NIR fluorescence-guided tumor surgery: new strategies for the use of indocyanine green

Introduction

Fluorescence-guided surgery

Surgery is the frontline treatment for a large number of cancers.^1,2 Between 63% and 98% of patients with lung, breast, bladder, or colorectal cancer will undergo a surgical resection.³ The objective of these excisional curative surgeries is the complete removal of the primary tumor with sufficient safety margins. Obtaining negative margins of excision is essential to improve the chances of a full recovery. Indeed, positive margins can be the cause of local recurrence for 75% of patients⁴ and the development of distant metastases or a second histologically linked cancer.^5–7

Intraoperative evaluation of these margins consists of visual inspection and palpation and is followed by extemporaneous histological evaluation, which sometimes takes time and can be inaccurate.⁵ It is not uncommon to find discrepancies between the selective intraoperative evaluation and the more complete evaluation of the operative specimen. Despite the progress made in the various areas of preoperative imaging (computerized tomography, magnetic resonance imaging), the positive surgical margin rate has not significantly decreased in recent years.⁸

However, progress appears possible, for example by using fluorescence-guided surgery (FGS) techniques with fluorescent probes or nanoparticles to detect cancerous tissue in real time.^9,10 These techniques are noninvasive and have high resolution.¹¹ The concept of FGS is well known, as it has been used in neurosurgery since 1948.¹² Brain tumors remain a major indication for FGS; these tumors are infiltrative and safety margins can never be achieved.^13,14

In connection with the development and emergence of new technologies, FGS is again the subject of many studies. Most techniques developed for FGS consist of the use of a fluorescence camera with a near-infrared (NIR)-sensitive detector. The advantages of NIR light (700–900 nm) include its high tissue penetration (up to several centimeters deep) and the low autofluorescence of biological tissues, thus providing sufficient contrast.¹⁵ In addition, NIR wavelengths are not visible to the human eye and therefore do not change the surgeon’s vision of the surgical field.¹⁶ These advantages have resulted in the development of different imaging systems adapted for guided surgery.^17–19

Indocyanine green

The concomitant use of fluorescence and indocyanine green (ICG) has proved effective in the identification and characterization of tumors and metastatic lymph nodes.^16,20–23 It is authorized by the Food and Drug Administration (FDA) and the European Medicines Agency and is therefore the subject of a large number of studies. Nevertheless, it is important to note that ICG is approved by the FDA for determining cardiac output, hepatic function, liver blood flow, and for ophthalmic angiography, and ICG-based FGS is currently only used in clinical trials. It also has a good signal-to-noise ratio due to low autofluorescence and high tissue penetration at a wavelength of 820 nm.²⁴

Before hepatologists, cardiologists, nephrologists, and ophthalmologists used it as a diagnostic tool, ICG was used as a photographic dye from the late 1940s. It was subsequently rediscovered as a fluorophore that absorbed and emitted light in the NIR.²⁵ ICG is one of the most common fluorophores used in NIR fluorescence-guided techniques. It is an anionic, amphiphilic, water-soluble fluorophore with a molecular weight of 776 Da.^26,27 It binds rapidly to plasma proteins after being injected intravenously. Its excitation and emission peaks are respectively 780 and 820 nm.

However, ICG also has some disadvantages, including limited photostability, a moderate fluorescence quantum yield, a high plasma protein binding rate, and undesired aggregation in aqueous solution.¹¹ The short persistence of fluorescence of the free dye in vivo is attributed to fluorescence quenching of free ICG in physiological environments with rapid aggregation and clearance from the body.²⁸ Moreover, ICG is not a specific marker for tumor cells.²⁹ An opportunity exists to exploit the features of ICG while offsetting these disadvantages, by designing high-performance NIR nanocomplexes formulated with ICG (with high selectivity for tumors, high tumor-to-background ratios, and minimal toxicity).^19,30–35 The vectorization of ICG with nanoparticles results in its protection and thus increases its circulation time. The biodistribution and the in vivo availability is thus more interesting. The binding of different ligands, either on ICG nanoparticles or directly on ICG, results in tumor tissue-specific labeling.

In this review article, we have focused on recent developments in ICG complexation strategies to improve NIR FGS.

Indocyanine green nanoparticles

Nanoparticles

The purpose of using nanoparticles or nanovectors is to increase the efficacy, specificity, and biosafety of therapeutic or imaging agents. A nanoparticle is defined as an object sized between 5 and 200 nm,³⁶ which is around the size of a protein or a virus.

There are three major generations of nanoparticles. The first generation corresponds to stable colloids in aqueous media encapsulating active agents; the main aim is to slow down their elimination (especially via the renal route) and prolong their effects. Nevertheless, this class of nanoparticles does not escape the immune system.

