Molecular Imaging of Tumor Microenvironment to Assess the Effects of Locoregional Treatment for Hepatocellular Carcinoma.

Liver cancer is one of the leading causes of cancer deaths worldwide. Among all primary liver cancers, hepatocellular carcinoma (HCC) is the most common type, representing 75%-85% of all primary liver cancer cases. Median survival following diagnosis of HCC is approximately 6 to 20 months due to late diagnosis in its course and few effective treatment options. Interventional therapy with minimal invasiveness is recognized as a promising treatment for HCC. However, due to the heterogeneity of HCC and the complexity of the tumor microenvironment, the long-term efficacy of treatment for HCC remains a challenge in the clinic. Tumor microenvironment, including factors such as hypoxia, angiogenesis, low extracellular pH, interstitial fluid pressure, aerobic glycolysis, and various immune responses, has emerged as a key contributor to tumor residual and progression after locoregional treatment for HCC. New approaches to noninvasively assess the treatment response and assist in the clinical decision-making process are therefore urgently needed. Molecular imaging tools enabling such an assessment may significantly advance clinical practice by allowing real-time optimization of treatment protocols for the individual patient. This review discusses recent advances in the application of molecular imaging technologies for noninvasively assessing changes occurring in the microenvironment of HCC after locoregional treatment.

13C magnetic resonance spectroscopic imaging

18F‐fluorodeoxyglucose

three‐dimensional

68Ga‐fibroblast activation protein inhibitor

antigen‐presenting immune cell

arterial spin labeling

Barcelona Clinic Liver Cancer

blood oxygen level–dependent

cancer‐associated fibroblast

contrast‐enhanced ultrasound

chemical shift imaging

computed tomography

dynamic contrast enhanced

diffusion‐weighted

fibroblast activation protein

fluorescence imaging

glypican‐3

hepatocellular carcinoma

hypoxia‐inducible factor 1 alpha

interstitial fluid pressure

locoregional treatment

matrix metalloproteinase

magnetic resonance

magnetic resonance imaging

near‐infrared

nitroreductase

optical imaging

photoacoustic imaging

positron emission tomography

extracellular pH

radiofrequency ablation

Arg‐Gly‐Asp

single‐photon emission computed tomography

transarterial chemoembolization

tumor‐infiltrating lymphocyte

tumor microenvironment

ultrasound

vascular endothelial growth factor

Yttrium‐90

Hepatocellular carcinoma (HCC) is one of the leading causes of cancer deaths worldwide.( , ) Although surgical extirpation and transplantation are the curative treatment for early‐stage patients, locoregional treatment (LRT) is playing an increasing role in the management of HCC.( ) LRT for HCC includes (1) intra‐arterial therapy (IAT), which consists of transarterial chemoembolization (TACE), conventional TACE, drug‐eluting beads TACE, transarterial radioembolization, and selective internal radiation therapy; and (2) ablation, including radiofrequency ablation (RFA), microwave ablation (MWA), and percutaneous ethanol injection (PEI)( , ) (Fig. 1). LRT is recommended for patients with HCC at different stages guided by the Barcelona Clinic Liver Cancer (BCLC) staging system, such as the very early (BCLC stage 0), early (BCLC stage A), intermediate stages (BCLC stage B), and even advanced stage (BCLC stage C).( , , ) However, increasing evidence indicates that changes in the tumor microenvironment (TME) of HCC after LRT may stimulate tumor proliferation, angiogenesis, treatment resistance, tumor recurrence, and metastasis, which limit the long‐term efficacy of LRT.( , , , , , ) Therefore, effectively monitoring the changes of TME in real time is particularly important for optimizing the strategy of LRT for HCC.

FIG. 1

The landscape of immunosuppressive TME of HCC after LRT, including metabolic reprogramming and various immune responses, such as immune stimulation, immune suppression, and immune evasion. Changes in the TME after LRT of HCC are often characterized by hypoxia low extracellular pH, up‐regulation of glycolysis, increased interstitial fluid pressure, and tumor angiogenesis. Various immune outcomes can be measured after intra‐arterial therapy and tumor ablation.

