Met-MPA-treated L02 normal human cells (a and b) and MCF-7 (c and d) tumor cells. This figure has been adapted/reproduced from Chen et al. with permission from Elsevier, Copyright © 2012;55 (B) intracellular uptake and therapeutic potential of GNC-BSA-TG in KRAS mutant HCT116 and A549 cells: (a) representative fluorescence microscopy images of HCT116 cells treated with GNC-BSA-TG over varying time intervals; (b) quantitative analysis of red fluorescence intensity showing time-dependent cellular uptake of GNC-BSA-TG in HCT116 and A549 cells; (c and d) cell viability of HCT116 and A549 cells following treatment with GNC-BSA-TG and free 6-TG. This figure has been adapted/reproduced from Jaiswal et al. with permission from Elsevier, Copyright © 2024;56 (C) selective internalization of anti-ErbB-2 antibodies modified SREB nanocomplexes through active targeting to specific cancer cells by receptor-mediated endocytosis. This figure has been adapted/reproduced from Choi et al. with permission from RSC, Copyright © 2015.135 | ||
Mutations in the Kirsten Rat Sarcoma Viral Oncogene Homolog (KRAS) exhibit increased macropinocytosis, enabling albumin uptake and making nanogold-albumin a promising tool to target aberrant nutrient metabolism in cancers.136 Jaiswal et al. recently reported a fluorescent GNC-BSA conjugate for enhanced loading of the hydrophobic purine analogue drug 6-thioguanine (GNC-BSA-TG).56 The release of 6-TG from the nanoconjugate, driven by cellular thiols such as glutathione (GSH), demonstrates its stimulus-responsive properties. Additionally, the nanoconjugate exhibits peroxidase-like enzyme activity, depleting cellular GSH levels and inducing oxidative stress, synergistically enhancing the chemotherapeutic efficacy of 6-thioguanine. Cytotoxicity analysis revealed a roughly 50% reduction in IC50 values for GNC-BSA-TG compared with free 6-TG in HCT116 and A549 cells with KRAS mutations, while KRAS wild-type HEK293T cells showed minimal toxicity under similar conditions. The enhanced albumin macropinocytosis in KRAS mutant cells likely facilitates a greater uptake of GNC-BSA-TG, leading to higher cancer cell death while sparing normal cells. The fluorescent nature of the 6-thioguanine-loaded GNC-BSA conjugate allows its uptake to be easily traced via fluorescence imaging (Fig. 4B). These findings underscore the potential of nanogold-albumin conjugates as targeted drug delivery carriers that exploit altered cancer metabolism.
Conjugation of targeting peptides/proteins or antibodies presents another paradigm for delivering cargo into cells. Research on peptide- or protein-coated GNPs predominantly explores the use of targeting peptide sequences or receptor-specific antibodies. Importantly, these surface modifications improve the particles’ ability to enter various organelles or selectively target cancer cells. Achilli et al. demonstrated that GNPs can be coated with a cross-linked multilayer of albumin to produce a highly compact protein shell, preserving the structure of the most external layer of the nanogold-albumin.138 Surface functionalization of these nanoconjugates with bombesin-related peptide shows enhanced in vitro uptake by PC-3 cells and a significant reduction of the corona effect. Tkachenko et al. developed an elegant nanogold-albumin conjugate by modifying gold nanospheres with BSA (GNP-BSA), which is pre-linked to different cellular targeting peptides.139,140 The presence of albumin contributes significantly to the stability of GNP-BSA-peptide conjugates in serum-containing media. This GNP-BSA enters the nucleus of HepG2 cells when functionalized with targeting peptides containing sequences for receptor-mediated endocytosis (RME) and nuclear localization signals (NLS). Studies show that conjugating these sequences separately, rather