Second-generation nanoparticles are termed “stealthy”, as they have undergone surface modifications allowing them to escape the immune system.³⁷ This escape leads to an increase in the nanoparticle plasma half-life. The most commonly used surface treatment is polyethylene glycol (PEG) because it is biocompatible, releasable in aqueous media, nontoxic, and weakly immunogenic. This type of nanoparticle allows passive tumor targeting.

Third-generation nanoparticles are stealthy and targeted. Their surface is functionalized with biological ligands recognizing specific targets. The ligands can be extremely varied in nature and allow active tumor targeting.

ICG nanoparticles

The use of ICG for fluorescence-guided surgical techniques presents a number of constraints; ICG has a low fluorescence quantum yield in solution due to self-quenching³⁸ but also a rapid elimination by the liver after intravenous administration.³⁹ To overcome this, it is possible to incorporate ICG into nanoparticles and thus improve stability and circulation time and facilitate the accumulation of ICG in tumors.⁴⁰ ICG can be loaded, doped, or conjugated to different types of nanoparticles. These nanoparticles can themselves be bound to ligands and thus allow tumor-specific targeting.

In recent years, there has been a steady increase in the development of nanoparticles for the treatment and imaging of cancers. There are currently 225 clinical trials involving the use of nanoparticles in oncology and two using ICG nanoparticles. However, there is still a limited number of clinically approved nanoparticles.

ICG nanoparticles for passive tumor targeting

Enhanced permeability and retention effect

For tumor imaging, the passive targeting of tumor tissue by nanoparticles relies mainly on the EPR (enhanced permeability and retention) effect. The EPR effect results from poor vascular formation in solid tumors with openings between endothelial cells, resulting in preferential retention of macromolecules and nanoparticles.^41–43 When tumors reach a sufficient size, oxygen and nutrients cannot diffuse fast enough inside the tumor.⁴⁴ When this happens, growth factors are released that trigger angiogenesis in the surrounding tissue, forming new blood vessels.² However, the vascularization formed is not well structured, which leads to increased extravasation of all molecules that intercalate between discontinuities in the endothelial layer, ranging from 200 to 2000 nm. After extravasation, larger particles are retained preferentially in the tumor because of the deficiency of the lymphatic system.² This is advantageous, as many first-generation nanoparticles are not targeted, and this phenomenon is therefore used to allow the release of therapeutic compounds passively within solid tumors.

Passive tumor targeting

Passive targeting requires the use of stable, nonaggregated, stealthy compounds that have a sufficiently long circulation time to result in accumulation in tumors. It also requires that the compounds are of a size that does not exceed the pore size of permeabilized vessels (between 380 and 780 nm)^45,46 and which is not too small. The EPR effect is negligible for small molecules that can be redistributed into the bloodstream by diffusion and/or convection and are eliminated preferentially by the renal route.⁴⁷

However, because of the variability in the structure and extent of the vascular system, tumor stroma, and lymphatic drainage, the EPR effect varies depending on the type and location of the tumor, making it a useful but not universal method of targeting. For example, it is more prominent in small tumors, which is probably related to a higher density of vessels compared with large tumors with an avascular region.⁴⁸

It is interesting to note that the tumor targeting that exists during the injection of ICG alone is also explained by the EPR effect, due to the fact that upon administration, ICG binds to serum proteins.

Different types of ICG nanoparticles

Inorganic ICG nanoparticles

The characteristics (nature, size) of the nanoparticles described in this section and the tumor models used are presented in Table 1.

Table 1 Non-organic ICG NPs

One of the first types of ICG inorganic nanoparticles developed was the mesoporous silica nanoparticle. In 2009, Lee et al⁴⁹ were interested in the characterization and the in vivo biodistribution of mesoporous silica nanoparticles loaded with ICG for optical imaging and demonstrated their effectiveness. They found a reduction in ICG aggregation, fluorescence self-quenching, and host immune response. This type of nanoparticle has the advantage of an excellent biocompatibility and easy functionalization with different compounds.⁵⁰

The same team was subsequently interested in the impact of the surface charge of mesoporous silica nanoparticles on in vivo biodistribution and found that positively charged nanoparticles were excreted from the liver into the gastrointestinal tract much faster than negatively charged nanoparticles.⁵¹ The authors concluded that excretion and clearance are influenced by surface charge and that positively charged mesoporous silica nanoparticles are more easily eliminated than negatively charged ones.

Chen et al designed an ICG-loaded, PEGylated, reduced nano-graphene oxide nanocomposite (rNGO-PEG/ICG) for photoacoustic and fluorescence dual-modality imaging.⁵² They reported an excellent fluorescence signal both in vitro and in vivo, with minimal toxicity. These nanoparticles possessed greater stability, a longer blood circulation time, and superior tumor targeting capability compared with free ICG. In mice, rNGO-PEG/ICG was found to circulate for up to 6 hrs after intravenous injection, and after 1 day no accumulation of nanoparticles was found in any major organs except the tumor regions. The authors concluded that their rNGO-PEG/ICG nanocomposite is capable of effectively targeting tumors in vivo via the EPR effect.