Although a few invasive approaches, such as oxygen electrodes( ) and microvessel density (MVD),( ) are available to monitor TME in HCC, most invasive methods may induce or accelerate tumor metastasis. Thus, the noninvasive methods that can be used to access the changes of TME in HCC are favorable and of great significance. Molecular imaging as an emerging technology enables the noninvasive visualization, characterization, and quantification of molecular events in living subjects.( , , ) The commonly used molecular imaging modalities include (1) positron emission tomography (PET) and single‐photon emission computed tomography (SPECT); (2) magnetic resonance imaging (MRI); (3) optical imaging (OI), such as bioluminescence imaging and fluorescence imaging (FLI); and (4) contrast‐enhanced ultrasound (US) and photoacoustic imaging (PAI) (Table 1). With the development of molecular imaging techniques, hybrid imaging modalities, such as PET/CT and PET/MRI, are proving to be invaluable, as they can provide comprehensive anatomic and functional information by taking the strengths of modalities.

TABLE 1

Major Molecular Imaging Modalities

Imaging Modality	Detection	Spatial Resolution	Temporal Resolution	Advantages	Disadvantages	Application
PET	γ‐ray	1‐2 mm (microPET); 6‐10 mm (clinical PET)	Second to minutes	High sensitivity; quantitative whole‐body scanning; no tissue penetrating limit	Radiation risk; high cost; low spatial resolution	Functional imaging
SPECT	γ‐ray	0.5‐2 mm (microSPECT); 7‐15 mm (clinical SPECT)	Minutes	High sensitivity; no tissue penetrating limit	Radiation risk; low spatial resolution	Functional imaging
MRI	Magnetic field	0.01‐0.1 mm (small‐animal MRI); 0.5‐1.5 mm (clinical MRI)	Minutes to hours	High spatial resolution; no tissue penetrating limit; no radiation risk	Relatively low sensitivity; long imaging time; exogenous contrast agent; low edge contrast	Anatomical/functional imaging
Fluorescence imaging	Fluorescence	2‐3 mm	Second to minutes	High sensitivity; multiplexed imaging	Low spatial resolution; poor tissue penetration; high degree of scattering	Functional imaging
Bioluminescence imaging	Fluorescence	3‐5 mm	Second to minutes	High sensitivity; high throughput	Relying on luciferin; requiring excitation (external light source); low potential for clinical translation	Functional imaging
US	Ultrasonic waves	0.01‐0.1 mm for superficial (few mm depth) applications; 1‐2 mm for deeper (few cm depths) applications	Second to minutes	Real time; low cost; portable	Low resolution; operator‐dependent analysis	Anatomical/functional imaging
PAI	Ultrasonic waves	~0.01 to 1 mm	Second to minutes	Higher resolution (from optical tomography); deeper penetration (from ultrasonography); high optical contrast; low acoustic scattering	Shielding by strongly absorbing objects	Anatomical/functional imaging

In this review, we summarize the recent applications of molecular imaging to assess the TME in HCC post‐locoregional therapy. Comments and future perspectives on the development of imaging techniques in this field are also provided.

Characterization of TME After LRT in HCC

The TME of HCC is a highly heterogeneous ecosystem composed of noncellular and cellular components, and it plays a key role in regulating liver fibrosis, liver cancer, epithelial–mesenchymal transition (EMT), tumor invasion, and metastasis.( , ) The noncellular components of tumor stroma are usually characterized by extracellular matrix proteins, proteolytic enzymes, growth factors, and inflammatory cytokines, regulating HCC biology by influencing tumor signaling pathways in tumor cells. The cellular components consist primarily of, for example, HCC cells, HCC‐related fibroblasts, immune cells, and endothelial cells. The interaction between tumor and stroma plays an active role in the recruitment and metabolic reprogramming of stromal cells in TME.( , , , )