than combining them into a single sequence, enhances nuclear targeting efficiency. The intracellular distribution of NLS sequences is further explored using GNP-BSA nanoconjugates modified with various NLS peptides in HeLa, 3T3, and HepG2 cells. Findings reveal that the transport of nanoparticles into the cytoplasm and nucleus depends on the peptide sequence and the cell type.139 For instance, GNP-BSA modified with protein transduction domains (PTDs) from the HIV Tat protein are internalized into the cytoplasm but do not reach the nucleus in 3T3 and HepG2 cells. The uptake of these nanoparticles is temperature-dependent, suggesting the involvement of an endosomal pathway. In contrast, GNP-BSA functionalized with adenovirus-derived NLS and integrin-binding domains are internalized via an energy-dependent mechanism and successfully localized to the nucleus.140 These observations suggest that combining specific targeting peptides on a single nanogold-albumin carrier offers the most efficient strategy for nuclear targeting. Furthermore, as BSA does not add greatly to the size of the GNPs, it may conveniently be used in constructing intracellular organelle targeting vectors, as only particles with diameters below 30 nm can enter cell nuclei. A significant study by Choi et al. reports the efficient ErbB-2 receptor-targeted delivery of Bcl-2 specific siRNA using a nanogold-albumin conjugate.135 They developed a gold nanorod-BSA-based complex containing Bcl-2 specific siRNA and modified it with anti-ErbB-2 antibodies (SREB nanocomplexes). The SREB nanocomplexes show a high loading of 2 × 105 siRNA molecules and eight nanorods per BSA complex. The anti-ErbB-2 antibodies on the surfaces of SREB nanocomplexes enabled active targeting via selective receptor-mediated endocytic uptake by ErbB-2 receptor-overexpressing SK-BR-3 cells. The intracellular decomposition of the nanocomplexes by proteolytic enzymes led to an efficient synergistic anticancer effect, combining RNA interference-mediated silencing of Bcl-2 with the photothermal effect mediated by GNPs (Fig. 4C). These SREB nanocomplexes demonstrated potent in vitro efficacy, resulting in up to approximately 80% cancer cell death, with therapeutic effects sustained for around 72 hours, highlighting the possibility of SREB nanocomplexes as a robust and effective theranostic tool in vivo. Fernandes et al. developed a multifunctional nanogold-albumin conjugate – TargetNanoTS265 – for targeted cancer therapy.137 This system incorporates a monoclonal antibody against the epidermal growth factor receptor (EGFR) (anti-EGFR D-11) for active targeting and an anticancer cobalt(II) coordination compound, [CoCl(H2O)(phendione)2][BF4] (phendione = 1,10-phenanthroline-5,6-dione) (TS265). The formulation known as TargetNanoTS265 consists of ∼14 nm GNPs functionalized with bifunctional polyethylene glycol (PEG) (SH-EG (8) –(CH2)2-COOH) to enhance stability and stealth properties in vivo, BSA/HSA to facilitate TS265 loading, and anti-EGFR D-11 antibody to target cancer cells exhibiting high EGFR expression. The efficacy of TargetNanoTS265 and its non-targeted counterpart (NanoTS265) tested in vitro on cancer cell lines and in vivo using mouse xenograft models demonstrates efficient and selective delivery of the cytotoxic payload, significantly enhancing tumor cell death compared with the free compound. In particular, treatment of HCT116-derived xenograft tumors with TargetNanoTS265 achieved a remarkable 93% tumor reduction. This formulation highlights the potential of nanogold-albumin-based systems for nanovectorizing chemotherapeutic agents. Its adaptable design, employing BSA or HSA conjugates for drug delivery, offers a versatile platform for controlled and selective targeting of diverse therapeutic agents to cancer cells.