ICG-encapsulating calcium phosphate nanoparticles have also been developed,^28,53 and have improved ICG loading efficiency and quantum yield compared to polymeric nanoparticles.²⁸ Calcium phosphate nanoparticles can be used for in vivo tumor imaging and also for drug, gene, or siRNA delivery, with the huge advantage of being nontoxic.⁵³ ICG encapsulation significantly enhanced emission intensity compared to free ICG at elevated concentrations.⁴⁰ Altinoglu et al developed PEGylated calcium phosphate nanoparticles with a prolonged circulation time in vivo.²⁸

In addition, Song et al⁵⁴ developed small ICG-loaded magnetic carbon nanoparticles (MCNPs) for combined fluorescent and MRI imaging, which efficiently accumulated in tumors due to the EPR effect and the small particle size.

In vivo biodistribution of inorganic nanoparticles

In mouse model studies, in vivo biodistribution of inorganic nanoparticles demonstrated a strong and stable fluorescence, prominent in the liver.^49,51 In one study, there was a strong accumulation in internal organs such as the liver and intestine from 0.5 to 6 hrs. Over time, accumulation of the nanoparticles toward the tumor region became more significant and after 48 hrs the fluorescence signals were found only in the tumor region.⁵² In contrast, the clearance process for free ICG was rather rapid and the majority of the dye was cleared out of the body after 6 hrs.³⁴

In conclusion, the fluorescence signals from ICG nanoparticles are significantly extended in vivo compared to free ICG.

Organic ICG nanoparticles

The characteristics (nature, size) of the nanoparticles described in this section and the tumor models used are presented in Table 2. Poly(lactic-co-glycolic acid) (PLGA) carriers are one of the most common biodegradable and biocompatible systems used for ICG loading.⁴⁰ Zhao et al developed ICG-loaded PLGA-lecithin-PEG core-shell nanoparticles of 39 nm, 68 nm, or 116 nm in size via single-step nanoprecipitation.⁵⁵ The aim of their study was to explore the effects of nanoparticle size on biodistribution and tumor accumulation. They compared the excretion time of free ICG versus that of their nanoparticle. Fluorescence imaging indicated that nanoparticles were retained within the body longer than free ICG, which was quickly excreted and cleared. They also concluded there was a size-dependent tumor accumulation of ICG-PLGA nanoparticles: the 68 nm particles could easily pass through the vessel pores and had slower clearance than 39 nm particles.

Table 2 Organic ICG NPs

Wu et al developed a nanoparticle in which ICG was encapsulated in the core of a polymeric micelle, which self-assembled from amphiphilic PEG-polypeptide hybrid triblock copolymers of poly(ethylene glycol)-b-poly(L-lysine)-b-poly(L-leucine) (PEG-PLL-PLLeu), with PLLeu as the hydrophobic core and PEG as the hydrophilic shell.⁵⁶ The ICG was associated with the hydrophobic core via hydrophobic interaction and with the hydrophilic heads through electrostatic attractive interaction. Compared with free ICG, PEG-PLL-PLLeu-ICG micelles significantly improved quantum yield and fluorescent stability. The cellular uptake experiments showed that PEG-PLL-PLLeu-ICG micelles had a high cellular uptake rate. In addition, in vivo experiments revealed an excellent passive tumor targeting ability and long circulation time.

This and other studies^57–59 demonstrates that the encapsulation of ICG into polymer-based nanoparticles positively influences the properties of ICG.

Liposomes are another type nanoparticle frequently used for encapsulating ICG. Liposomes are closed spherical vesicles composed of a lipid bilayer made of either synthetic or natural phospholipids and have diameters of about 100 nm. Because ICG is an amphiphilic dye, it can be loaded either inside the lipid core or at the interface of lipid nanoparticles. Liposomes can protect the inside agents from the surrounding environment and prolong circulation time in the body. Another advantage is that liposomal ICG can be made entirely of clinically approved components.^40,60

Suganami et al explored the use of a liposomally formulated phospholipid-conjugated ICG for intraoperative brain tumor detection,⁶¹ and confirmed that this nanoparticle allowed the real-time detection of tumor and normal brain tissues.

In the study of Mérian et al, liposomal forms of ICG showed similar biodistribution patterns as free ICG, which indicate the immediate leakage from the nanoparticle after intravenous injection.⁶² They also demonstrated that ICG leakage increased considerably in the presence of bovine serum albumin because of the high affinity of the fluorophore for plasma proteins.