Changes in the TME after LRT of HCC are often characterized by hypoxia, tumor angiogenesis, up‐regulation of glycolysis, low extracellular pH (pHe), increased interstitial fluid pressure, and various immune response, such as immune stimulation, immune suppression, and immune evasion, which is usually associated with tumor residue, recurrence, metastasis, and treatment resistance.( , , ) TACE and RFA can expose residual cancer cells to a hypoxic TME.( , ) Detrimental effects of hypoxia in carcinogenesis include (1) induction of a more aggressive tumor phenotype (up‐regulation of growth factors, induction of apoptosis resistance, DNA hypermethylation of tumor suppressor genes, and induction of EMT); (2) increased expression of immune checkpoints and impaired antitumor immune response, such as impaired entry of antitumor immune cells, recruitment of immunosuppressive regulatory T cells (Tregs), and myeloid‐derived suppressor cells (MDSCs); (3) stimulation of angiogenesis; (4) up‐regulation of glycolysis; (5) low pHe; and (6) increased interstitial fluid pressure (IFP).( ) In addition, changes in the immune response are often observed in patients with HCC after LRT.( ) LRT, including but not limited to TACE, MWA, RFA and Yttrium‐90 (Y90), can cause various immune responses( , ) (Fig. 1). It is worthwhile to mention that the TME change could be treatment‐specific. For example, the main therapeutic effect of TACE is via ischemic tumor necrosis due to the embolic effect, while local ablation provides treatment via thermal damage to cancer. In addition, Y90 has no embolic or thermal effect but radiation can induce tumor necrosis with slower therapeutic effect than TACE or ablation. Various molecular imaging techniques are being developed for accessing the changes of TME in HCC (Table 2).

TABLE 2

Imaging Modalities Used for the Assessment of TME in HCC

TME	Imaging Modalities	Biological Targets	Imaging Probes and Methods	Preclinical and/or Clinical Studies	References
Hypoxia	PET/CT	NTR	18F‐FMISO, 124I‐ IAZGP, 18F‐EF1, 18F‐EF5	Preclinical and clinical	( 24, 25, 26, 27 )
		pO2	18F‐FDG, perfusion CT	Preclinical	( 86 )
	MR	Oxygen‐sensitive	BOLD, TOLD	Preclinical and clinical	( 28, 29 )
		HIF‐1α	DW‐MRI, DCE‐MRI	Preclinical and clinical	( 30, 31 )
	OI	NTR	BBP	Preclinical	( 32 )
	PAI	HIF‐1α	sO2	Preclinical	( 33 )
Angiogenesis	PET/SPECT	Integrin αvβ3	64Cu‐cyclam‐RAFT‐c(‐RGDfK‐)4, 99mTc‐3PRGD2	Preclinical	( 34, 35 )
	SPECT	CD13	99mTc‐NGR	Preclinical	( 36 )
	MR	Angiogenesis	DCE‐MRI, DW‐MRI, ASL‐MRI, BOLD‐MRI	Preclinical and clinical	( 37, 38, 39, 40 )
		Integrin αvβ3	RGD‐modified T1‐Fe3O4	Preclinical	( 41 )
		VEGFR	IONP	Preclinical	( 42 )
	US	Integrin αvβ3, VEGFR	Microbubbles	Preclinical	( 43, 44 )
		Angiogenesis	CEUS, 3D DCE‐US	Preclinical	( 45, 46 )
Low pHe	SPECT/PAI	pH‐sensitive	131I‐Pd‐PEG or 125I‐Pd‐PEG	Preclinical	( 47 )
	MR	pH‐sensitive	31P MRSI, HP 13C MRSI, CEST, pHe mapping, IONP	Preclinical	( 48, 49, 50 )
	OI	pH‐sensitive	pH‐sensitive nanoprobes	Preclinical	( 51 )
Glycolysis and lactate	PET	Metabolic parameters	18F‐FDG	Preclinical and clinical	( 22, 52, 53, 54 )
	MR	PKM2	Hyperpolarized 13C‐MRSI, 13C‐Pyruvate	Preclinical	( 53, 55 )
IFP	CT	Liposomes	DCE‐CT	Preclinical	( 56, 87 )
	MR	IFP	DCE‐MRI	Preclinical	( 57 )
Immune cells	MR	CD3+ and CD8+ T cells	Radiomics (Immunoscore and Rad score)	Preclinical and clinical	( 61, 62 )
		Macrophages	SPIONs	Preclinical	( 68 )
	OI	TILs	IRDye800‐AbOX40	Preclinical	( 60 )
CAFs	PET	FAPI	68Ga‐FAPI	Preclinical and clinical	( 63, 64 )
MMPs	MR/OI	MMP‐2	Gd–Au@IR820	Preclinical	( 65 )
	OI	MMP	NIR dye	Preclinical	( 66 )
APCs	MR	HLA‐DR antibodies	160Gd‐HLA‐DR antibodies	Preclinical	( 68 )
GPC3	PET	GPC3	89Zr‐αGPC3, Al[18F]F‐GP2633	Preclinical	( 70, 73 )
	OI	GPC3	GSI‐Lip, Cy5.5‐GBP	Preclinical	( 71, 72 )