3.3 Delivery of therapeutic proteins
The intracellular delivery of therapeutic proteins into cells presents a promising strategy for addressing “undruggable” diseases related to protein deficiencies and cancer.141 Protein therapeutics are more effective at modulating cellular functions and treating various diseases, due to their high functional specificity and minimal side effects, than genetic therapies or small molecules.3 However, the delivery of such protein biologics to the target sites has been the bottleneck of current approaches due to the high clearance, low plasma stability, and limited cellular uptake due to their relatively large sizes, hydrophilicity, and rapid degradation in the endo-/lysosomal compartments of cells.142 The stability of the protein cargo against enzymatic digestion poses another major challenge.Potentially, non-covalent conjugation of proteins of interest to the nanogold-albumin platform can address these limitations by preserving the structure and activity of the protein cargo. The nanogold-albumin conjugates provide a versatile platform for protein delivery, leveraging albumin's inherent capacity to form non-covalent interactions such as hydrogen bonding, van der Waals forces, and hydrophobic interactions. These properties of albumin ensure efficient loading and stabilization of proteins, making nanogold-albumin conjugates a promising tool for therapeutic applications. Khandelia et al. developed an innovative, self-assembled-GNP-lysozyme-albumin-based nanocarrier that can efficiently encapsulate both doxorubicin (DOX) and pyrene (Pyr) as model hydrophilic and hydrophobic drug molecules, respectively, with high loading capacity.143 Negatively charged citrate-capped GNPs and positively charged lysozyme spontaneously assembled through complementary electrostatic interactions, followed by an albumin coating to enhance stability and biocompatibility. In vitro experiments show that the nanocarriers are successfully internalized by cancer cells, where they simultaneously release their payloads, resulting in cell death that is more effective than using the drug molecules alone. This innovative design exhibits no detectable cytotoxicity, underscoring its potential as a safe platform for protein-based therapeutic delivery. The incorporation of albumin leads to preferential intratumor accumulation of the nanocarrier.143
Modified nanogold-albumin-based carriers for the intracellular delivery of enhanced green fluorescent protein (GNP-BSAFA-EGFP) and enzyme (GNP-BSAFA-RNase A) have been synthesized by metal-directed assembly of EGFP and RNase A with a biomimetic folic acid-modified BSA corona, which can specifically target FR-overexpressing cancers for the delivery of therapeutics.54 These nanogold-albumin-based EGFP and RNase A delivery nanocarriers exhibited high protein loading capacities of ∼42 and ∼54%, respectively, and high colloidal stability increased colloidal stability and rapid protein release in the presence of biological thiols. Furthermore, folate receptor-targeting facilitates receptor-mediated internalization and successful cytosolic delivery of EGFP and RNase A in HT29 cells (Fig. 5A and B). RNase A delivery in multicellular 3D spheroids of HT29 cells exhibits a radical reduction in the cellular RNA, signifying RNA degradation and resulting in subsequent cell death (Fig. 5B). The study represents the first proof of concept on folic acid-modified nanogold-albumin as a targeting and antifouling platform for enhanced intracellular EGFP and RNase A delivery. Such nanoconjugates could be adapted to efficiently deliver therapeutic proteins, a forward-looking perspective for the targeted delivery of therapeutic proteins and enzymes, with enormous potential as a safe and efficacious platform for application in protein-based cancer therapeutics.
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| Fig. 5 Nanogold-albumin-based protein therapeutics. Time-dependent intracellular protein delivery by GNP-BSAFA-EGFP in HT29 (FR+) cells. (A) Fluorescence microscopy images of HT29 cells treated with GNP-BSAFA-EGFP for t = 0, 0.5, 1, 2, 4, and 24 h; (B) intracellular RNA degradation efficacy of GNP-BSAFA-RNaseA in 3D spheroids of HT29 cells for untreated (control), GNP-BSAFA-EGFP, and GNP-BSAFA-RNaseA-treated HT29 spheroids stained with AO for differential staining of total cellular DNA and RNA. This figure has been adapted/reproduced from Jaiswal et al. with permission from Elsevier, Copyright © 2022;54 (C) schematic illustration of HSA-copper complex-loaded gold nanocages coated with bacterial membranes (GNP-HSA-Cu) targeting the cuproptosis–lactate regulation pathway to induce cuproptosis and enhance anti-tumor immunity. This figure has been adapted/reproduced from Zafar et al. with permission from Elsevier, Copyright © 2024.144 | ||
In recent years, cancer immunotherapy has emerged as a promising approach for cancer therapy with fewer side effects by directly engaging the immune system, particularly in cases where traditional therapies are ineffective. They function by delivering antigenic information to dendritic cells (DCs), which subsequently stimulate an immune response. However, cancer immunotherapy faces significant challenges, including limited immune cell proliferation and the highly immunosuppressive nature of the tumor microenvironment, which hinder its overall effectiveness. Nanogold-albumin conjugates can be a valuable tool in addressing these challenges by enhancing the delivery and stability of antigens, facilitating the activation of dendritic cells, and modulating the tumor microenvironment to overcome immune suppression. A recent study by Zafar et al. study proposes a novel nanogold-albumin conjugate composed of HSA-copper complex-loaded gold nanocages coated with bacterial membranes (GNP-HSA-Cu) targeting the cuproptosis–lactate regulation pathway to induce cuproptosis and enhance anti-tumor immunity.144 The near-infrared (NIR) active gold nanocages release the HSA-copper complex, enabling its reaction with intratumoral GSH through a disulfide exchange reaction, thereby releasing Cu2+ ions and inducing cuproptosis. Induction of cuproptosis subsequently initiates immunogenic cell death (ICD) by releasing damage-associated molecular patterns (DAMPs), which stimulate robust anti-tumor immunity by activating cytotoxic CD8+ T cells and helper CD4+ T cells. Concurrently, NIR irradiation of the gold nanocages generates excessive reactive oxygen species (ROS), significantly inhibiting glycolysis and reducing lactate and ATP levels. This cascade of reduced lactate production, ATP depletion, and GSH consumption sensitizes tumor cells to cuproptosis. Moreover, the lower lactate levels effectively suppress immunosuppressive T regulatory cells (Tregs), further enhancing anti-tumor immunity. This innovative nanogold-albumin conjugate effectively inhibits breast cancer metastasis to the lungs, amplifying the therapeutic impact of the GNP-HSA-Cu + NIR treatment. This study introduces a novel platform for cuproptosis–lactate regulation, offering a highly innovative and effective strategy to develop nanogold-albumin conjugates for tumor immunotherapy.