In vivo biodistribution of organic nanoparticles

Organic nanoparticles have excellent passive tumor targeting ability and a long circulation time. They are released slowly, which avoids the strong binding of ICG to nonspecific plasma proteins and the subsequent rapid elimination from the body (a half-life of 3–4 min). In mice treated with free ICG, fluorescence appeared in the liver and kidneys 4 hrs after injection, showing a dominant uptake of ICG by these organs. Twenty-four hours after injection, no detectable signal was recorded from free ICG, in contrast to what is observed with ICG nanoparticles.⁵⁶

Zhao et al demonstrated that the in vivo biodistribution varies according to the size of the nanoparticles. Size could not only influence endocytosis but also affect tumor accumulation.⁵⁵

The architecture of these inorganic and organic nanoparticles allowed ICG protection and so enhanced biocompatibility, photostability, and tumor accumulation by increasing the EPR effect. Nevertheless, the specificity of tumor labeling with ICG by passive targeting remains limited as previously described. This limitation explains the growing development of formulations allowing active tumor targeting.

ICG nanoparticles for active tumor targeting

Active tumor targeting by nanoparticles loaded with ICG is based on two elements: the target and the molecule recognizing the target, which must be grafted onto the nanoparticle. The target must be carefully chosen. It must be accessible (expressed on the surface of cells) and specific to the tumor (or at least be expressed more strongly in tumors). There must also be a ligand with high selectivity and high affinity for the target.

Folic acid-conjugated nanoparticles

Folate receptors are highly overexpressed on the surface of many tumor types. This makes folic acid (FA) a prime ligand for the active targeting of tumor tissues. Table 3 summarizes reported types of FA-conjugated nanoparticles with their characteristics (type, size) and the chosen tumor model.

Table 3 Folic-acid conjugated NPs

One of the most common forms of ICG-loaded nanoparticles coupled with FA is a polymer and liposome assembly (lipid-polymer hybrid nanoparticles, which have a biodegradable polymeric core surrounded by a lipid monolayer). These lipid-polymer hybrid nanoparticles have the combined advantages of polymeric nanoparticles and liposomes.⁶³ Chopra⁶³ developed FA-conjugated PLGA-lipid nanoparticles containing ICG at the core, called FA-ICG-PLGA-lipid nanoparticles. The imaging properties and biodistribution of FA-ICG-PLGA-lipid nanoparticles have been compared to those of free ICG and of the nanoparticles without FA. Twenty-four hours after injection, only the fluorescence signal of FA-ICG-PLGA-lipid nanoparticles could be detected in tumors. NIR fluorescence imaging of the various organs and tumors ex vivo demonstrated significant differences between the three compounds tested, with the best tumor fluorescence obtained with FA-ICG-PLGA-lipid nanoparticles. Xin et al⁶⁴ synthesized PLGA-lipid nanoparticles (PNPs) that covalently conjugate FA and ICG, called FA-RIPNPs. They concluded that FA-RIPNPs may facilitate a high cellular uptake via folate receptor-mediated endocytosis and that these nanoparticles have excellent stability and biocompatibility characteristics. FA-RIPNPs exhibited a 2.8-fold higher tumor accumulation than RIPNPs without FA, and a 12.6-fold higher accumulation than free ICG. The authors also added a PEG shell around the PLGA core to prolong the circulation time. Zheng et al⁶⁵ also described the same type of nanoparticles. These were ICG dye-doped PLGA-lipid folate receptor-targeted nanoparticles (FA-ICG-PLGA-lipid nanoparticles) constructed by employing a single-step self-assembly and nanoprecipitation method. The FA-ICG-PLGA-lipid nanoparticles exhibited excellent optical properties compared to free ICG (high aqueous stability, significant stability against photobleaching, excellent NIR optical properties), highly selective tumor localization, and prolonged circulation time in vivo. In the same way, Zheng et al⁶⁶ developed an ICG-containing nanostructure utilizing the noncovalent self-assembly chemistry between phospholipid-PEG (PL-PEG) and ICG. They used two different cellular models: U87 cancer cells, which overexpress the integrin Rvβ3 on the cell surface, and MCF-7 cancer cells, which express a very low level of integrin Rvβ3. These models were used because the nanoparticles were functionalized both with FA and with monoclonal antibodies (mAbs) to Rvβ3.

Another possible design is that proposed by Wu et al⁶⁷ a multifunctional nanostructure (ICG-FA-PPD), which consisted of the self-assembly of ICG- and FA-modified PEI (polyethylenimine)-PEG-gadoteric acid (FA-PPD). This nanoparticle showed greater photostability and lower cytotoxicity than free ICG and significantly accumulated in the tumor.