Abbreviations: BBP, n‐butyl benzyl phthalate; CEST, chemical exchange saturation transfer; HLA, human leukocyte antigen IONP, iron oxide nanoparticle; SPION, superparamagnetic iron oxide nanoparticle; TOLD, tissue oxygen level–dependent.

Molecular Imaging of TME After LRT in HCC

Hypoxia

Hypoxia can be assessed by hypoxia markers using molecular imaging modalities, such as PET, MRI, OI, and PAI. Nitroreductase (NTR), hypoxia‐inducible factor 1 alpha (HIF‐1α), and carbonic anhydrase IX (CA‐IX) are the major targets used for noninvasive imaging of tumor hypoxia. A variety of NTR‐targeted radionuclide‐labeled imaging agents, such as 18F‐FMISO,( ) 124I‐IAZG,( , ) 18F‐EF1( ) and 18F‐EF5,( ) have been developed for detecting the hypoxia region of HCC using PET imaging. The development of new oxygen‐sensitive MRI techniques makes it possible to noninvasively detect the perfusion and oxygenation state of tumors.( , , , ) For example, blood oxygen level–dependent (BOLD) and tissue oxygen level–dependent MRI have been used in preclinical and clinical studies to assess the blood supply and oxygenation of HCC.( , ) The apparent diffusion coefficient in diffusion‐weighted MRI (DW‐MRI) and volume transfer constant (Ktrans), area under the curve (AUC) in dynamic contrast‐enhanced MRI (DCE‐MRI) are related to hypoxia markers, such as HIF‐1α, CA‐IX, and vascular endothelial growth factor (VEGF). Therefore, DW‐MRI and DCE‐MRI have been used to assess cell proliferation and hypoxia in HCC.( , ) In addition, NTR‐targeted fluorescent probes, such as n‐butyl benzyl phthalate,( ) have shown the potential of detecting hypoxia of HCC by OI. A recent study demonstrated that PAI is useful for noninvasive monitoring of the changes of tissue oxygen saturation in a rodent model of HCC treated with sorafenib.( )