Among the various immunotherapy strategies, therapeutic cancer vaccines aim to activate the adaptive immune system to target and eliminate cancer cells. These vaccines represent a significant advancement in cancer treatment by enhancing the immune system's therapeutic potential. However, the efficacy of many cancer vaccines remains limited due to challenges such as insufficient stability, inadequate immune activation, and the lack of effective adjuvants. Recent research has demonstrated that photothermal therapy (PTT) holds significant promise as a potent adjuvant for immunotherapy, as it can stimulate the release of tumor-associated antigens, thereby recruiting the immune cells necessary to initiate a robust immune response. In this context, gold nanoparticles (GNPs) are exemplary photosensitizers for PTT, and albumin, which contains numerous disulfide bonds, is sensitive to elevated levels of glutathione (GSH) in tumor microenvironments, making nanogold-albumin a suitable carrier for tumor-targeted therapies. Zhang et al. recently reported a nanogold-albumin conjugate composed of self-generated GNPs templated by human serum albumin (HSA), encapsulating the hydrophilic human melanoma antigen gp10025–33 (hgp100) peptide. This peptide is known for its ability to stimulate a specific immune response due to its high expression in melanoma, one of the most aggressive skin cancers.145 The GNP-HSA conjugate effectively shields the peptide in physiological environments, enabling controlled drug release triggered by near-infrared (NIR) irradiation and elevated GSH levels at tumor sites. The PTT mediated by GNP-HSA ablates tumors and promotes the release of endogenous tumor antigens, which, together with hgp100, induce immune activation and dendritic cell maturation. In vivo results demonstrate that dendritic cell maturation and specific hgp100 cross-presentation are significantly enhanced in the lymph nodes, spleen, and tumor microenvironment. This dual action of local PTT and immune amplification establishes GNP-HSA as a highly efficient cancer vaccine platform with potential applications across various diseases.
3.4 Bio-imaging
Bio-imaging plays a critical role in cancer diagnosis and treatment by providing precise, detailed visualization of tumors within the body. Advanced imaging techniques, including fluorescence imaging, magnetic resonance imaging (MRI), positron emission tomography (PET), and optical coherence tomography (OCT), offer high-resolution, real-time insights into tumor morphology, vascularization, and metabolic activity. Among these, fluorescence imaging is particularly notable for its non-invasive nature and exceptional spatial resolution, making it highly effective for early-stage tumor detection and accurate diagnosis. Additionally, it enables real-time monitoring of tumor progression and treatment response, thereby enhancing the precision and efficacy of cancer therapies. Notably, nanogold-albumin, particularly ultra-small GNC-BSA, exhibits intriguing fluorescence properties derived from the Au25 core, further expanding its potential in advanced bio-imaging applications (Table 6).73 GNC-BSA demonstrates favorable physicochemical attributes and biocompatibility due to the presence of the serum albumin in GNC-BSA, enabling it to overcome inherent issues associated with conventional imaging agents, such as organic dyes, which are prone to photobleaching or phototoxicity, and QDs, which entails harsh synthetic conditions and high cytotoxicity, making them a promising class bio-imaging agents.146,147| Nanogold-albumin platform | Cell line/model used | Imaging mode(s) | Remarks | Ref. |
|---|---|---|---|---|
| GNC-BSA | MCF-7 and HeLa cells; athymic nude mice | Near-infrared fluorescence (NIRF) | Fast synthesis of GNC-BSA at 80 °C for 10 min compared with that at 37 °C for 12 h | 146 |