For ICG-loaded nanoparticles functionalized with FA, micelles could also be used. For example, Yan and Qui ⁶⁸ encapsulated ICG into folate-conjugated poly(2-ethyl-2-oxazoline)-b-poly(ɛ-caprolactone) micelles. In this nanoparticle, the poly(2-ethyl-2-oxazoline) plays the “stealth” role to extend blood circulation and suppress unwanted uptake by liver and spleen and the poly(ɛ-caprolactone) serves as drug storage to improve the stability of ICG. With their configuration, the authors obtained a significantly higher ICG stability compared to free ICG in vitro and in vivo and an excellent biocompatibility. These micelles could effectively target tumors and realize long-term tumor imaging with high contrast resolution. Also of interest is that the fluorescence of the ICG-loaded micelles was stable at room temperature for 14 days.⁶⁹

Hyaluronic acid-conjugated nanoparticles

Several studies have coupled ICG nanoparticles with hyaluronic acid. This allows both passive targeting (by the EPR effect due to nanoparticles) and active targeting (due to the affinity of hyaluronic acid for CD44). Uthaman et al⁷⁰ hydrophobically modified ICG prior to loading it into hyaluronic acid-based micelles and utilized these nanoparticles for CD44-based targeting. They used hyaluronic acid-C18 (octadecylamine) micelles, explaining that this type of micelle is better than the systems in which ICG is conjugated on the polymer. They observed protection of ICG by micelles from degradation and clearance until complete imaging.

In the same way, Qi et al⁷¹ utilized hyaluronic acid-derived nanoparticles with physico-chemically entrapped ICG, termed NanoICG, for intraoperative NIR fluorescence of pancreatic cancer. This formulation improved the poor aqueous solubility of imaging agents.⁷² NanoICG accumulated significantly within the pancreas in an orthotopic pancreatic adenocarcinoma model and demonstrated contrast enhancement for pancreatic lesions relative to nondiseased portions of the pancreas: ICG accumulation in the tumor was increased compared with free ICG and the fluorescence intensity of NanoICG was higher compared with ICG both in pancreas and splenic metastases. The in vitro and in vivo experimentation indicated negligible toxicity of NanoICG.

However, a limitation of hyaluronic acid-conjugated nanoparticles is their preferential uptake by the reticuloendothelial system,⁷² probably due to their high molecular weight.⁷¹

Antibody-conjugated nanoparticles

ICG-loaded nanoparticles can also be conjugated with antibodies. Table 4 describes the characteristics (nature, size, ligand/target) of antibody-conjugated nanoparticles and the tumor models used.

Table 4 Antibody conjugated NPs

mAbs against the human epidermal growth factor receptor-2 (HER-2) is of great interest for imaging of active tumor targeting.^73–75 HER-2 is involved in the carcinogenesis of various solid tumors, such as breast, colorectal, nonsmall cell lung, and ovarian cancer.^76,77 Different designs have been investigated, including nanocapsules,⁷³ erythrocyte-derived transducers,⁷⁴ and silica nanoparticles.⁷⁵ All these designs resulted in a significantly higher fluorescence in cells overexpressing HER-2 compared with cancer cells expressing lower HER-2 levels; the study authors concluded that successful tumor targeting is achieved by conjugating nanoparticles with anti-HER-2 antibodies.

Chen et al⁷⁸ proposed anti-NGAL (neutrophil gelatinase-associated lipocalin)-conjugated gold nanoshells that specifically targeted pancreatic cells in vitro and in vivo. They designed a theranostic nanocomplex targeted to NGAL and observed a higher tumor contrast compared with nontargeted PEGylated nanoparticles.

To target colorectal adenocarcinoma, Kolitz-Domb et al⁷⁹ synthesized a proteinoid-poly(L-lactic acid) copolymer bound to an anti-carcinoembryonic antigen (anti-CEA) antibody. The encapsulation of the ICG within this nanoparticle improved its photostability (by avoiding leakage and photobleaching) and targeting with anti-CEA antibodies achieved specific colon tumor detection in vivo.

Finally, using ICG-containing PL-PEG coupled with anti-Rvβ3 mAbs, Zheng et al⁶⁶ observed a higher ICG fluorescence intensity in cells overexpressing the integrin Rvβ3 compared to cell lines with few cell surface receptors.

Nanoparticles coupled with other ligands

To target prostate cancer cells (PC3), PLGA nanoparticles loaded with ICG and conjugated with RGD-4C (specific to α5β3) or R11 peptides can be used.⁸⁰ R11 peptides are cell-penetrating peptides specific to prostate cancer cells. In vitro studies showed that these nanoparticles had an improved optical stability (compared with free ICG), excellent biocompatibility with healthy cells, and an effective targeting capability.