Angiogenesis

Several targets of tumor angiogenesis, such as integrin αvβ3 and VEGF, are being intensively investigated to evaluate tumor angiogenesis in HCC by molecular imaging. For instance, the radiolabeled tracers, 64Cu‐cyclam‐RAFT‐c(‐RGDfK‐)4( ) and 99mTc‐3PRGD2,( ) were studied for monitoring integrin αvβ3 by PET and SPECT, whereas 99mTc‐NGR( ) was prepared for targeting CD13 by SPECT. The vascular MRI techniques can be generally divided into two groups: (1) direct detection of angiogenesis with extrinsic contrast agents, such as DCE‐MRI and MRI with targeted agents; and (2) indirect detection of angiogenesis without contrast agents, such as arterial spin labeling (ASL) and BOLD‐MRI.( ) DCE‐MRI was used to measure the enhancement of exogenous contrast. On the other hand, ASL‐MRI, BOLD‐MRI, and DW‐MRI have been used to measure the enhancement of endogenous contrast.( , , ) The quantitative parameter Ktrans and semi‐quantitative parameter iAUC60 of DCE‐MRI are related to MVD, which can noninvasively assess tumor angiogenesis in the VX2 liver tumor model after PEI.( ) Additionally, the Arg‐Gly‐Asp (RGD)‐modified T1‐Fe3O4 was used as a highly sensitive positive contrast agent targeting integrin αvβ3, and it can monitor angiogenesis of HCC by MRI.( ) Iron oxide nanoparticles also showed the utility of detecting the local sorafenib delivery to HCC for targeted embolotherapy and visualizing the distribution of microspheres using MRI.( ) Furthermore, integrins αvβ3 and VEGF‐targeted microbubbles were successfully tested for noninvasive monitoring of tumor angiogenesis in HCC by US.( , ) Quantitative three‐dimensional (3D) DCE‐US is also feasible to detect angiogenesis in liver tumor models.( ) A comparison study of contrast‐enhanced US (CEUS) and DCE‐MRI was performed in a rat model of HCC, and the result showed that DCE‐MRI is more accurate than CEUS to evaluate the sorafenib‐induced reduction in vascular permeability.( )

Low pHe

Molecular imaging techniques are developed for monitoring low pHe, which is largely related to tumor growth, invasion, metastasis, and chemoresistance.( , , , ) For example, Pd nanosheet‐based radiotracers, 131I‐Pd‐PEG and 125I‐Pd‐PEG, were developed for SPECT/CT imaging of HCC.( ) The results showed that the tumor retention of the radiotracer correlates well with the acidic microenvironment. MRI has been used for monitoring pHe in HCC with success in preclinical studies.( , , ) Biosensor imaging of redundant deviation in shifts–based pHe mapping can serve not only as a longitudinal monitoring tool for noninvasive imaging of pHe but also as a functional surrogate biomarker for metabolic changes induced by cTACE of HCC( , ) (Fig. 2). The pHe mapping of HCC was also achieved by using chemical exchange saturation transfer MRI.( ) In terms of OI, a new near‐infrared (NIR) fluorescence probe, DiIRB‐S, was developed for monitoring pHe in HCC.( ) The results showed that the probe can target the primary tumors with a high tumor‐to‐background signal ratio, and a good correlation can be established between the metastatic potential and acidosis distribution pattern in the tumor.

FIG. 2

In vivo pHe mapping using biosensor imaging of redundant deviation in shifts with TmDOTP5‐ in a rabbit liver at 3 T. T1 VIBE MR images (A,B) were used to localize the VX2 tumor (red contour) within the liver (blue contour), while the profile of the rabbit body is shown with an orange contour. Two different chemical shift imaging (CSI) slices from the same animal were used to show the H2, H3, and H6 MR signals of TmDOTP5‐ in each voxel, in a part of the liver containing the VX2 tumor (C) and in a part of the liver devoid of any tumor (D). 1H spectra containing the H2, H3, and H6 resonances from the tumor (E) and normal liver (F) indicate a high signal‐to‐noise ratio in these voxels (>10), allowing accurate pHe determination (6.80 for the tumor and 7.23 for the normal liver). The pHe maps corresponding to the two CSI slices shown in (C) for the liver region with a VX2 tumor and in (D) for a normal liver region are shown in (G) and (H), respectively. The measurements indicate lower average pHe values inside the tumor (6.77 ± 0.03) and in the immediate vicinity of the tumor (6.89 ± 0.09), compared with those for the normal liver (7.22 ± 0.04). Reprinted with permission from Coman et al. (2019). © 2019 Wiley.