| GNC-BSA | MDA-MB-45 and HeLa cells | Fluorescence microscopy | High accumulation in the tumor areas due to the enhanced permeability and retention (EPR) effects | 150 |
| GNC-BSA | Mice | 2D and 3D ++ tomography (CT) | Can be clear visualization of the renal collecting system and ureters | 151 |
| GNC-BSA-p | HeLa cells | Confocal fluorescence microscopy | A polymer-like shielding layer significantly improves the stability of AuNCs against ROS and protease degradation; carbodiimide-activated coupling | 152 |
| GNC-BSA-SiNPs | A549 cells | Confocal fluorescence microscopy | Improved photostable and chemical stable properties | 153 |
| GNC-BSA-Her | ErbB-2+ breast tumor | Confocal fluorescence microscopy | Specific targeting and nuclear localization in ErbB2-over-expressing breast cancer cells, for simultaneous imaging and cancer therapy | 154 |
| GNC-BSA-DOX | HeLa cells | Two-photon excitation | NIR excitation and emission (650–900 nm), ideal potential platform for imaging-guided drug delivery | 81 |
| GNC-BSA-RGD | U87-MG cells | One-photon/two-photon fluorescence microscopy | Polymeric nano-capsules loaded with GNCs specifically target U87-MG cancer cells overexpressing integrin anb3 | 155 |
| GNC-BSA-NHA | BxPC-3 and HT-1080 tumor-bearing mice | Computed tomography (CT) | Imaging of hypoxia in the tumor microenvironment | 156 |
| GNC-BSA-iodine | Thyroid tumor-bearing mice | Fluorescence microscopy/CT | Produce sensitive and accurate diagnosis of minimal thyroid cancer, as small as 2 mm3 | 157 |
| GNC-BSA-Gd2O3 | U87-MG tumor-bearing mice | Fluorescence/MRI | Modification with arginine–glycine–aspartic acid peptide c(RGDyK) (RGD) enabled the nanoprobe for targeted tumor imaging in vivo | 158 |
| GNC-BSA-Gd | MCF-7 tumor-bearing mice | NIRF/CT/MRI | Ultrasmall hybrid NCs penetrate into the solid tumor for cancer targeted imaging and diagnosis in vivo | 159 |
| GNC-BSA-Gds-FA | KB tumor-bearing mice | Optical/MRI/CT | Very clear structural and anatomical information can be obtained; show good biocompatibility, quick renal clearance, and do not induce normal tissue toxicity in vivo | 160 |
Zhang et al. synthesized vibrant red fluorescence-emitting GNC-BSA with a quantum yield of ∼9.4% and used it for rapid imaging of tumor cells.146 The GNC-BSA did not display cell cytotoxicity in the 0.1–10 mg mL−1 concentration range towards MCF-7, HeLa, L02, U87, and A549 cells (Fig. 6A and B). Moreover, prepared GNC-BSA, when used as an in vitro and in vivo cancer imaging modality, showed excellent tumor-targeted imaging in a relatively short period (Fig. 6C–F). GNC-BSA may also be modified with specific molecules to impart cell receptor targeting functionality. Retnakumari et al. functionalized GNC-BSA with folic acid (FA) to target overexpressed folate receptors (FRs).105 They observed a significantly high accumulation of the fluorescent GNC-BSA in FR-overexpressing KB (oral squamous cell carcinoma) compared with FR-negative MCF-7 (breast adenocarcinoma) cells. A similar observation was reported by Zhang et al. where GNC-BSA coated with FA or hyaluronic acid (HA) exhibited strong red fluorescence under a UV lamp (λex = 365 nm) with a high fluorescence QY of 14.8 ± 2.2%. Modifying these nanogold-albumin conjugates with FA or HA (GNC-BSA-FA/HA) as a recognition component for active tumor-targeted imaging exhibits strong red fluorescence in the FR overexpressing HEp-2 (hepatocellular carcinoma) cells. In contrast, very weak fluorescence is seen for FR-negative A549 cells. HA functionalization results in the significant accumulation of GNC-BSA-HA in CD44-overexpressing A549 cells. Fluorescence studies in vivo in tumor-bearing nude mice show selective accumulation of the GNC-BSA-FA/HA in either HeLa or Hep-2 tumors, respectively.148 These findings establish that GNC-BSA could be used for active targeting and sensitive imaging of cell-associated receptors for rapid tumor diagnosis in future clinical applications.