Liposome-encapsulated ICG can also be coupled with various ligands, such as the RGD (Arg-Gly-Asp) peptide used to target gastric cancer.⁸¹ This formulation had a higher stability than free ICG, showed greater accumulation in the tumor tissues, and exhibited prolonged circulation time leading to an improved in vivo visualization of tumor tissues.

Cancer cell membrane-coated nanoparticles

Chen et al⁸² proposed another way of achieving active tumor targeting with ICG-loaded nanoparticles: using cancer cell membrane-cloaked nanoparticles. They synthesized biomimetic nanoparticles called ICNP (for “ICG-loaded and cancer cell membrane-coated nanoparticles”), which have a core−shell nanostructure consisting of an ICG-polymeric core and a cancer cell membrane shell (Figure 1). Due to their membrane structure and antigens, this type of active cell membrane-cloaked nanoparticle allows specific tumor binding, a long blood circulation time, and immune system escape. Nude mice bearing MCF-7 tumors received tail-vein injections of free ICG, nanoparticles without a cancer cell membrane coating, or ICNPs. ICNPs significantly promoted cell endocytosis and homologous-targeting tumor accumulation in vivo. These nanoparticles possessed both passive and homologous active targeting with a significantly enhanced tumor accumulation 24 hrs after injection. Nevertheless, these nanoparticles only target the type of tumor from which the membrane that covers them originates. It is therefore necessary to obtain nanoparticles for each tumor type.

Figure 1 Illustration of the cancer cell membrane coated nanoparticles with ICG (ICNPs). Preparation procedure of ICNPs: extracting cancer MCF-7 cell membrane hybridized with PEGylated phospholipids (DSPE-PEG) and then coated onto ICG-loaded polymeric cores by extrusion. Notes: Reprinted with permission from Chen Z, Zhao P, Luo Z, et al. Cancer Cell Membrane-Biomimetic Nanoparticles for Homologous-Targeting Dual-Modal Imaging and Photothermal Therapy. ACS Nano. 2016;10(11):10049–10057.82 Copyright © 2016, American Chemical Society.

In vivo biodistribution of targeted nanoparticles

Strong fluorescence signals were obtained in the whole body 5 mins after injection of free ICG, nanoparticles, and targeted nanoparticles. Six hours after injection, however, more intense fluorescence signals were obtained in the tumor region for the targeted nanoparticle group compared with the ICG and nontargeted nanoparticle groups. Twenty-four hours after injection, no detectable fluorescence was recorded in the free ICG and nontargeted nanoparticles groups. In contrast, the tumors of the targeted nanoparticle group exhibited a significant fluorescence signal.^64,65

The location and tumor margin could be observed 1 hr after injection in mice receiving targeted nanoparticles, but not in mice receiving nontargeted nanoparticles or free ICG.⁶⁸

With targeted nanoparticles, the fluorescence gradually diminished but remained detectable for 7 days.

Indocyanine green complexation

To specifically address a molecule through a mechanism of active targeting, biological conjugation with cancer-specific ligands (such chemical molecules, peptides, proteins, antibodies, and aptamers) is possible.¹⁸ The binding of cyanine dyes (such as ICG) to nucleic acids or proteins resulted in rigidization of the fluorophores, which increased fluorescence efficiency.^83,84

ICG conjugated to antibodies

Many authors report successful conjugation of ICG with antibodies. Table 5 summarizes the different designs proposed as well as the main characteristics (type, size, ligand/target) and the chosen tumor model. The binding of ICG to antibodies allows the creation of activatable NIR probes. ICG loses its fluorescence after protein binding; after cell binding and internalization of ICG–antibody complex, ICG dissociates from the targeting antibody and the fluorescence is therefore activated.²⁷ This is related to a unique property of ICG: it loses fluorescence when bound to the antibody, but regains it once it is chemically separated from the antibody, which occurs after internalization and degradation of the conjugate.⁸⁵

Table 5 ICG-antibodies complexation

A frequently used antibody is the anti-epidermal growth factor receptor (EGFR) mAb, also called panitumumab.^27,86–88 For antibody conjugation, ICG-sulfo-OSu (ICG-sOSu), an ICG derivative, is often used.^85,86 It seems that the interaction between ICG-sOSu and panitumumab is due to both covalent and noncovalent binding of the ICG-sOSu to the protein.⁸⁸ Zhou et al⁸⁸ purified the bioconjugate by size-exclusion high-performance liquid chromatography analysis (SE-HPLC), to remove aggregates and impurities, and then removed the noncovalently bound dye by extraction with ethyl acetate to further purify the conjugates. This technique allowed an excellent target-specific uptake of the doubly purified conjugates, with minimal liver retention in vivo.