Glycolysis and Lactate

Glycolysis is related to metabolic reprogramming caused by hypoxia in the TME, leading to the overproduction of pyruvate, lactate, and carbonic acids. Tumor glycolysis can typically be evaluated using 18F‐fluorodeoxyglucose (18F‐FDG) PET.( , , ) Based on PET/CT imaging, several metabolic parameters, including maximum and mean standardized uptake values, peak standardized uptake values, metabolic tumor volume, and total lesion glycolysis, can be calculated to evaluate glycolysis after IAT of HCC.( , ) Recently, 13C magnetic resonance spectroscopic imaging (13C‐MRSI) of hyperpolarized [1‐13C]pyruvate and its metabolites was developed to study energy metabolism by visualizing.( , ) One study that compared spectroscopic images with 18F‐FDG PET for visualizing tumor metabolism in a rat model of HCC revealed that PET and 13C‐MRSI can be used to visualize increased glycolysis flux in HCC malignant tissues.( ) Although the hyperpolarized 13C‐MRSI of [1‐13C]pyruvate increases the sensitivity of MRI, signal‐to‐noise ratio constraints still apply for spatially and temporally resolved 13C‐MRSI, suggesting the further needs for magnetic resonance (MR) methodologic development (Fig. 3). In addition, an echo‐planar 3D 13C‐MRSI compression‐sensing sequence using hyperpolarized 13C‐MRSI was used to rapidly assess and locate the production of lactic acid in precursors, such as 13C‐labeled pyruvate or glucose, for imaging of HCC in a preclinical study.( ) Tumor voxels exhibited dramatically elevated lactate/pyruvate ratios (Fig. 4). Although 13C‐MRSI is very sensitive for imaging metabolic events, rapid signal decay has a limitation of its broad application.

FIG. 3

Examples of 13C MR metabolite images (integrating 30 seconds) and PET images (summing 10 minutes). Color scale was windowed to 6 times background for [1‐13C]lactate images and to 10 times background for [1‐13C]pyruvate and [1‐13C]alanine images. (A) Tumor with high lactate tumor‐to‐muscle ratio (TMR). (B) Tumor with high lactate TMR despite large necrotic part. Reprinted with permission from Menzel et al. (2013). © 2013 Society of Nuclear Medicine and Molecular Imaging. Abbreviations: GIT, gastrointestinal tract; LS, lactate syringe; M, muscle; T, tumor; and VC, vena cava.

FIG. 4

(A) Spectra from a transgenic liver cancer mouse with an early‐stage tumor, as shown in the upper left of the anatomic image, in which acceleration was used to reduce voxel size by a factor of 4 (×3.37 acceleration, 0.034‐cm3 voxel size, 16‐second acquisition). Tumor voxels exhibited dramatically elevated lactate/pyruvate ratios. The higher resolution reduced partial volume such that distinct metabolic profiles were observed in tumor and adjacent tissue voxels. (B) A separate data set in the same mouse with the same acquisition parameters in which the 3D‐MRSI data are presented coronally to emphasize the distinct metabolic profiles in tumors and other tissues. (C) A 3D‐MRSI data set from a different mouse with a moderate‐stage tumor at the level of the kidneys. Distinct differences between tumor and normal tissue are readily visualized in the color overlay maps. (D) Data from a mouse with a large very late‐stage tumor. Elevated alanine, as well as lactate, was detected in the tumor mass. Reprinted with permission from Hu et al. (2010). © 2009 Wiley.