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| Fig. 6 Representative in vitro and in vivo bio-imaging applications of GNC-BSA bioconjugates. Laser confocal fluorescence micrographs of (A) HeLa cells and (B) L02 cells treated with 1 mg mL−1 GNC-BSA for 4 h; fluorescence imaging of xenograft tumour nude mice after intratumoral injection of 10 mg mL−1 GNC-BSA for varying times: (C) 0 min, (D) 30 min, (E) 60 min, and (F) 120 min. This figure has been adapted/reproduced from Zhang et al. with permission from RSC, Copyright © 2015;146 (G) total internal reflection fluorescence (TIRF) image; (H) super-resolution radial fluctuation (SRRF) image of GNC-BSA-treated HeLa cells for labeling lysosomes and (I) The localization average pattern obtained from SRRF microscopy for lysosomes present. This figure has been adapted/reproduced from Yadav et al. with permission from Elsevier, Copyright © 2020.149 | ||
Nanogold-albumin conjugates (GNC-BSA/HSA) demonstrate significant potential as probes for advanced imaging techniques, including single-molecule super-resolution microscopy. These probes enable fluorescence visualization of complex cellular dynamics, such as those of the cytoskeleton, with nanometer-scale resolution in vitro.161 Recently, Yadav et al. employed GNC-BSA as a highly effective nanoprobe for lysosomal imaging in HeLa cells.149 The super-resolution radial fluctuation images revealed lysosomal structures with finer detail and reduced background noise compared with conventional fluorescence imaging (Fig. 6G and H). The average localization pattern of lysosomes is obtained with a maximum resolution of approximately 59 nm, closely resembling the original diameter of the smallest lysosome at around 50 nm in HeLa cells (Fig. 6I). These findings highlight the potential of nanogold-albumin conjugates as specific markers for super-resolution microscopy, offering a promising tool for high-precision imaging of various cellular organelles and advancing the field of cellular imaging and diagnostics.
3.5 Bio-sensing
The precise detection and quantification of disease-specific biomarkers are critical for early cancer diagnosis, enabling effective clinical intervention, timely treatment planning, and accurate prognosis assessment. In cancer, metastasis to distant tissues is a key driver of mortality, accounting for over 90% of cancer-related deaths.162 It is a complex process in which tumor cells detach from the primary site, enter the bloodstream, and form secondary tumors in distant organs, significantly contributing to cancer-related morbidity and mortality.163,164 The blood of cancer patients contains valuable biomarkers, including circulating tumor DNA (ctDNA), tumor-derived extracellular vesicles (tEVs), and circulating tumor cells (CTCs), which facilitate early detection and disease monitoring.165–167 In this context, nanogold-albumin conjugates, due to their unique optical, electronic, and physicochemical properties, serve as potential platforms for developing ultrasensitive nanoassays.167 Sensitive detection of cancer-related biomarkers is possible through a range of nanogold-albumin facilitated analytical approaches, including surface-enhanced Raman scattering (SERS),168 fluorescence imaging,166,169–171 electrochemical methods, etc., for enhancing diagnostic accuracy, prognostic evaluation, and overall survival outcomes for cancer patients.Circulating tumor cells (CTCs) have garnered increasing attention in medical biology and clinical practice, particularly for their applications in cancer diagnosis, prognosis, and treatment monitoring. Detecting CTCs within the vast population of healthy blood cells remains a significant challenge due to their scarcity, necessitating the development of detection methods with exceptional sensitivity and specificity. CTCs initiate metastases and carry genetic information reflective of the primary tumor.172 High levels of CTCs in the bloodstream are often associated with a poor prognosis, indicating their potential as biomarkers for tracking cancer progression and predicting patient outcomes.162,163 Regular monitoring of CTC concentrations can aid in devising personalized treatment approaches by providing insights into real-time therapeutic responses. Wu et al. developed three kinds of surface-enhanced Raman scattering (SERS)-based nanogold-albumin conjugates consisting of gold nanospheres, nanorods, and nanostars conjugated with 4-MBA (4-mercaptobenzoic acid, a Raman reporter) and stabilized with FA-modified BSA.168 These nanogold-albumin conjugates are employed to detect cancer cells in the peripheral blood of rabbits without the need for an enrichment process. Stabilization with reductive BSA minimizes nonspecific binding and uptake by healthy blood cells, ensuring excellent specificity. Additionally, conjugation with FA as a targeting ligand enhances sensitivity by facilitating the identification of CTCs. The specificity and sensitivity of the three SERS-active nanoparticles are assessed using HepG2 and HeLa cells, as HepG2 cells lack folate receptor alpha (FRα), while HeLa cells are FRα-positive. White blood cells (WBCs) served as a control due to their low FRα expression.173 The study established that all three nanogold-albumin conjugates could be utilized for CTC detection in the blood with high specificity without the need for enrichment. The nanostar-based conjugate is the best due to its super-sensitivity with a limit of detection (LOD) of 1 cell per mL, whereas the LOD for both nanospheres and nanorods is 3 cells per mL. These findings highlight the potential of SERS-based nanogold-albumin conjugates as highly sensitive and specific tools for CTC detection, offering advancements in cancer diagnostics and monitoring.