Sano et al⁸⁶ re-engineered a panitumumab-ICG conjugate using bifunctional ICG derivatives (ICG-PEG4-Sulfo-Osu and ICG-PEG8-Sulfo-Osu) with short PEG linkers. PEG has a well-known biocompatibility and is widely used in clinical products.^88–90 ICG conjugates with PEG linkers significantly increased the percentage of covalent binding of ICG to the antibody, resulting in less in vivo noncovalent dissociation. Compared with the original panitumumab-ICG conjugate without short PEG linkers, the conjugates with PEG linkers were better able to specifically depict EGFR-positive tumors with high tumor-to-background ratios, especially for lesions in or near the liver. PEG linkers also result in a higher stability in serum and a higher in vitro cellular uptake. Villaraza et al⁸⁷ proposed a similar approach of using PEGylated panitumumab-ICG complexes. For this, a water-soluble amine-reactive PEGylated analogue of ICG⁹¹ was synthesized and used to label the panitumumab and was compared with the nonPEGylated conjugate. The PEGylation prevented aggregation in solution, whereas the targeting moiety was conserved. The panitumumab-ICG conjugate has also been used as a photoacoustic imaging probe to target cancer-associated EGFR.⁹²

Ogawa et al²⁷ studied three FDA-approved antibodies: daclizumab, trastuzumab, and panitumumab. For each, they successfully characterized the in vivo tumor over-expression of cell surface receptors using their respective ICG-conjugated antibodies. All conjugates demonstrated a high quenching capacity and were activatable, “switching on” only in target cells.

Nakajima et al⁸⁵ designed a humanized anti–prostate-specific membrane antigen (PSMA) antibody (J591) coupled with ICG. They obtained an activatable NIR probe that was able to detect PSMA+ tumors with high contrast compared to PSMA- tumors up to 10 days after injection of a low dose of reagent. Its ability to be activated only in PSMA+ cells led to very high tumor-to-background ratio.

Finally, Zhang et al⁹³ fabricated an anti-integrin αvβ6 antibody and labeled it with ICG to form an ICG-αvβ6 antibody. The expression of αvβ6 integrin is significantly upregulated in cutaneous squamous cell carcinoma (cSCC).^94,95 This ICG-αvβ6 antibody complex could detect cSCC with high specificity and deep penetration (1 cm).

ICG conjugated to antibody fragments

Antibody fragments, including diabodies, have more desirable pharmacokinetic characteristics than whole antibodies. For this reason, Sano et al⁹⁶ proposed an activatable optical imaging probe composed of a PSMA-targeted cys-diabody conjugated with ICG. This complex is only activated when bound to the tumor, which leads to high signal-to-background ratios. For this purpose, they used short PEG linkers between ICG and the reactive functional group, resulting in covalent conjugation of ICG to the cys-diabody. This configuration allowed a lower dissociation of ICG from the cys-diabody after injection and therefore reduced hepatic uptake. However, the authors concluded that whole ICG-conjugated antibodies appeared to be more effective activatable probes for PSMA-specific cancer detection than ICG-conjugated diabody probes. In fact, when ICG is conjugated to small proteins such as diabodies (which are catabolized in the kidneys) it can be recirculated after liver excretion, leading to a prolonged increased background in the abdomen in fluorescence images.

ICG conjugation with other ligands

ICG can also be conjugated to chlorotoxin.⁹⁷ An amine-reactive ester form of ICG was conjugated to chlorotoxin using standard amine-reactive chemistry; the conjugate was termed BLZ-100. The chlorotoxin is derived from the venom of the Leirus quinquestriatus scorpion and presents binding properties in gliomas⁹⁸ and many different solid tumors.^99,100 The target of the chlorotoxin is not yet known but is thought to involve the membrane proteins annexin A2¹⁰¹ and metalloproteinase-2.¹⁰² Baik et al⁹⁷ aimed to explore the uptake of BLZ-100 in an in vivo model of head and neck squamous cell carcinoma (HNSCC) and to test the ability of BLZ-100 to discriminate among stages of oral dysplasia. The signal-to-background ratio of BLZ-100 was significantly greater than that of free ICG in different HNSCC tumor models. Moreover, BLZ-100 demonstrated highly sensitive and specific uptake at the tumor periphery. This is interesting from a surgical point of view, because the difficulty in operating is not identifying the core of the tumor, but rather identifying the tumor margins and peripheral residual clusters.⁹⁷ BLZ-100 signal increased with dysplasia severity, allowing differentiation between high-risk and low-risk dysplasia.

Transferrin is another ligand that has been used to specifically target ICG to tumor tissue.¹⁰³ A simple mixing of transferrin with ICG enabled their self-assembly in aqueous solution to form nanoparticles that had excellent active targeting abilities and water solubility, colloidal stability, and favorable biocompatibility. There was a high reproducibility because of the simple synthesis procedure. These nanoparticles exhibited an impressive active targeting activity in vitro and in vivo in a cervical carcinoma model.