IFP

Tumor IFP is a physiological parameter that has a predictive value for tumor aggressiveness, drug delivery, as well as response to treatment, such as radiotherapy and chemotherapy. Recent studies demonstrated that heterogeneous intratumoral accumulation of liposomes is associated with chaotic tumor microcirculation and elevated IFP. For example, DCE computed tomography (DCE‐CT)( ) and DCE‐MRI( ) have been used to monitor the IFP of HCC in preclinical studies. Although diffusion‐weighted (DW) MRI has been applied for the characterization of the IFP in cervical carcinoma and melanoma,( , ) the utility of DW‐MRI in HCC remains uncertain.

Immune Response

TME contains a repertoire of immune cells, such as innate tumor‐associated macrophages, tumor‐associated neutrophils, mast cells, MDSCs, cancer‐associated fibroblasts (CAFs), dendritic cells, natural killer cells, Treg cells, and tumor‐infiltrating lymphocytes (TILs). It is well‐known that immune cell recruitments, various immune responses, and metabolic reprogramming are involved in tumor development and spread.( , , , ) A near‐infrared fluorescence probe (IRDye800‐AbOX40) was used for noninvasive imaging of OX40 expression on TILs, and it can predict the early response to immunotherapy of HCC.( ) Radiomics has been used as a method to detect the TME of HCC to optimize treatment decisions for immunotherapy. For example, MRI‐based immunoscore can be used to evaluate the density of CD3+ and CD8+ T cells,( ) and contrast‐enhanced CT‐based Rad score was calculated to estimate tumor‐infiltrating CD8+ T cells.( )

CAFs are instrumental in coordinating cellular and molecule in TME, including recombinant extracellular matrix, secreting extracellular matrix metalloproteinases (MMPs), mediating angiogenesis, and regulating the proliferation of tumor and immune cells and migration. The high expression of fibroblast activation protein (FAP) in CAFs has been used as an ideal target for diagnosis. 68Ga‐fibroblast activation protein inhibitor (68Ga‐FAPI) exhibits excellent target specificity and pharmacokinetics, and it can be used for clinical noninvasive monitoring of CAFs by PET/CT imaging. Increasing evidence shows that 68Ga‐FAPI PET/CT imaging is useful for clinical noninvasive detection of CAFs in the TME of HCC.( , ) 68Ga‐FAPI PET/CT should also be considered complementary for tumor entities known to perform poorly with 18F‐FDG in HCC. MMPs are proteolytic enzymes that play a key role in the initiation and progression of tumors, and they are related to tumor invasion and metastasis. A dual‐modality imaging nanoprobe (Gd‐Au@IR820) formed by self‐assembly of ultrasmall AuNPs modified with MMP‐2 on the surface was used for dual‐mode (MRI/FLI) real‐time imaging‐guided photodynamic/photothermal combination therapy for HCC.( ) In another study, NIR dye‐labeled MMP was used as a molecular probe to successfully detect MMP of HCC using FLI.( ) RGD, MMP, and 18F‐FDG were imaged on tumor‐bearing mice using PET, CT, X‐ray, and multi‐wavelength OI modalities.( ) Image results revealed that each agent is bound to a specific disease target component.

Other Molecular Targets

TACE with immunotherapies can exploit tumor‐associated antigens that are exposed during tissue destruction and presented by antigen‐presenting immune cells (APCs) to activate T‐lymphocytes.( ) A study demonstrated that specific gadolinium 160‐labeled anti‐human leukocyte antigen–DR isotope antibodies (160Gd‐HLA‐DR antibodies) and superparamagnetic iron oxide nanoparticles (SPIONs) showed curvilinear peritumoral distribution on MRI scans in a VX2 rabbit liver tumor model, corresponding to APCs and iron deposits in macrophages, respectively.( ) In addition, glypican‐3 (GPC3) is a carcinoembryonic antigen that is an ideal target for anticancer immunotherapy against HCC. A study showed that patients with GPC3‐expressing HCCs exhibited an increase in GPC3‐specific cytotoxic T lymphocytes after RFA or TACE, whereas none of the patients did after surgical resection.( ) Molecular probes for targeting GPC3 are actively being developed for PET and OI.( , , , )