The simultaneous enrichment and detection of circulating tumor cells (CTCs) provide invaluable insights for comprehensive cancer diagnosis, accurate prognosis, improved patient outcomes, and the development of personalized medicine.174–176 Li et al. recently reported the development of an antifouling surface composed of silicon nanowires (SW) as a substrate, coated with amyloid-like transformed BSA inlaid with GNPs, and modified with sgc8 aptamer as a recognition group that can exclusively recognize overexpressed protein tyrosine kinase 7 (PTK7) in tumor cells.166 The amyloid-transformed BSA coating embedded with gold nanoparticles provided a uniform antifouling surface, significantly reducing fouling by blood components, including human serum albumin (HSA), platelet-rich plasma (PRP), and white blood cells (WBC) by 88.5%, 88.0%, and 83.7%, respectively. The amyloid-transformed BSA, integrated with gold nanoparticles, also offered abundant sites for aptamer crosslinking, enhancing its functional versatility. The optimal conditions for target cell capture were assessed using MCF-7 cells (high PTK7 expression) and PC-3 cells (low PTK7 expression) on nanogold-albumin-modified SW surfaces over incubation times ranging from 10 to 40 minutes. At 30 minutes, fluorescence microscopic surface analysis shows an efficient capture rate of 85.2% for MCF-7 cells, with only 1.9% retention of PC-3 cells, demonstrating its ability to selectively isolate PTK7-expressing cells while minimizing nonspecific adhesion. Further studies with untreated blood samples show that the surfaces can capture approximately six cells per mL of fresh whole blood spiked with 10 cells. The nanogold-albumin surfaces additionally facilitated selective cell capture, with gentle and non-destructive release, and preserved the high viability of captured cells following incubation with GSH, attributed to their excellent biocompatibility.
GNC-BSA-stabilized fluorescent polystyrene (PS) nanoparticles modified with EpCAM aptamer (GNC-BSA-PS-Apt) have also been used to efficiently detect breast cancer cells based on a dual-fluorescence signal approach169 (Fig. 7). The GNC-BSA adsorbed via electrostatic interaction imparted excellent colloidal stability and photostability to PS nanoparticles and abundant active linking sites for EpCAM aptamers. Quantitative analysis revealed approximately 198 EpCAM aptamers present per GNC-BSA-PS-Apt nanoparticle, which gave a strong green fluorescent signal from the GNC-BSA-PS-Apt that was observed on MCF-7 cells (Fig. 7A). In contrast, only a weak signal is detected on HEK-293T and MCF-10A cells, indicating that the interaction of GNC-BSA-PS-Apt with MCF-7 cells is primarily mediated by EpCAM aptamer targeting. The dual-fluorescence (green and red) signals from the fluorescent PS nanoparticles and GNC-BSA ensured high specificity for cell detection, minimizing the risk of false positives (Fig. 7B). The exceptional targeting capability of the nanogold-albumin platform was further demonstrated in xenograft tumor models of MCF-7 and HeLa cells in BALB/c nude mice, showing selective binding to EpCAM-positive MCF-7 breast tumor tissues with no interaction observed with EpCAM-negative HeLa tissues169 (Fig. 7C). These studies provide a comprehensive insight into the innovative application of nanogold-albumin conjugates in developing liquid biopsy-based biosensors to enrich biomarkers from complex biological fluids efficiently. It extends beyond the traditional understanding of these conjugates as mere delivery vehicles, highlighting their potential as multifunctional platforms in biomedical diagnostics.