Future developments

ICG nanoparticles for cancer theranostics

Recently, the development of multifunctional nanoparticles offering both diagnostic and therapeutic capabilities has attracted attention.⁴⁰ It is interesting to note that many of the nanoparticles described in this review are multi-modal and exhibit different optical or theranostic properties. For example, the nanoparticles proposed by Chen et al⁵² enable both photoacoustic and fluorescence tumor imaging. Ashokan et al⁵³ designed a nanoparticle to combine nuclear, magnetic, and NIR in vivo imaging. Nanoparticles can also have drug delivery functions⁶⁴ or photothermal/photodynamic activities.^{55,56,66,68,73,78} Nanoparticles have been reported to cause substantial tumor cell death. This is possibly because ICG can be used as a photosensitizer to generate reactive oxygen species, such as singlet oxygen and superoxide, to damage cancer cells by illumination.⁴⁰

The use of theranostic ICG nanoparticles is of great interest in the management of brain tumors. Fluorescence-guided brain tumor surgery is routinely used in some centers and is under further investigation in clinical trials.¹⁰⁴ The difficulty of this type of surgery is that it is frequently impossible to resect the entire tumor. In this case, the use of theranostic nanoparticles would allow cellular targeting and thus permit the destruction of all the tumor cells while limiting the associated functional losses.

Second NIR window

Fluorescent imaging of biological systems in the second NIR window (NIR-II) can probe tissue at centimeter depths and achieve micrometer-scale resolution at millimeter depths. Unfortunately, all current NIR-II fluorophores are excreted slowly and are largely retained within the reticuloendothelial system, making clinical translation nearly impossible.¹⁰⁵ Currently, the use of ICG as an NIR-II probe is under investigation.¹⁰⁶

For example, Zeh et al developed a novel way to administer ICG in gliobastoma surgery. This technique, named Second Window ICG, exploits the natural permeability of tumor vasculature and its poor clearance to deliver high doses of ICG to tumors. They obtained an NIR optical contrast with good signal characteristics in intracranial brain tumors over a longer period of time than previously obtained with ICG video angiography alone. This nonspecific tumor accumulation of ICG within the tumor provided strong signal-to-background contrast and was not significantly time dependent between 6 hrs to 48 hrs, providing a broad plateau for stable visualization.¹⁰⁷

Conclusion

NIR FGS is an innovative and interesting technique for the real-time visualization of resection margins. Accurate visualization of margins would result in decreased risk of recurrence and reduced tissue loss, and would allow detection of tumor micro-foci. ICG, an FDA-approved dye, has been the subject of a large number of studies and is currently the fluorophore of choice for FGS. In this review, we have discussed a large number of ICG complexation strategies. All have the same goal: to overcome the limitations of free ICG, such as poor and exclusively passive tumor targeting, rapid elimination after intravenous injection, and a low fluorescence quantum yield in solution due to self-quenching. Studies have shown that the incorporation of ICG into nanoparticles can increase circulation time, thus increasing the EPR effect and as such passive tumor targeting. Subsequently, the complexation of ICG-loaded nanoparticles, or of ICG with different ligands directly, improved the circulation times as well as the optical properties of ICG, achieving active tumor targeting.

Nevertheless, given the absence of systematic studies and the fact that they have been implemented under different conditions, comparison between the various systems is very difficult. Similarly, the large number of different formulations makes their comparison and choosing between them extremely complex.

Considering the number of publications and their year of publication, it seems that future progress is ultimately related to the development of actively targeted nanoparticles loaded with ICG. Only four clinical trials using targeted ICG-conjugated nanoparticles are referenced; nevertheless, these are particularly recent studies (according to the U.S National Library of Medicine). Such nanoplatforms combine the protective benefits of ICG and the immune system escape offered by nanoparticles with the benefits of active targeting enabled by the attachment of different ligands. In addition, there is a greater risk of altering the optical properties of ICG when it is bound directly to ligands than when it is included in nanoparticles. Finally, given the developments in nanotechnology, the different techniques for producing nanoparticles have already been optimized.

The ultimate aim of all these devices is to be used in the clinical settings. ICG is already FDA approved, and most FDA-approved nanoparticles in oncology are organic nanoparticles. However, of the 55 trials involving nanoparticles, only two clinical trials using ICG nanoparticles were open to inclusion at the end of 2018 (according to the U.S National Library of Medicine). In view of the large number of recent formulations of ICG nanoparticles tested in preclinical models, it is not surprising that for the moment their use in clinical trials is still limited but will undoubtedly progress. One of the main challenges to this transition to the clinic will be to overcome concerns about nanoparticles. In this context, the development of ICG directly conjugated with a targeting agent could, despite some drawbacks, constitute an interesting alternative to ICG-conjugated nanoparticles.