Conclusion and Perspectives

Cancer immunotherapy has undergone a rapid expansion in terms of the number of agents that confer a prognostic benefit by activating the immune system to mount a response against developing tumors. Recently, immunotherapy approaches that involve blocking the immune‐suppressive cytotoxic T‐lymphocyte‐associated protein 4 or programmed cell death protein 1 have shown promising results.( ) However, the distinction between hot, altered, and cold tumors relies on the cytotoxic T‐cell landscape within a tumor. Monitoring of TME with thorough profiling can better analyze the complexity of the tumors and provide dynamic information about the complex network changes occurring in the TME to assist in clinical decisions.( ) With the advent of immunotherapy for HCC, there is an increasing interest in understanding how immunotherapy may be best combined with locoregional therapies.( , ) Currently, a good number of phase 2 and 3 clinical trials are investigating the combined locoregional‐immunotherapy,( , ) such as the combination of TACE and immunotherapy (NCT04268888, NCT04246177, NCT03778957, NCT03575806, NCT03572582, NCT03592706, NCT03397654, NCT02856815, NCT02568748, and NCT02487017); the combination of ablation and immunotherapy (NCT03383458); the combination of TACE, ablation, and immunotherapy (NCT03124498 and NCT02821754); and the combination of Y90 and immunotherapy (NCT02837029, NCT03380130, NCT03033446, and NCT03099564). As new treatment approaches are being developed, noninvasive assessment, in real time, of tumor response to treatment currently remains a major challenge. Imaging tools to assist in this clinical decision‐making process, thus enabling treatment optimization for the individual patient, are therefore urgently needed.

Clinically, assessment of response to LRT includes the measurement of tumor size, tumor margins, tumor necrosis, and the detection of residual or recurring and new tumors. Advances in morphological imaging techniques, particularly MRI and CT, have improved the detection and staging of tumors, as well as the measurement of therapy response.( , ) Further improvement in the HCC patient management through imaging will be limited unless anatomical studies are augmented with an assessment of tumor biology and metabolism in vivo. Metabolic imaging can be an excellent supplementary method for evaluating the response of LRT in HCC. PET and SPECT imaging modalities have been used to monitor the response of locoregional therapy in HCC.( , , ) Recently, a clinical trial showed that 18F‐fluorocholine (18F‐FCH) PET/CT can predict the outcome of early‐stage HCC undergoing LRT.( ) Compared with FDG, 18F‐FCH is considered to be more sensitive in detecting HCC, especially for well‐differentiated HCC.( )

Image‐guided surgery can visually distinguish tumor cells from surrounding tissues in real time, thereby facilitating the complete removal of tumor lesions.( , ) Indocyanine green (ICG) is the most popular imaging agent used for image‐guided surgery, and it has been approved by the U.S. Food and Drug Administration for surgical procedures.( , ) In addition to ICG, many fluorescent dyes, including Cy5.5, Cy7, IRdye800 CW, and quantum dots have been extensively studied.( ) After the conjugation with tumor‐specific ligands of biomarkers, such as matrix metalloproteinase and integrin αvβ3, the imaging probes can enhance intraoperative tumor‐specific uptake.( ) It is expected that imaging tools will continue to play an important role in the LRT of HCC, including surgical resection.

Due to the heterogeneity of HCC and the complexity of the TME, combinations of imaging techniques, as so‐called “multimodality imaging,” are being designed to take the strengths of modalities while minimizing their limitations, which as a result may simultaneously provide comprehensive biological information. Although recent preclinical data are quite promising in the assessment of treatment response in HCC, a huge effort remains required to accelerate the translation of new imaging techniques from bench to bedside. To foster the continued discovery and development of imaging techniques, strong collaborations among academia, industry, and government are pivotal. In the foreseeable future, it is expected that molecular imaging techniques will be extensively applied in clinical settings and thus pave the way toward personalized cancer medicine to improve the management of patients with HCC.