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| Fig. 7 Schematic illustration of the workflow for detecting EpCAM-positive breast cancer cells by GNC-BSA-PS-Apt. (A) Fabrication of GNC-BSA-PS-Apt. (B) Detection of breast cancer cells based on dual-color fluorescence signals. (C) Detection of xenografted breast tumor tissue. This figure has been adapted/reproduced from Wu et al. with permission from Elsevier, Copyright © 2022.169 | ||
4 Summary and outlook
Nanogold-albumin conjugates are emerging as innovative tools in nanomedicine, offering significant potential for cancer therapy and diagnostics. These versatile systems are especially well-suited for theranostic applications, seamlessly integrating therapeutic, diagnostic, and bio-sensing functionalities. They are developed through two primary strategies: (1) supramolecular coating of GNPs with albumin via electrostatic or hydrophobic interactions(GNP-BSA/HSA) and (2) albumin-templated in situ synthesis of ultra-small gold nanoclusters (GNC-BSA/HSA). Both systems serve as flexible platforms for delivering diverse therapeutics, from small molecules to larger biomolecules, while offering promising applications in cancer monitoring and management. The synergy between gold and albumin endows these constructs with several key advantages, including low inherent toxicity, a high surface area, adjustable surface chemistry, distinctive optical properties and an extended shelf-life. These attributes enhance their suitability for clinical applications. Furthermore, albumin's natural affinity for receptors such as gp60 and SPARC—commonly overexpressed in tumor tissues—facilitates the selective accumulation of nanogold-albumin constructs in cancer cells, improving intratumoral drug delivery.Despite their potential, several challenges hinder the clinical translation of nanogold-albumin conjugates. Although nanogold platforms such as AuroLase and CYT-6091 have entered clinical trials, widespread adoption remains limited due to issues related to reproducibility, batch consistency, long-term stability, and immune responses. Unlike conventional chemotherapy and antibody–drug conjugates, which benefit from well-established manufacturing pipelines, nanogold-albumin conjugates require precise control over surface characteristics such as charge, hydrophobicity, and functional group composition to optimize interactions with the tumor microenvironment. The incorporation of targeting ligands can further enhance the specificity; however, such modifications necessitate careful calibration to maintain the structural and functional integrity of the constructs. A comprehensive understanding of cellular uptake mechanisms and nanoparticle interactions within the tumor microenvironment is crucial to ensure the scalability and clinical viability of these platforms.
Beyond formulation challenges, the translation of nanogold-albumin conjugates from laboratory research to clinical application is impeded by regulatory, economic, and scalability constraints. Maintaining precise control over nanoparticle size, shape, and albumin interactions at a commercial scale requires advanced and costly fabrication techniques. Additionally, regulatory approval for nanoparticle-based therapeutics is particularly stringent, requiring extensive preclinical and clinical validation to ensure long-term safety, biocompatibility, and efficacy.
Addressing these challenges through continued research, optimization of fabrication processes, and advancements in regulatory frameworks will be essential for the successful clinical translation of nanogold-albumin conjugates. The development of cost-effective and scalable synthesis techniques, coupled with a deeper understanding of nanoparticle interactions in biological systems, could facilitate their transition from experimental models to widely available therapeutic options. With further innovations, nanogold-albumin conjugates can potentially drive a paradigm shift in modern cancer nanomedicine, offering more effective, targeted, and less toxic alternatives to existing treatment modalities. Their multifunctional nature and ability to integrate therapy with real-time diagnostics underscore their potential to significantly enhance patient outcomes and redefine cancer management in the future.
Data availability
No primary research results, software or code have been included and no new data were generated or analysed as part of this review.Conflicts of interest
There are no conflicts of interest to declare.Acknowledgements
The authors express their gratitude to the Director of CSIR-CMERI, Durgapur, and the Director of NIT Durgapur for their support and encouragement. They also extend their thanks to the Department of Biotechnology, India, for financial support (BT/PR49579/MED/32/849/2023, GAP-245112).References
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